US20050148512A1 - Medical implants and fibrosis-inducing agents - Google Patents

Medical implants and fibrosis-inducing agents Download PDF

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Publication number
US20050148512A1
US20050148512A1 US10/986,230 US98623004A US2005148512A1 US 20050148512 A1 US20050148512 A1 US 20050148512A1 US 98623004 A US98623004 A US 98623004A US 2005148512 A1 US2005148512 A1 US 2005148512A1
Authority
US
United States
Prior art keywords
fibrosis
fibrosing agent
agent
inducing agent
poly
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US10/986,230
Other languages
English (en)
Inventor
William Hunter
David Gravett
Philip Toleikis
Arpita Maiti
Pierre Signore
Richard Liggins
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Angiotech International AG
Original Assignee
Angiotech International AG
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Angiotech International AG filed Critical Angiotech International AG
Priority to US10/986,230 priority Critical patent/US20050148512A1/en
Priority to US10/996,353 priority patent/US20050152941A1/en
Priority to CA002536242A priority patent/CA2536242A1/en
Priority to EP04812062A priority patent/EP1687041A2/en
Priority to JP2006541669A priority patent/JP2007513650A/ja
Priority to PCT/US2004/039346 priority patent/WO2005051232A2/en
Priority to PCT/US2004/039465 priority patent/WO2005051444A2/en
Priority to US10/996,352 priority patent/US20050158356A1/en
Priority to AU2004293075A priority patent/AU2004293075A1/en
Priority to EP04811760A priority patent/EP1687043A2/en
Priority to PCT/US2004/039353 priority patent/WO2006055008A2/en
Priority to AU2004293030A priority patent/AU2004293030A1/en
Priority to US10/996,355 priority patent/US20050149157A1/en
Priority to PCT/US2004/039183 priority patent/WO2005051483A2/en
Priority to PCT/US2004/039099 priority patent/WO2005051451A2/en
Priority to CA002536188A priority patent/CA2536188A1/en
Priority to CA002536192A priority patent/CA2536192A1/en
Priority to AU2004293463A priority patent/AU2004293463A1/en
Priority to JP2006541689A priority patent/JP2007514472A/ja
Priority to PCT/US2004/039387 priority patent/WO2005051871A2/en
Priority to EP04817879A priority patent/EP1685085A2/en
Priority to JP2006541598A priority patent/JP2007516742A/ja
Priority to US10/998,351 priority patent/US20050209665A1/en
Priority to US10/998,349 priority patent/US20050209664A1/en
Priority to US10/998,350 priority patent/US20050187600A1/en
Priority to US11/001,415 priority patent/US20050181007A1/en
Priority to US11/001,421 priority patent/US20060240063A9/en
Priority to US11/001,789 priority patent/US20050181010A1/en
Priority to US11/001,416 priority patent/US20050142162A1/en
Priority to US11/001,422 priority patent/US20060240064A9/en
Priority to US11/001,787 priority patent/US20050181009A1/en
Priority to US11/001,420 priority patent/US20050169958A1/en
Priority to US11/004,671 priority patent/US20050169960A1/en
Priority to US11/004,675 priority patent/US20050169961A1/en
Priority to US11/004,673 priority patent/US20050175657A1/en
Priority to US11/004,672 priority patent/US20050175664A1/en
Priority to US11/006,902 priority patent/US20050158274A1/en
Priority to US11/006,906 priority patent/US20050182496A1/en
Priority to US11/006,880 priority patent/US20050186245A1/en
Priority to US11/006,893 priority patent/US7166570B2/en
Priority to US11/006,892 priority patent/US20050187639A1/en
Priority to US11/006,882 priority patent/US20050154374A1/en
Priority to US11/006,886 priority patent/US20050147562A1/en
Priority to US11/006,901 priority patent/US20050181005A1/en
Priority to US11/006,898 priority patent/US20050192647A1/en
Priority to US11/007,838 priority patent/US20050152948A1/en
Priority to US11/006,884 priority patent/US20050182467A1/en
Priority to US11/006,909 priority patent/US20050203635A1/en
Priority to US11/006,910 priority patent/US20060282123A1/en
Priority to US11/006,897 priority patent/US20050186239A1/en
Priority to US11/006,883 priority patent/US20050186246A1/en
Priority to US11/006,891 priority patent/US20050182468A1/en
Priority to US11/006,894 priority patent/US20050152946A1/en
Priority to US11/006,885 priority patent/US20050209666A1/en
Priority to US11/006,907 priority patent/US20050191248A1/en
Priority to US11/006,881 priority patent/US20050152944A1/en
Priority to US11/006,890 priority patent/US20050182450A1/en
Priority to US11/006,887 priority patent/US20050152945A1/en
Priority to US11/006,903 priority patent/US20050152947A1/en
Priority to US11/006,904 priority patent/US20050186247A1/en
Priority to US11/007,837 priority patent/US20050182469A1/en
Priority to US11/006,889 priority patent/US20050147599A1/en
Assigned to ANGIOTECH INTERNATIONAL AG reassignment ANGIOTECH INTERNATIONAL AG ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: GRAVETT, DAVID M., HUNTER, WILLIAM L., LIGGINS, RICHARD T., MAITI, ARPITA, SIGNORE, PIERRE E., TOLEIKIS, PHILIP M.
Priority to US11/129,763 priority patent/US7241736B2/en
Publication of US20050148512A1 publication Critical patent/US20050148512A1/en
Priority to IL174640A priority patent/IL174640A0/en
Priority to IL174638A priority patent/IL174638A0/en
Priority to IL174639A priority patent/IL174639A0/en
Assigned to ANGIOTECH INTERNATIONAL AG reassignment ANGIOTECH INTERNATIONAL AG ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: GUAN, DECHI
Priority to US11/431,427 priority patent/US20070026043A1/en
Priority to US11/775,816 priority patent/US20070254833A1/en
Priority to US12/425,316 priority patent/US20090214652A1/en
Priority to US12/464,012 priority patent/US20100092536A1/en
Priority to US12/703,679 priority patent/US20100268288A1/en
Abandoned legal-status Critical Current

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Definitions

  • the present invention relates generally to pharmaceutical compositions, methods and devices, and more specifically, to compositions and methods for preparing medical implants to make them more adherent to, or, more readily incorporated within a living tissue.
  • the pharmaceutical agents and compositions are utilized to create novel drug-coated implants and medical devices which induce a fibrotic response in the surrounding tissue such that the device is effectively anchored in situ and its performance is enhanced.
  • implantable medical devices generally are composed of materials that are highly biocompatible and designed to reduce the host tissue response. These materials (e.g., stainless steel, titanium based alloys, fluoropolymers, and ceramics) typically do not provide a good substrate for host tissue attachment and ingrowth during the scarring process. As a result of poor attachment between the device and the host tissue, devices can have a tendency to migrate within the vessel or tissue in which they are implanted.
  • the extent to which a particular type of medical device can move or migrate after implantation depends on a variety of factors including the type and design of the device, the material(s) from which the device is formed, the mechanical attributes (e.g., flexibility and ability to conform to the surrounding geometry at the implantation site), the surface properties, and the porosity of the device or device surface.
  • the tendency of a device to loosen after implantation also depends on the type of tissue and the geometry at the treatment site, where the ability of the tissue to conform around the device generally can help to secure the device in the implantation site.
  • Device migration can result in device failure and, depending on the type and location of the device, can lead to leakage, vessel occlusion, and/or damage to the surrounding tissue.
  • the medical device is anchored mechanically to biological tissue.
  • artificial implants can be anchored to the surrounding tissues by physical and mechanical means (e.g., screws, cements and porous surfaces) or by friction.
  • mechanical attachment of a device to the site can be effected by using a fastener, such as a suture or staple.
  • the device includes in its design mechanical means for fastening it into the surrounding tissue.
  • the device may include metallic spikes, anchors, hooks, barbs, pins, clamps, or a flange or lip to affix the device in place (see, e.g., U.S. Pat. Nos. 4,523,592; 6,309,416; 6,302,905; and 6,152,937).
  • a disadvantage of mechanical fasteners is that they can damage the tissue or vessel wall when the device is deployed.
  • Other methods for preventing device migration have focused on mechanically altering the surface characteristics of the device.
  • One such approach involves scoring or abrading the surface of the implant. The roughened surfaces promote cell, bone or tissue adhesion for better affixing of the implants in the body (see, e.g., WO 96/29030A1).
  • Medical devices such as implantable orthopedic devices, may be fixed to host tissue (e.g., bone) with an adhesive, such as a polymethyl methacrylate (PMMA) bone cement or a bone cement made from calcium phosphates and calcium aluminate (see, e.g., U.S. Pat. No. 6,723,334).
  • PMMA polymethyl methacrylate
  • a drawback of bone cements is that over time the cemented bone-prosthesis interface can degenerate, and/or the cement itself may weaken and fail, resulting in loosening of the implant.
  • the present invention provides compositions for delivery of selected therapeutic agents via medical implants or implantable medical devices, as well as methods for making and using these implants and devices.
  • drug-coated or drug-impregnated implants and medical devices are provided which induce adhesion or fibrosis in the surrounding tissue, or facilitate “anchoring” of the device/implant in situ, thus enhancing the efficacy.
  • fibrosis is induced by local or systemic release of specific pharmacological agents that become localized to the adjacent tissue.
  • tissue following a mechanical or surgical intervention involves two distinct processes: (1) regeneration (the replacement of injured cells by cells of the same type) and (2) fibrosis (the replacement of injured cells by connective tissue).
  • angiogenesis new blood vessels
  • ECM extracellular matrix
  • remodeling maturation and organization of the fibrous tissue.
  • inducing or promoting one or more of the processes of angiogenesis, fibroblast migration or proliferation, ECM production, and/or remodeling numerous therapeutic agents described in this invention can have the additional benefit of also promoting tissue regeneration.
  • an implant or device is adapted to include or to release an agent that induces fibrosis or regeneration through one or more of the mechanisms sited above.
  • the present invention provides devices that comprise a medical implant and at least one of (i) a fibrosis-inducing agent and (ii) a composition that comprises a fibrosis-inducing agent.
  • the agent is present so as to induce fibrosis formation that may otherwise not occur or increase fibrosis in a statistically significant manner when the implant is placed within an animal.
  • the present invention is directed to methods wherein both an implant and at least one of (i) a fibrosis-inducing agent and (ii) a composition that comprises a fibrosis-inducing agent, are placed into an animal, and the agent causes the formation of fibrosis that may otherwise not occur or increase fibrosis in a statistically significant manner.
  • the present invention provides the following: a device, comprising an orthopedic implant and a fibrosis-inducing agent or a composition comprising a fibrosis-inducing agent, wherein the agent induces fibrosis; a device, comprising a male or female sterilization implant and a fibrosis-inducing agent or a composition comprising a fibrosis-inducing agent, wherein the agent induces fibrosis; a device, comprising an implant for treating or preventing urinary incontinence device and a fibrosis-inducing agent or a composition comprising a fibrosis-inducing agent, wherein the agent induces fibrosis; a device, comprising an implant for treating or preventing gastroesophageal reflux disease (GERD) and a fibrosis-inducing agent or a composition comprising a fibrosis-inducing agent, wherein the agent induces fibrosis; a device, comprising an implant for treating or preventing gastroe
  • the agent is: an arterial vessel wall irritan; selected from the group consisting of talcum powder, metallic beryllium and oxides thereof, copper, silk, silica, crystalline silicates, talc, quartz dust, and ethanol; a component of extracellular matrix selected from fibronectin, collagen, fibrin, or fibrinogen; a polymer is selected from the group consisting of polylysine, poly(ethylene-co-vinylacetate), chitosan, N-carboxybutylchitosan, and RGD proteins; vinyl chloride or a polymer of vinyl chloride; an adhesive selected from the group consisting of cyanoacrylates and crosslinked poly(ethylene glycol)-methylated collagen; an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8
  • an inflammatory cytokine e.g., T
  • the device may additionally comprise a proliferative agent that stimulates cellular proliferation.
  • proliferative agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • the agent may be present in a composition along with a polymer.
  • the polymer is biodegradable.
  • the polymer is non-biodegradable.
  • the invention provides a composition, comprising a fibrosis-inducing agent and a bulking agent, wherein the fibrosis-inducing agent induces fibrosis.
  • the invention provides a composition, comprising a fibrosis-inducing agent and a sealant, wherein the agent induces fibrosis.
  • Exemplary fibrosis-inducing agents include, without limitation: an arterial vessel wall irritant selected from the group consisting of talcum powder, metallic beryllium and oxides thereof, copper, silk, silica, crystalline silicates, talc, quartz dust, and ethanol; a component of extracellular matrix selected from fibronectin, collagen, fibrin, or fibrinogen; a polymer selected from polylysine, poly(ethylene-co-vinylacetate), chitosan, N-carboxybutylchitosan, and RGD proteins; vinyl chloride or a polymer of vinyl chloride; an adhesive selected from the group consisting of cyanoacrylates and crosslinked poly(ethylene glycol)-methylated collagen; an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-8, IL-6, and growth hormone); CTGF; BMP (e.g
  • the device may additionally comprise an agent that stimulates cellular proliferation.
  • agents that stimulates cellular proliferation include: dexamethasone, isotretinoin, 17- ⁇ -estradiol, estradiol, diethylstibesterol, cyclosporine A, all-trans retinoic acid (ATRA), and analogues and derivatives thereof. Bulking agents and sealants are described herein.
  • the present invention also provides methods.
  • the present invention provides methods whereby a specified device is implanted into an animal, and a specified agent associated with the device induces fibrosis that may otherwise not occur or increases fibrosis in a statistically significant manner.
  • a specified device is implanted into an animal, and a specified agent associated with the device induces fibrosis that may otherwise not occur or increases fibrosis in a statistically significant manner.
  • Each of the devices identified herein may be a “specified device”, and each of the fibrosis-inducing agents identified herein may be a “fibrosis-inducing agent”, where the present invention provides, in independent embodiments, for each possible combination of the device and the agent.
  • the agent may be associated with the device prior to the device being placed within the animal.
  • the agent or composition comprising the agent
  • the agent may be coated onto an implant, and the resulting device then placed within the animal.
  • the agent may be independently placed within the animal in the vicinity of where the device is to be, or is being, placed within the animal.
  • the agent may be sprayed or otherwise placed onto the tissue that can be contacting the medical implant or may otherwise undergo scarring.
  • the present invention provides, in independent aspects: a method for treating or preventing spider veins or varicose veins, comprising injecting into the vein a composition comprising a fibrosis-inducing agent; a method for sterilizing a female patient, comprising injecting into a Fallopian tube a composition comprising a fibrosis-inducing agent; a method for treating or preventing urinary incontinence, comprising injecting into an urethra a composition comprising a fibrosis-inducing agent; a method for treating or preventing GERD, comprising injecting into a lower esophageal sphincter a composition comprising a fibrosis-inducing agent; a method for treating or preventing fecal incontinence, comprising injecting into an anal sphincter a composition comprising a fibrosis-inducing agent; a method for treating or preventing snoring or sleep apnea,
  • the agent may be present in a composition along with a polymer.
  • the polymer is biodegradable.
  • the polymer is non-biodegradable.
  • the composition may contain collagen.
  • FIG. 1 is a graph showing the effect of cyclosporine A on proliferation of human smooth muscle cells.
  • FIG. 2 is a graph showing the effect of dexamethasone on proliferation of human fibroblasts.
  • FIG. 3 is a graph showing the effect of all-trans retinoic acid (ATRA) on proliferation of human smooth muscle cells.
  • ATRA all-trans retinoic acid
  • FIG. 4 is a graph showing the effect of isotretinoin on proliferation of human smooth muscle cells.
  • FIG. 5 is a graph showing the effect of 17- ⁇ -estradiol on proliferation of human fibroblasts.
  • FIG. 6 is a graph showing the effect of 1a,25-dihydroxy-vitamin D 3 on proliferation of human smooth muscle cells.
  • FIG. 7 is a graph showing the effect of PDGF-BB on smooth muscle cell migration.
  • FIG. 8 is a bar graph showing the area of granulation tissue in carotid arteries exposed to silk coated perivascular polyurethane (PU) films relative to arteries exposed to uncoated PU films.
  • PU perivascular polyurethane
  • FIG. 9 is a bar graph showing the area of granulation tissue in carotid arteries exposed to silk suture coated perivascular PU films relative to arteries exposed to uncoated PU films.
  • FIG. 10 is a bar graph showing the area of granulation tissue in carotid arteries exposed to natural and purified silk powder and wrapped with perivascular PU film relative to a control group in which arteries are wrapped with perivascular PU film only.
  • FIG. 11 is a bar graph showing the area of granulation tissue (at 1 month and 3 months) in carotid arteries sprinkled with talcum powder and wrapped with perivascular PU film relative to a control group in which arteries are wrapped with perivascular PU film only.
  • FIG. 12 is a bar graph showing indicating the area of perivascular granulation tissue quantified by computer-assisted morphometric analysis in rat carotid arteries treated with control uncoated PU films and with PU films treated with degummed and virgin silk strands. As shown in the figure, both types of silk markedly increased granulation tissue growth around the blood vessel to the same extent.
  • FIG. 13 shows representative histology sections of rat carotid arteries treated with PU films coated with degummed and virgin silk strands. As shown in the figure, both types of silk induced a marked tissue reaction around the treated blood vessel. Movat stain, 100 ⁇ .
  • FIG. 14 shows representative histology sections of rat carotid arteries treated with PU films coated with degummed and virgin silk strands showing the granulation tissue that has grown around the treated vessels.
  • the silk strands have broken down into small particles surrounded by giant cells and macrophages.
  • the granulation tissue is highly vascularized and contains numerous inflammatory cells and fibroblasts. Extracellular matrix deposition is also extensive. H&E stain 200 ⁇ .
  • FIG. 15 shows the release profile for cyclosporine A from a polyurethane film as analyzed by HPLC.
  • the present invention discloses pharmaceutical agents which promote one or more aspects of the production of fibrous (scar) tissue or tissue regeneration. Furthermore, compositions and methods are described for coating medical devices and implants with drug-delivery compositions such that the pharmaceutical agent is delivered in therapeutic levels over a period sufficient for fibrosis and healing to occur. The present invention also describes various compositions and methods for enhancing the production of scar tissue adjacent to or on the surface of the implant are described. Numerous specific implants and devices are described that are capable of producing superior clinical results as a result of being coated with agents that promote scarring and healing, as well as other related advantages.
  • Medical Device refers to any object placed in the body for the purpose of restoring physiological function, reducing/alleviating symptoms associated with disease, and/or repairing/replacing damaged or diseased organs and tissues.
  • While normally composed of biologically compatible synthetic materials e.g., medical-grade stainless steel, titanium and other metals, polymers such as polyurethane, silicon, polylactic acid (PLA), polyglycolic acid (PLGA) and other materials
  • other materials that are exogenous, some medical devices and implants include materials derived from animals (e.g., “xenografts” such as whole animal organs; animal tissues such as heart valves; naturally occurring or chemically-modified molecules such as collagen, hyaluronic acid, proteins, carbohydrates and others), human donors (e.g., “allografts” such as whole organs; tissues such as bone grafts, skin grafts and others), or from the patients themselves (e.g., “autografts” such as saphenous vein grafts, skin grafts, tendon/ligament/muscle transplants).
  • autografts such as saphenous vein grafts, skin grafts, tendon/ligament/muscle transplants.
  • Medical devices of particular utility in the present invention include, but are not restricted to, orthopaedic implants (artificial joints, ligaments and tendons, screws, plates, and other implantable hardware), dental implants, intravascular implants (particularly arterial and venous occlusion devices and implants; vascular destructive implants), male and female contraceptive or sterilization devices and implants, implantable tissue bulking agents for incontinence (esophageal, urethral, anal), soft palate implants, embolization agents, pulmonary sealants, surgical meshes (e.g., hernia repair meshes, tissue scaffolds), fistula treatments, and spinal implants (e.g., artificial intervertebral discs, spinal fusion devices, etc.).
  • orthopaedic implants artificial joints, ligaments and tendons, screws, plates, and other implantable hardware
  • dental implants include, but are not restricted to, orthopaedic implants (artificial joints, ligaments and tendons, screws, plates, and other implantable hardware), dental implants, intravascular implants (particularly
  • Fibrosis refers to the formation of fibrous tissue in response to injury or medical intervention.
  • Therapeutic agents which promote also referred to interchangeably herein as “induce,” “stimulate,” “cause,” and the like) fibrosis or scarring are referred to interchangeably herein as “fibrosis-inducing agents,” “scarring agents,” “fibrosing agents,” “adhesion-inducing agents,” and the like, where these agents do so through one or more mechanisms including: inducing or promoting angiogenesis, stimulating migration or proliferation of connective tissue cells (such as fibroblasts, smooth muscle cells, vascular smooth muscle cells), inducing ECM production, and/or promoting tissue remodeling.
  • numerous therapeutic agents described in this invention can have the additional benefit of also promoting tissue regeneration (the replacement of injured cells by cells of the same type).
  • “Sclerosing” refers to a tissue reaction in which an irritant is applied locally to a tissue which results in an inflammatory reaction and is followed by scar tissue formation at the site of irritation.
  • a pharmaceutical agent that induces or promotes sclerosis is referred to as a “sclerosant,” or a “sclerosing agent.”
  • Representative examples of sclerosants include ethanol, dimethyl sulfoxide, surfactants (e.g., Triton X, sorbitan monolaurate, sorbitan sesquioleate, glycerol monostearate and polyoxyethylene, polyoxyethylene cetyl ether, etc.), sucrose, sodium chloride, dextrose, glycerin, minocycline, tetracycline, doxycycline, polidocanol, sodium tetradecyl sulfate, sodium morrhuate, ethanolamine, phenol, sarapin and sotradecol.
  • Release of an agent refers to any statistically significant presence of the agent, or a subcomponent thereof, which has disassociated from the implant/device.
  • any concentration ranges, percentage range, or ratio range recited herein are to be understood to include concentrations, percentages or ratios of any integer within that range and fractions thereof, such as one tenth and one hundredth of an integer, unless otherwise indicated.
  • any number range recited herein relating to any physical feature, such as polymer subunits, size or thickness are to be understood to include any integer within the recited range, unless otherwise indicated. It should be understood that the terms “a” and “an” as used above and elsewhere herein refer to “one or more” of the enumerated components. As used herein, the term “about” means ⁇ 15%.
  • the present invention provides compositions, methods and devices relating to medical implants, which greatly increase their ability to scar in place and incorporate into the surrounding tissue. Described in more detail below are methods for constructing medical implants, compositions and methods for generating medical implants which promote fibrosis, and methods for utilizing such medical implants.
  • Medical implants of the present invention contain and/or are adapted to release an agent which induces or promotes adhesion between the implant and tissue or a fibrotic reaction.
  • the medical implant when placed in to a tissue, releases an agent that induces or promotes adhesion between the implant and the tissue or a fibrotic reaction.
  • the medical implant contains or is made of a fibrosing agent, but does not release the fibrosing agent.
  • the fibrosing agent contained in the medical implant induces or promotes fibrosis by direct contact of the agent to the tissue where the implant is placed.
  • medical implants include: orthopaedic implants (artificial joints, ligaments and tendons, screws, plates, and other implantable hardware), dental implants, intravascular implants (particularly arterial and venous occlusion devices and implants; vascular destructive implants), male and female contraceptive or sterilization devices and implants, implantable tissue bulking agents for incontinence (esophageal, urethral, anal), soft palate implants, embolization agents, pulmonary sealants, surgical meshes (e.g., hernia repair meshes, tissue scaffolds), fistula treatments, and spinal implants (e.g., artificial intervertebral discs, spinal fusion devices, etc.).
  • orthopaedic implants artificial joints, ligaments and tendons, screws, plates, and other implantable hardware
  • dental implants include: intravascular implants (particularly arterial and venous occlusion devices and implants; vascular destructive implants), male and female contraceptive or sterilization devices and implants, implantable tissue bulking agents for incontinence (esophageal,
  • therapeutic agents also referred to herein as ‘therapeutic agents’ or ‘drugs’
  • the agent may be formulated with one or more other materials, e.g., a polymeric carrier, where formulations are discussed below.
  • a polymeric carrier e.g., polyethylene glycol
  • therapeutic agents which promote fibrosis can be identified through in vivo models such as the rat carotid artery model (Examples 17-20).
  • the fibrosis or adhesion-inducing agent is silk.
  • Silk refers to a fibrous protein, and may be obtained from a number of sources, typically spiders and silkworms. Typical silks contain about 75% of actual fiber, referred to as fibroin, and about 35% sericin, which is a gummy protein that holds the filaments together. Silk filaments are generally very fine and long—as much as 300-900 meters long. There are several species of domesticated silkworm that are used in commercial silk production, however, Bombyx mori is the most common, and most silk comes from this source.
  • silkworms include Philosamia cynthia ricini, Antheraea yamamai, Antheraea pernyi , and Antheraea mylitta .
  • Spider silk is relatively more difficult to obtain, however, recombinant techniques hold promise as a means to obtain spider silk at economical prices (see, e.g., U.S. Pat. Nos. 6,268,169; 5,994,099; 5,989,894; and 5,728,810, which are exemplary only).
  • Biotechnology has allowed researchers to develop other sources for silk production, including animals (e.g., goats) and vegetables (e.g., potatoes). Silk from any of these sources may be used in the present invention.
  • a commercially available silk protein is available from Croda, Inc., of Parsippany, N.J., and is sold under the trade names CROSILK LIQUID (silk amino acids), CROSILK 10,000 (hydrolyzed silk), CROSILK POWDER (powdered silk), and CROSILKQUAT (cocodiammonium hydroxypropyl silk amino acid).
  • CROSILK LIQUID sik amino acids
  • CROSILK 10,000 hydrolyzed silk
  • CROSILK POWDER powdered silk
  • CROSILKQUAT cocodiammonium hydroxypropyl silk amino acid
  • SERICIN available from Pentapharm, LTD, a division of Kordia, BV, of the Netherlands. Further details of such silk protein mixtures can be found in U.S. Pat. No. 4,906,460, to Kim, et al., assigned to Sorenco.
  • Silk useful in the present invention includes natural (raw) silk, hydrolyzed silk, and modified silk, i.e., silk that has undergone a chemical, mechanical, or vapor treatment, e.g., acid treatment or acylation (see, e.g., U.S. Pat. No. 5,747,015).
  • a chemical, mechanical, or vapor treatment e.g., acid treatment or acylation
  • Raw silk is typically twisted into a strand sufficiently strong for weaving or knitting.
  • Four different types of silk thread may be produced by this procedure: organzine, crepe, tram and thrown singles.
  • Organzine is a thread made by giving the raw silk a preliminary twist in one direction and then twisting two of these threads together in the opposite direction.
  • Crepe is similar to organzine but is twisted to a much greater extent. Twisting in only one direction two or more raw silk threads makes tram. Thrown singles are individual raw silk threads that are twisted in only one direction. Any of these types of silk threads may be used in the present invention.
  • the silk used in the present invention may be in any suitable form that allows the silk to be joined with the medical implant, e.g., the silk may be in thread or powder-based forms.
  • the silk can be prepared in the powdered form by several different methods. For example the silk can be milled (e.g., cryomill) into a powdered form. Alternatively the silk can be dissolved in a suitable solvent (e.g., HFIP or 9M LiBr) and then sprayed (electrospray, spray dry) or added to a non-solvent to produce a powder.
  • a suitable solvent e.g., HFIP or 9M LiBr
  • the silk may have any molecular weight, where various molecular weights are typically obtained by the hydrolysis of natural silk, where the extent and harshness of the hydrolysis conditions determines the product molecular weight.
  • the silk may have an average (number or weight) molecular weight of about 200 to 5,000. See, e.g., JP-B-59-29199 (examined Japanese patent publication) for a description of conditions that may be used to hydrolyze silk.
  • fibrosis and adhesion-inducing agents include irritants (e.g., talc, talcum powder, copper, metallic beryllium (or its oxides), wool (e.g., animal wool, wood wolol, and synthetic wool), quartz dust, silica, crystalline silicates), polymers (e.g., polylysine, polyurethanes, poly(ethylene terephthalate), polytetrafluoroethylene (PTFE), poly(alkylcyanoacrylates), and poly(ethylene-co-vinylacetate)); vinyl chloride and polymers of vinyl chloride; peptides with high lysine content; growth factors and inflammatory cytokines involved in angiogenesis, fibroblast migration, fibroblast proliferation, ECM synthesis and tissue remodeling, such as epidermal growth factor (EGF) family, transforming growth factor- ⁇ (TGF- ⁇ ), transforming growth factor- ⁇ (TGF-9-1, TGF-9-2, TGF-9-3, platelet-derived growth factor
  • CTGF connective tissue growth factor
  • inflammatory microcrystals e.g., crystalline minerals such as crystalline silicates
  • bromocriptine methylsergide, methotrexate, chitosan, N-carboxybutyl chitosan, carbon tetrachloride, thioacetamide, fibrosin, ethanol, bleomycin, naturally occurring or synthetic peptides containing the Arg-Gly-Asp (RGD) sequence, generally at one or both termini (see e.g., U.S. Pat. No.
  • fibrosis-inducing agents include bone morphogenic proteins (e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6 (Vgr-1), BMP-7 (OP-1), BMP-8, BMP-9, BMP-10, BMP-11, BMP-12, BMP-13, BMP-14, BMP-15, and BMP-16.
  • BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, and BMP-7 are of particular utility.
  • Bone morphogenic proteins are described, for example, in U.S. Pat. Nos.
  • fibrosis-inducing agents include crosslinked compositions that comprise amino-functional groups.
  • amino-functionalized polyethylene glycol e.g., 4-armed tetra-amino PEG [10k]
  • a 4-armed NHS functionalized PEG e.g., pentaerythritol poly(ethylene glycol)ether tetra-succinimidyl glutarate
  • a 4-armed thiol functionalized PEG e.g., pentaerythritol poly(ethylene glycol)ether tetra-thiol
  • pentaerythritol poly(ethylene glycol)ether tetra-thiol can be substituted for the 4-arm amino-functionalized PEG such that the amount of amino functional groups in the final composition can be varied.
  • These reagents can be mixed at the time of application to provide an in situ forming crosslinked hydrogel.
  • These reagents could be premixed to produce the crosslinked material.
  • the material can be made in various forms such as rods, tubes, films, slabs or spheres.
  • the crosslinked material could also be milled to produce a particulate material.
  • These materials can be dried (e.g., air, vacuum, freeze-dried) and used as a dry powdered material. Alternatively the materials can be hydrated just prior to application. These materials can further comprise one of the fibrosis-inducing agents described herein.
  • fibrosis-inducing agents include components of extracellular matrix (e.g., fibronectin, fibrin, fibrinogen, collagen (e.g., bovine collagen), fibrillar and non-fibrillar collagen, adhesive glycoproteins, proteoglycans (e.g., heparin sulfate, chondroitin sulfate, dermatan sulfate), hyaluronan, secreted protein acidic and rich in cysteine (SPARC), thrombospondins, tenacin, and cell adhesion molecules (including integrins, vitronectin, fibronectin, laminin, hyaluronic acid, elastin, bitronectin), proteins found in basement membranes, and fibrosin) and inhibitors of matrix metalloproteinases, such as TIMPs (tissue inhibitors of matrix metalloproteinases) and synthetic TIMPs, e.g., marimistat, batimistat,
  • a device is coated with a first composition that promotes fibrosis (and/or restenosis) and a second composition or compound which acts to have an inhibitory effect on pathological processes in or around the treatment site.
  • agents which can inhibit pathological processes in the treatment site include, but not limited to, the following classes of compounds: anti-inflammatory agents (e.g., dexamethasone, cortisone, fludrocortisone, prednisone, prednisolone, 6 ⁇ -methylprednisolone, triamcinolone, and betamethasone); Matrix Metalloproteinase (MMP) inhibitors (e.g., marimistat, batimistat, TIMP's representative examples of which are included in U.S.
  • MMP Matrix Metalloproteinase
  • WO 00/63204A2 WO 01/21591A1, WO 01/35959A1, WO 01/74811A2, WO 02/18379A2, WO 02/064594A2, WO 02/083622A2, WO 02/094842A2, WO 02/096426A1, WO 02/101015A2, WO 02/103000A2, WO 03/008413A1, WO 03/016248A2, WO 03/020715A1, WO 03/024899A2, WO 03/031431A1, WO 03/040103A1, WO 03/053940A1, WO 03/053941A2, WO 03/063799A2, WO 03/079986A2, WO 03/080024A2, WO 03/082287A1, WO 97/44467A1, WO 99/01449A1, and WO 99/58523A1), and immunomodulatory agents (rapamycin, everolimus, ABT-578, azathioprine azi
  • tyrosine kinase inhibitors such as imantinib, ZK-222584, CGP-52411, CGP-53716, NVP-MK980-NX, CP-127374, CP-564959, PD-171026, PD-173956, PD-180970, SU-0879, and SKI-606.
  • MMP inhibitors such as nimesulide, PKF-241-466, PKF-242-484, CGS-27023A, SAR-943, primomastat, SC-77964, PNU-171829, AG-3433, PNU-142769, SU-5402, and dexlipotam.
  • p38 MAP kinase inhibitors such as CGH-2466 and PD-98-59.
  • cytokine inhibitors include TNF-484A, PD-172084, CP-293121, CP-353164, and PD-168787.
  • drugs that may be included in the compositions and devices of the invention include include NFKB inhibitors, such as, AVE-0547, AVE-0545, and IPL-576092.
  • HMGCoA reductase inhibitors such as, pravestatin, atorvastatin, fluvastatin, dalvastatin, glenvastatin, pitavastatin, CP-83101, U-20685
  • a device incorporates or is coated with a composition which promotes fibrosis (and/or restenosis), as well as a composition or compound which acts to stimulate cellular proliferation.
  • agents that stimulate cellular proliferation include, pyruvic acid, naltrexone, leptin, D-glucose, insulin, amlodipine, alginate oligosaccharides, minoxidil, dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME (L-NG-nitroarginine methyl ester (hydrochloride)), all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • agents that stimulate cellular proliferation include: sphingosine 1-phosphate receptor agonist (e.g., FTY-720 (1,3-propanediol, 2-amino-2-(2-(4-octylphenyl)ethyl)-, hydrochloride; immunostimulants, such as Imupedone (methanone, [5-amino-2-(4-methyl-1-piperidinyl)phenyl](4-chlorophenyl)-, DIAPEP227 synthetic peptide (Peptor Ltd., Israel)); and nerve growth factor agonist, e.g., NG-012 (5H,9H,13H,21H,25H,-dibenzo[k,u][1,5,9,15,19]pentaoxacyclotetracosin-5,9,13,21,25-pentone, 7,8,11,12,15,16,23,24,27,28-decahydro-2,4,18,20-
  • a device incorporates or is coated on one aspect with a composition which promotes fibrosis (and/or restenosis), as well as with a composition or compound which prevents restenosis on another aspect of the device.
  • agents that inhibit restenosis include paclitaxel, sirolimus, everolimus, vincristine, biolimus, mycophenolic acid, ABT-578, cervistatin, simvastatin, methylprednisolone, dexamethasone, actinomycin-D, angiopeptin, L-arginine, estradiol, 17- ⁇ -estradiol, tranilast, methotrexate, batimistat, halofuginone, BCP-671, QP-2, lantrunculin D, cytochalasin A, nitric oxide, and analogues and derivatives thereof.
  • the medical implant may include a fibrosing agent and an anti-thrombotic agent and/or antiplatelet agent, which reduces the likelihood of thrombotic events upon implantation of a medical implant.
  • a device is coated on one aspect with a composition which promotes fibrosis (and/or restenosis), as well as being coated with a composition or compound which prevents thrombosis on another aspect of the device.
  • anti-thrombotic and/or antiplatelet agents include heparin, heparin fragments, organic salts of heparin, heparin complexes (e.g., benzalkonium heparinate, tridodecylammonium heparinate), dextran, sulfonated carbohydrates such as dextran sulphate, coumadin, coumarin, heparinoid, danaparoid, argatroban chitosan sulfate, chondroitin sulfate, danaparoid, lepirudin, hirudin, AMP, adenosine, 2-chloroadenosine, aspirin, phenylbutazone, indomethacin, meclofenamate, hydrochloroquine, dipyridamole, iloprost, streptokinase, and factor Xa inhibitors, such as DX9065a, magnesium, and tissue plasminogen
  • the anti-thrombotic agent is a modified heparin compound, such as a hydrophobically modified heparin or modified hirudin compound (e.g., stearylkonium heparin, benzalkonium heparin, cetylkonium heparin, or trdodecylmethyl ammonium heparin).
  • modified heparin compounds such as a hydrophobically modified heparin or modified hirudin compound (e.g., stearylkonium heparin, benzalkonium heparin, cetylkonium heparin, or trdodecylmethyl ammonium heparin).
  • anti-thrombotic agents include plasminogen, lys-plasminogen, alpha-2-antiplasmin, urokinase, ticlopidine, clopidogrel, glycoprotein IIb/IIIa inhibitors such as abcixamab, eptifibatide, and
  • agents capable of affecting the rate of clotting include glycosaminoglycans, danaparoid, 4-hydroxycourmarin, warfarin sodium, dicumarol, phenprocoumon, indan-1,3-dione, acenocoumarol, anisindione, and rodenticides including bromadiolone, brodifacoum, diphenadione, chlorophacinone, and pidnone.
  • the thrombogenicity of a medical implant may be reduced by coating the implant with a polymeric formulation that has anti-thrombogenic properties.
  • a medical device may be coated with a hydrophilic polymer gel.
  • the polymer gel can comprise a hydrophilic, biodegradable polymer that is physically removed from the surface of the device over time, thus reducing adhesion of platelets to the device surface.
  • the gel composition can include a polymer or a blend of polymers. Representative examples include alginates, chitosan and chitosan sulfate, hyaluronic acid, dextran sulfate, PLURONIC polymers (e.g., F-127 or F87) and chain extended PLURONIC polymers (BASF Corporation, Mt.
  • the anti-thrombotic composition can include a crosslinked gel formed from a combination of molecules (e.g., PEG) having two or more terminal electrophilic groups and two or more nucleophilic groups.
  • the present invention also provides for the combination of a medical implant (as well as compositions and methods for making medical implants) that includes a fibrosing agent and an anti-infective agent, which reduces the likelihood of infections in medical implants.
  • Infection is a common complication of the implantation of foreign bodies such as medical devices.
  • Foreign materials provide an ideal site for micro-organisms to attach and colonize. It is also hypothesized that there is an impairment of host defenses to infection in the microenvironment surrounding a foreign material. These factors make medical implants particularly susceptible to infection and make eradication of such an infection difficult, if not impossible, in most cases.
  • the present invention provides agents (e.g., chemotherapeutic agents) that can be incorporated onto or into, or released from, an implantable device, and which have potent antimicrobial activity at extremely low doses.
  • agents e.g., chemotherapeutic agents
  • a wide variety of anti-infective agents can be utilized in combination with a fibrosing agent according to the invention.
  • Chemotehrapeutic/anti-infective agents that can be used: (A) anthracyclines (e.g., doxorubicin and mitoxantrone), (B) fluoropyrimidines (e.g., 5-FU), (C) folic acid antagonists (e.g., methotrexate), (D) podophylotoxins (e.g., etoposide), (E) camptothecins, (F) hydroxyureas, and (G) platinum complexes (e.g., cisplatin).
  • anthracyclines e.g., doxorubicin and mitoxantrone
  • fluoropyrimidines e.g., 5-FU
  • C folic acid antagonists (e.g., methotrexate)
  • D podophylotoxins
  • E camptothecins
  • F hydroxyureas
  • platinum complexes e.g., cisp
  • Anthracyclines have the following general structure, where the R groups may be a variety of organic groups:
  • R 1 is CH 3 or CH 2 OH
  • R 2 is daunosamine or H
  • R 3 and R 4 are independently one of OH, NO 2 , NH 2 , F, Cl, Br, I, CN, H or groups derived from these
  • R 5 is hydrogen, hydroxyl, or methoxy
  • R 6-8 are all hydrogen.
  • R 5 and R 6 are hydrogen and R 7 and R 8 are alkyl or halogen, or vice versa.
  • R 1 may be a conjugated peptide.
  • R 5 may be an ether linked alkyl group.
  • R 5 may be OH or an ether linked alkyl group.
  • R 1 may also be linked to the anthracycline ring by a group other than C(O), such as an alkyl or branched alkyl group having the C(O) linking moiety at its end, such as —CH 2 CH(CH 2 —X)C(O)—R 1 , wherein X is H or an alkyl group (see, e.g., U.S. Pat. No.
  • R 2 may alternately be a group linked by the functional group ⁇ N—NHC(O)—Y, where Y is a group such as a phenyl or substituted phenyl ring.
  • R 3 may have the following structure: in which R 9 is OH either in or out of the plane of the ring, or is a second sugar moiety such as R 3 .
  • R 10 may be H or form a secondary amine with a group such as an aromatic group, saturated or partially saturated 5 or 6 membered heterocyclic having at least one ring nitrogen (see U.S. Pat. No. 5,843,903).
  • R 10 may be derived from an amino acid, having the structure —C(O)CH(NHR 11 )(R 12 ), in which R 11 is H, or forms a C 3-4 membered alkylene with R 12 .
  • R 12 may be H, alkyl, aminoalkyl, amino, hydroxyl, mercapto, phenyl, benzyl or methylthio (see U.S. Pat. No. 4,296,105).
  • anthracyclines are doxorubicin, daunorubicin, idarubicin, epirubicin, pirarubicin, zorubicin, and carubicin.
  • Suitable compounds have the structures: R 1 R 2 R 3 Doxorubicin: OCH 3 C(O)CH 2 OH OH out of ring plane Epirubicin: OCH 3 C(O)CH 2 OH OH in ring plane (4′ epimer of doxorubicin) Daunorubicin: OCH 3 C(O)CH 3 OH out of ring plane Idarubicin: H C(O)CH 3 OH out of ring plane Pirarubicin: OCH 3 C(O)CH 2 OH Zorubicin: OCH 3 C(CH 3 )( ⁇ N)NHC(O)C 6 H 5 OH Carubicin: OH C(O)CH 3 OH out of ring plane
  • anthracyclines are anthramycin, mitoxantrone, menogaril, nogalamycin, aclacinomycin A, olivomycin A, chromomycin A 3 , and plicamycin having the structures: R 1 R 2 R 3 Menogaril H OCH 3 H Nogalamycin O-sugar H COOCH 3 R 1 R 2 R 3 R 4 Olivomycin A COCH(CH 3 ) 2 CH 3 COCH 3 H Chromomycin A 3 COCH 3 CH 3 COCH 3 CH 3 Plicamycin H H H CH 3
  • anthracyclines include, FCE 23762, a doxorubicin derivative (Quaglia et al., J. Liq. Chromatogr. 17(18): 3911-3923, 1994), annamycin (Zou et al., J. Pharm. Sci. 82(11): 1151-1154, 1993), ruboxyl (Rapoport et al., J. Controlled Release 58(2): 153-162, 1999), anthracycline disaccharide doxorubicin analogue (Pratesi et al., Clin. Cancer Res.
  • the therapeutic agent is a fluoropyrimidine analog, such as 5-fluorouracil, or an analogue or derivative thereof, including carmofur, doxifluridine, emitefur, tegafur, and floxuridine.
  • fluoropyrimidine analog such as 5-fluorouracil
  • an analogue or derivative thereof including carmofur, doxifluridine, emitefur, tegafur, and floxuridine.
  • Exemplary compounds have the structures: A R 1 R 2 5-Fluorouracil H H H Carmofur C(O)NH(CH 2 ) 5 CH 3 H Doxifluridine A 1 H Floxuridine A 2 H Emitefur CH 2 OCH 2 CH 3 B Tegafur C H B C
  • fluoropyrimidine analogues include 5-FudR (5-fluoro-deoxyuridine), or an analogue or derivative thereof, including 5-iododeoxyuridine (5-ludR), 5-bromodeoxyuridine (5-BudR), fluorouridine triphosphate (5-FUTP), and fluorodeoxyuridine monophosphate (5-dFUMP).
  • fluoropyrimidine analogues include N3-alkylated analogues of 5-fluorouracil (Kozai et al., J. Chem. Soc., Perkin Trans. 1(19): 3145-3146, 1998), 5-fluorouracil derivatives with 1,4-oxaheteroepane moieties (Gomez et al., Tetrahedron 54(43): 13295-13312, 1998), 5-fluorouracil and nucleoside analogues (Li, Anticancer Res.
  • the therapeutic agent is a folic acid antagonist, such as methotrexate or derivatives or analogues thereof, including edatrexate, trimetrexate, raltitrexed, piritrexim, denopterin, tomudex, and pteropterin.
  • Methotrexate analogues have the following general structure: The identity of the R group may be selected from organic groups, particularly those groups set forth in U.S. Pat. Nos. 5,166,149 and 5,382,582.
  • R 1 may be N
  • R 2 may be N or C(CH 3 )
  • R 3 and R 3 ′ may H or alkyl, e.g., CH 3
  • R 4 may be a single bond or NR, where R is H or alkyl group.
  • R 5 , R 6 , and/or R 8 may be H, OCH 3 , or alternately they can be halogens or hydro groups.
  • R 9 and R 10 can be NH 2 or may be alkyl substituted.
  • N-( ⁇ -aminoacyl)methotrexate derivatives Cheung et al., Pteridines 3(1-2): 101-2, 1992
  • biotin methotrexate derivatives Fean et al., Pteridines 3(1-2): 131-2, 1992
  • D-glutamic acid or D-erythrou threo-4-fluoroglutamic acid methotrexate analogues
  • Pteridines Folic Acid Deriv., 1154-7, 1989 N-(L- ⁇ -aminoacyl)methotrexate derivatives (Cheung et al., Heterocycles 28(2): 751-8, 1989), meta and ortho isomers of aminopterin (Rosowsky et al., J. Med. Chem. 32(12): 2582, 1989), hydroxymethylmethotrexate (DE 267495), ⁇ -fluoromethotrexate (McGuire et al., Cancer Res. 49(16): 4517-25, 1989), polyglutamyl methotrexate derivatives (Kumar et al., Cancer Res.
  • the therapeutic agent is a Podophyllotoxin, or a derivative or an analogue thereof.
  • exemplary compounds of this type are etoposide or teniposide, which have the following structures:
  • podophyllotoxins include Cu(II)-VP-16 (etoposide) complex (Tawa et al., Bioorg. Med. Chem. 6(7): 1003-1008, 1998), pyrrolecarboxamidino-bearing etoposide analogues (Ji et al., Bioorg. Med. Chem. Lett. 7(5): 607-612, 1997), 4 ⁇ -amino etoposide analogues (Hu, University of North Carolina Dissertation, 1992), ⁇ -lactone ring-modified arylamino etoposide analogues (Zhou et al., J. Med. Chem.
  • the therapeutic agent is camptothecin, or an analogue or derivative thereof.
  • Camptothecins have the following general structure.
  • X is typically 0, but can be other groups, e.g., NH in the case of 21-lactam derivatives.
  • R 1 is typically H or OH, but may be other groups, e.g., a terminally hydroxylated C 1-3 alkane.
  • R 2 is typically H or an amino containing group such as (CH 3 ) 2 NHCH 2 , but may be other groups e.g., NO 2 , NH 2 , halogen (as disclosed in, e.g., U.S. Pat. No. 5,552,156) or a short alkane containing these groups.
  • R 3 is typically H or a short alkyl such as C 2 H 5 .
  • R 4 is typically H but may be other groups, e.g., a methylenedioxy group with R 1 .
  • camptothecin compounds include topotecan, irinotecan (CPT-11), 9-aminocamptothecin, 21-lactam-20(S)-camptothecin, 10,11-methylenedioxycamptothecin, SN-38, 9-nitrocamptothecin, 10-hydroxycamptothecin.
  • Exemplary compounds have the structures: R 1 R 2 R 3 Camptothecin: H H H Topotecan: OH (CH 3 ) 2 NHCH 2 H SN-38: OH H C 2 H 5 X: O for most analogs, NH for 21-lactam analogs
  • Camptothecins have the five rings shown here.
  • the ring labeled E must be intact (the lactone rather than carboxylate form) for maximum activity and minimum toxicity.
  • Camptothecins are believed to function as topoisomerase I inhibitors and/or DNA cleavage agents.
  • the therapeutic agent of the present invention may be a hydroxyurea.
  • Hydroxyureas have the following general structure:
  • Suitable hydroxyureas are disclosed in, for example, U.S. Pat. No. 6,080,874, wherein R 1 is: and R 2 is an alkyl group having 1-4 carbons and R 3 is one of H, acyl, methyl, ethyl, and mixtures thereof, such as a methylether.
  • R 1 is a cycloalkenyl group, for example N-[3-[5-(4-fluorophenylthio)-furyl]-2-cyclopenten-1-yl]N-hydroxyurea
  • R 2 is H or an alkyl group having 1 to 4 carbons and R 3 is H
  • X is H or a cation.
  • Suitable hydroxyureas are disclosed in, e.g., U.S. Pat. No. 4,299,778, wherein R 1 is a phenyl group substituted with one or more fluorine atoms; R 2 is a cyclopropyl group; and R 3 and X is H.
  • the hydroxyurea has the structure:
  • the therapeutic agent is a platinum compound.
  • suitable platinum complexes may be of Pt(II) or Pt(IV) and have this basic structure: wherein X and Y are anionic leaving groups such as sulfate, phosphate, carboxylate, and halogen; R 1 and R 2 are alkyl, amine, amino alkyl may be further substituted, and are basically inert or bridging groups.
  • X and Y are anionic leaving groups such as sulfate, phosphate, carboxylate, and halogen
  • R 1 and R 2 are alkyl, amine, amino alkyl may be further substituted, and are basically inert or bridging groups.
  • Z 1 and Z 2 are non-existent.
  • Z 1 and Z 2 may be anionic groups such as halogen, hydroxy, carboxylate, ester, sulfate or phosphate. See, e.g., U.S. Pat. Nos. 4,588,831 and 4,250,189.
  • Suitable platinum complexes may contain multiple Pt atoms. See, e.g., U.S. Pat. Nos. 5,409,915 and 5,380,897.
  • platinum compounds are cisplatin, carboplatin, oxaliplatin, and miboplatin having the structures:
  • platinum compounds include (CPA) 2 Pt[DOLYM] and (DACH)Pt[DOLYM] cisplatin (Choi et al., Arch. Pharmacal Res. 22(2): 151-156, 1999), Cis-[PtCl 2 (4,7-H-5-methyl-7-oxo]1,2,4[triazolo[1,5-a]pyrimidine) 2 ] (Navarro et al., J. Med. Chem. 41(3): 332-338, 1998), [Pt(cis-1,4-DACH)(trans-C[ 2 )(CBDCA)]. ⁇ fraction (1/2) ⁇ MeOH cisplatin (Shamsuddin et al., Inorg. Chem.
  • Drug dose can be calculated as a function of dose per unit area (of the portion of the device being coated), total drug dose administered can be measured and appropriate surface concentrations of active drug can be determined.
  • the preferred anticancer/anti-infective agents used alone or in combination, should be administered under the following dosing guidelines:
  • anthracyclines Utilizing the anthracycline doxorubicin as an example, whether applied as a polymer coating, incorporated into the polymers which make up the implant components, or applied without a carrier polymer, the total dose of doxorubicin applied to the implant should not exceed 25 mg (range of 0.1 ⁇ g to 25 mg). In a particularly preferred embodiment, the total amount of drug applied should be in the range of 1 ⁇ g to 5 mg.
  • the dose per unit area i.e., the amount of drug as a function of the surface area of the portion of the implant to which drug is applied and/or incorporated
  • doxorubicin should be applied to the implant surface at a dose of 0.1 ⁇ g/mm 2 -10 ⁇ g/mm 2 .
  • the above dosing parameters should be utilized in combination with the release rate of the drug from the implant surface such that a minimum concentration of 10 ⁇ 7 -10 ⁇ 4 M of doxorubicin is maintained on the surface. It is necessary to insure that surface drug concentrations exceed concentrations of doxorubicin known to be lethal to multiple species of bacteria and fungi (i.e., are in excess of 10 ⁇ 4 M; although for some embodiments lower concentrations are sufficient).
  • doxorubicin is released from the surface of the implant such that anti-infective activity is maintained for a period ranging from several hours to several months.
  • the drug is released in effective concentrations for a period ranging from 1 week-6 months.
  • analogues and derivatives of doxorubicin (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as doxorubicin is administered at half the above parameters, a compound half as potent as doxorubicin is administered at twice the above parameters, etc.).
  • the total dose of mitoxantrone applied should not exceed 5 mg (range of 0.01 ⁇ g to 5 mg).
  • the total amount of drug applied should be in the range of 0.1 ⁇ g to 1 mg.
  • the dose per unit area i.e., the amount of drug as a function of the surface area of the portion of the implant to which drug is applied and/or incorporated
  • mitoxantrone should be applied to the implant surface at a dose of 0.05 ⁇ g/mm 2 -3 ⁇ g/mm 2 .
  • the above dosing parameters should be utilized in combination with the release rate of the drug from the implant surface such that a minimum concentration of 10 ⁇ 5 -10 ⁇ 6 M of mitoxantrone is maintained. It is necessary to insure that drug concentrations on the implant surface exceed concentrations of mitoxantrone known to be lethal to multiple species of bacteria and fungi (i.e., are in excess of 10 ⁇ 5 M; although for some embodiments lower drug levels will be sufficient).
  • mitoxantrone is released from the surface of the implant such that anti-infective activity is maintained for a period ranging from several hours to several months.
  • the drug is released in effective concentrations for a period ranging from 1 week-6 months.
  • analogues and derivatives of mitoxantrone (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as mitoxantrone is administered at half the above parameters, a compound half as potent as mitoxantrone is administered at twice the above parameters, etc.).
  • the total dose of 5-fluorouracil applied should not exceed 250 mg (range of 1.0 ⁇ g to 250 mg). In a particularly preferred embodiment, the total amount of drug applied should be in the range of 10 ⁇ g to 25 mg.
  • the dose per unit area i.e., the amount of drug as a function of the surface area of the portion of the implant to which drug is applied and/or incorporated should fall within the range of 0.1 ⁇ g-1 mg per mm 2 of surface area.
  • 5-fluorouracil should be applied to the implant surface at a dose of 1.0 ⁇ g/mm 2 -50 ⁇ g/mm 2 .
  • the above dosing parameters should be utilized in combination with the release rate of the drug from the implant surface such that a minimum concentration of 10 ⁇ 4 -10 ⁇ 7 M of 5-fluorouracil is maintained. It is necessary to insure that surface drug concentrations exceed concentrations of 5-fluorouracil known to be lethal to numerous species of bacteria and fungi (i.e., are in excess of 10 ⁇ 4 M; although for some embodiments lower drug levels will be sufficient).
  • 5-fluorouracil is released from the implant surface such that anti-infective activity is maintained for a period ranging from several hours to several months.
  • the drug is released in effective concentrations for a period ranging from 1 week-6 months.
  • analogues and derivatives of 5-fluorouracil (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as 5-fluorouracil is administered at half the above parameters, a compound half as potent as 5-fluorouracil is administered at twice the above parameters, etc.).
  • the total dose of etoposide applied should not exceed 25 mg (range of 0.1 ⁇ g to 25 mg). In a particularly preferred embodiment, the total amount of drug applied should be in the range of 1 ⁇ g to 5 mg.
  • the dose per unit area i.e., the amount of drug as a function of the surface area of the portion of the implant to which drug is applied and/or incorporated should fall within the range of 0.01 ⁇ g-100 ⁇ g per mm 2 of surface area.
  • etoposide should be applied to the implant surface at a dose of 0.1 ⁇ g/mm 2 -10 ⁇ g/mm 2 .
  • the above dosing parameters should be utilized in combination with the release rate of the drug from the implant surface such that a concentration of 10 ⁇ 5 -10 ⁇ 6 M of etoposide is maintained. It is necessary to insure that surface drug concentrations exceed concentrations of etoposide known to be lethal to a variety of bacteria and fungi (i.e., are in excess of 10 ⁇ 5 M; although for some embodiments lower drug levels will be sufficient).
  • etoposide is released from the surface of the implant such that anti-infective activity is maintained for a period ranging from several hours to several months.
  • the drug is released in effective concentrations for a period ranging from 1 week-6 months.
  • analogues and derivatives of etoposide (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as etoposide is administered at half the above parameters, a compound half as potent as etoposide is administered at twice the above parameters, etc.).
  • anthracyclines e.g., doxorubicin or mitoxantrone
  • fluoropyrimidines e.g., 5-fluorouracil
  • folic acid antagonists e.g., methotrexate and/or podophylotoxins (e.g., etoposide)
  • traditional antibiotic and/or antifungal agents to enhance efficacy.
  • the anti-infective agent may be further combined with antithrombotic and/or antiplatelet agents (for example, heparin, dextran sulphate, danaparoid, lepirudin, hirudin, AMP, adenosine, 2-chloroadenosine, aspirin, phenylbutazone, indomethacin, meclofenamate, hydrochloroquine, dipyridamole, iloprost, ticlopidine, clopidogrel, abcixamab, eptifibatide, tirofiban, streptokinase, and/or tissue plasminogen activator) to enhance efficacy.
  • antithrombotic and/or antiplatelet agents for example, heparin, dextran sulphate, danaparoid, lepirudin, hirudin, AMP, adenosine, 2-chloroadenosine, aspirin, phenylbutazone, in
  • fibrosis is induced by local or systemic release of specific pharmacological agents that become localized to the tissue adjacent to the device or implant.
  • Medical devices or implants of the present invention contain and/or are adapted to release an agent which induces fibrosis or adhesion to the surrounding tissue.
  • Medical devices or implants may be adapted to have incorporated into their structure a fibrosis-inducing agent, adapted to have a surface coating of a fibrosis-inducing agent and/or adapted to release a fibrosis-inducing agent by (a) directly affixing to the implant or device a desired fibrosis-inducing agent or composition containing the fibrosis-inducing agent (e.g., by either spraying the medical implant with a drug and/or carrier (polymeric or non-polymeric)-drug composition to create a film or coating on all, or parts of the internal or external surface of the device; by dipping the implant or device into a drug and/or carrier (polymeric or non-polymeric)-drug solution to coat all or parts of the device or implant; or by other covalent or non-covalent (e.
  • a medical device may be modified by attaching fibers (threads) to the surface of the device.
  • the fibers may be polymeric and/or may be formed of or coated with a fibrosing material, such as silk.
  • the threads may be formed from a silk suture material. The presence of the threads can result in an enhanced cellular and/or extracellular matrix response to the exterior of the device.
  • the threads can be attached to the device by using any one or a combination of the following methods, including use of an adhesive, thermal welding, stitching, wrapping, weaving, knotting, and the like.
  • the threads can be coated with a material that delays the time it takes for the thread material to come into contact with the surrounding tissue and blood, thus allowing placement of the device without concern of thrombotic events due to the presence of the polymeric threads.
  • materials that can be used to prepare coatings capable of degrading or dissolving upon implantation include gelatin, polyesters (e.g., PLGA, PLA, MePEG-PLGA, PLGA-PEG-PLGA, and blends thereof), lipids, fatty acids, sugar esters, nucleic acid esters, polyanhydrides, polyorthoesters, and PVA.
  • the coating may further contain a fibrosing agent and/or a biologically active agent that may, for example, reduce the probability of an immediate thrombotic event (e.g., heparin, hydrophobic quaternary amine heparin complexes, and the like).
  • a fibrosing agent e.g., heparin, hydrophobic quaternary amine heparin complexes, and the like.
  • all or a portion of the device may be coated with a polymeric carrier that contains a fibrosis-inducing agent.
  • the fibers may further comprise a coating or composition that is affected by an applied magnetic field.
  • a device such as a stent graft may be coated with polymeric threads that are coated, contain, or are formed from a fibrosing agent (e.g., silk suture).
  • a magnetic field can be applied to the coated device to orient and align the polymeric fibers relative to each other and the surface of the device to increase the surface area of the fibers exposed to biological mediators which would stimulate a fibrotic reaction.
  • the magnetically active component can be associated with the polymeric fiber using a variety of methods.
  • the magnetically active component may be incorporated during manufacture of the fiber, for example, by incorporating a magnetically active material such as magnetite into a polymer feed prior to extrusion of the polymeric fiber.
  • the magnetically active component can be coated onto the entire fiber or a portion of the fiber using, for example, an adhesive or a polymeric coating.
  • the polymeric fiber (or a portion thereof) can be heated or plasticized with a solvent and then rolled in the magnetically active component, such that the magnetic material protrudes above the surface of the fiber or is embedded into the surface of the fiber.
  • the threads may be attached to the device in various configurations that can result in either partial or complete coverage of the exterior of the device.
  • the polymeric threads may be affixed to the ends of a device or to the central portion of a device, and the attachment may be in a vertical, horizontal, or diagonal manner.
  • a variety of drug-delivery technologies are available for systemic, regional and local delivery of therapeutic agents.
  • Several of these techniques may be suitable to achieve preferentially elevated levels of fibrosis-inducing agents in the vicinity of the medical device or implant, including: (a) using drug-delivery catheters for local, regional or systemic delivery of fibrosing agents to the tissue surrounding the device or implant (typically, drug delivery catheters are advanced through the circulation or inserted directly into tissues under radiological guidance until they reach the desired anatomical location; the fibrosing agent can then be released from the catheter lumen in high local concentrations in order to deliver therapeutic doses of the drug to the tissue surrounding the device or implant); (b) drug localization techniques such as magnetic, ultrasonic or MRI-guided drug delivery; (c) chemical modification of the fibrosis-inducing drug or formulation designed to increase uptake of the agent into damaged tissues (e.g., modification of the drug or formulation to include antibodies directed against damaged or healing tissue components such as macrophages, neutrophils, smooth muscle cells,
  • the tissue cavity into which the device or implant is placed can be treated with a fibrosis-inducing agent prior to, during, or after the implantation procedure.
  • a fibrosis-inducing agent prior to, during, or after the implantation procedure.
  • This can be accomplished in several ways including: (a) topical application of the fibrosing agent into the anatomical space where the device can be placed (particularly useful for this embodiment is the use of polymeric carriers which release the fibrosing agent over a period ranging from several hours to several weeks—fluids, suspensions, emulsions, microemulsions, microspheres, pastes, gels, microparticulates, sprays, aerosols, solid implants and other formulations which release a fibrosing agent can be delivered into the region where the device or implant can be inserted via specialized delivery catheters or other applicators); (b) microparticulate silk and/or silk strands (e.g., linear, branched, and/or coiled) are also useful
  • the fibrosis-inducing agent may be delivered as a solution.
  • the fibrosis-inducing agent can be incorporated directly into the solution to provide a homogeneous solution or dispersion.
  • the solution is an aqueous solution.
  • the aqueous solution may further include buffer salts, as well as viscosity modifying agents (e.g., hyaluronic acid, alginates, CMC, and the like).
  • the solution can include a biocompatible solvent, such as ethanol, DMSO, glycerol, PEG-200, PEG-300 or NMP.
  • the fibrosis-inducing agent can be incorporated or coated onto the device.
  • a desired fibrosis-inducing agent may be admixed with, blended with, conjugated to, or, otherwise modified to contain a polymeric composition (which may be either biodegradable or non-biodegradable) or non-polymeric composition.
  • the polymeric or non-polymeric composition i.e., carrier
  • the localized sustained delivery of the fibrosis inhibiting agent may be required.
  • a desired fibrosis-inducing agent may be admixed with, blended with, conjugated to, or, otherwise modified to contain a polymeric composition (which may be either biodegradable or non-biodegradable) or non-polymeric composition in order to release the fibrosis-inducing agent over a period of time.
  • a polymeric composition which may be either biodegradable or non-biodegradable
  • biodegradable and non-biodegradable polymers, polymer conjugates as well as non-polymeric materials can be used to accomplish the incorporation of the fibrosis-inducing agent onto or into the device.
  • biodegradable polymers suitable for the delivery of fibrosis-inducing agents include albumin, collagen, gelatin, hyaluronic acid, starch, cellulose and cellulose derivatives (e.g., methylcellulose, hydroxypropylcellulose, hydroxypropylmethylcellulose, carboxymethylcellulose, cellulose acetate phthalate, cellulose acetate succinate, hydroxypropylmethylcellulose phthalate), casein, dextrans, polysaccharides, fibrinogen, poly(ether ester) multiblock copolymers, based on poly(ethylene glycol) and poly(butylene terephthalate), tyrosine-derived polycarbonates (e.g., U.S. Pat. No.
  • non-degradable polymers suitable for the delivery of fibrosis-inducing agents include poly(ethylene-co-vinyl acetate) (“EVA”) copolymers, silicone rubber, acrylic polymers (e.g., polyacrylic acid, polymethylacrylic acid, polymethylmethacrylate, poly(butyl methacrylate)), poly(alkylcyanoacrylate) (e.g., poly(ethylcyanoacrylate), poly(butylcyanoacrylate), poly(hexylcyanoacrylate), and poly(octylcyanoacrylate)), polyethylene, polypropylene, polyamides (nylon 6,6), polyurethanes (including hydrophilic polyurethanes), poly(ester-urethanes), poly(ether-urethanes), poly(ester-urea), poly(carbonate urethane)s, polyethers (poly(ethylene oxide), poly(propylene oxide), polyoxyalkylene ether block copolymers based on ethylene
  • Polymers may also be developed which are either anionic (e.g., alginate, carrageenan, carboxymethyl cellulose, poly(acrylamido-2-methyl propane sulfonic acid) and copolymers thereof, poly(methacrylic acid) and copolymers thereof, and poly(acrylic acid) and copolymers thereof, as well as blends thereof) or cationic (e.g., chitosan, poly-L-lysine, polyethylenimine, and poly(allyl amine) and blends thereof (see generally, Dunn et al., J. Applied Polymer Sci. 50: 353-365, 1993; Cascone et al., J.
  • anionic e.g., alginate, carrageenan, carboxymethyl cellulose, poly(acrylamido-2-methyl propane sulfonic acid) and copolymers thereof, poly(methacrylic acid) and copolymers thereof, and poly(acrylic acid) and copolymers thereof,
  • Particularly preferred polymeric carriers include poly(ethylene-co-vinyl acetate), cellulose esters (nitrocellulose), poly(hydroxymethacrylate), poly(methylmethacrylate), poly(ethylene-co-acrylic acid), poly(vinylpyrrolidone) polyurethanes (e.g., CHRONOFLEX AL and CHRONOFLEX AR (both from CardioTech International, Inc., Woburn, Mass.) and BIONATE (Polymer Technology Group, Inc., Emeryville, Calif.), poly(D,L-lactic acid) oligomers and polymers, poly(L-lactic acid) oligomers and polymers, poly(glycolic acid), copolymers of lactic acid and glycolic acid, poly(caprolactone), poly(valerolactone), polyanhydrides, poly(anhydride esters), poly(ester-amides), poly(ester-ureas), copolymers of poly(caprolactone) or poly(lactic acid) with a polyethylene glycol (e.
  • polysaccharides such as hyaluronic acid, chitosan and fucans, and copolymers of polysaccharides with degradable polymers, as well as crosslinked compositions of the above.
  • fibrosis-inducing agents include carboxylic polymers, polyacetates, polyacrylamides, polycarbonates, polyethers, substituted polyethylenes, polyvinylbutyrals, polysilanes, polyureas, polyoxides, polystyrenes, polysulfides, polysulfones, polysulfonides, polyvinylhalides, pyrrolidones, isoprene rubbers, thermal-setting polymers, cross-linkable acrylic and methacrylic polymers, ethylene acrylic acid copolymers, styrene acrylic copolymers, vinyl acetate polymers and copolymers, vinyl acetal polymers and copolymers, epoxies, melamines, other amino resins, phenolic polymers, and copolymers thereof, water-insoluble cellulose ester polymers (including cellulose acetate propionate, cellulose acetate, nitrocellulose, cellulose a
  • polymers as described herein can also be blended or copolymerized in various compositions as required to deliver therapeutic doses of fibrosis-inducing agents to blood vessels in the treatment site.
  • Polymeric carriers for fibrosis-inducing agents can be fashioned in a variety of forms, with desired release characteristics and/or with specific properties depending upon the device, composition or implant being utilized.
  • polymeric carriers may be fashioned to release a fibrosis-inducing agent upon exposure to a specific triggering event such as pH (see, e.g., Heller et al., “Chemically Self-Regulated Drug Delivery Systems,” in Polymers in Medicine III, Elsevier Science Publishers B.V., Amsterdam, 1988, pp. 175-188; Kang et al., J. Applied Polymer Sci. 48: 343-354, 1993; Dong et al., J.
  • pH-sensitive polymers include poly(acrylic acid) and its derivatives (including for example, homopolymers such as poly(aminocarboxylic acid); poly(acrylic acid); poly(methyl acrylic acid), copolymers of such homopolymers, and copolymers of poly(acrylic acid) and acrylmonomers such as those discussed above.
  • pH sensitive polymers include polysaccharides such as cellulose acetate phthalate; hydroxypropylmethylcellulose phthalate; hydroxypropylmethylcellulose acetate succinate; cellulose acetate trimellilate; and chitosan.
  • pH sensitive polymers include any mixture of a pH sensitive polymer and a water-soluble polymer.
  • fibrosis-inducing agents can be delivered via polymeric carriers which are temperature sensitive (see, e.g., Chen et al., “Novel Hydrogels of a Temperature-Sensitive Pluronic Grafted to a Bioadhesive Polyacrylic Acid Backbone for Vaginal Drug Delivery,” in Proceed. Intern. Symp. Control. Rel. Bioact Mater. 22: 167-168, Controlled Release Society, Inc., 1995; Okano, “Molecular Design of Stimuli-Responsive Hydrogels for Temporal Controlled Drug Delivery,” in Proceed. Intern. Symp. Control. Rel. Bioact Mater.
  • thermogelling polymers and their gelatin temperature [LCST (° C.)] include homopolymers such as poly(N-methyl-N-n-propylacrylamide), 19.8; poly(N-n-propylacrylamide), 21.5; poly(N-methyl-N-isopropylacrylamide), 22.3; poly(N-n-propylmethacrylamide), 28.0; poly(N-isopropylacrylamide), 30.9; poly(N, n-diethylacrylamide), 32.0; poly(N-isopropylmethacrylamide), 44.0; poly(N-cyclopropylacrylamide), 45.5; poly(N-ethylmethyacrylamide), 50.0; poly(N-methyl-N-ethylacrylamide), 56.0; poly(N-cyclopropylmethacrylamide), 59.0; and poly(N-ethylacrylamide), 72.0.
  • homopolymers such as poly(N-methyl-N-n-propylacrylamide), 19.
  • thermogelling polymers may be made by preparing copolymers between (among) monomers of the above, or by combining such homopolymers with other water-soluble polymers such as acrylmonomers (e.g., acrylic acid and derivatives thereof, such as methylacrylic acid, acrylate and derivatives thereof, such as butyl methacrylate, acrylamide, and N-n-butyl acrylamide).
  • acrylmonomers e.g., acrylic acid and derivatives thereof, such as methylacrylic acid, acrylate and derivatives thereof, such as butyl methacrylate, acrylamide, and N-n-butyl acrylamide.
  • thermogelling polymers include cellulose ether derivatives such as hydroxypropyl cellulose, 41° C.; methyl cellulose, 55° C.; hydroxypropylmethyl cellulose, 66° C.; and ethylhydroxyethyl cellulose, polyalkylene oxide-polyester block copolymers of the structure X—Y, Y—X—Y and X—Y—X where X is a polyalkylene oxide and Y is a biodegradable polyester (e.g., PLG-PEG-PLG) and PLURONICS such as F-127, 10-15° C.; L-122, 19° C.; L-92, 26° C.; L-81, 20° C.; and L-61, 24° C.
  • PLG-PEG-PLG biodegradable polyester
  • PLURONICS such as F-127, 10-15° C.; L-122, 19° C.; L-92, 26° C.; L-81, 20° C.; and L-61,
  • Fibrosis-inducing agents may be linked by occlusion in the matrices of the polymer, bound by covalent linkages, or encapsulated in microcapsules.
  • therapeutic compositions are provided in non-capsular formulations such as microspheres (ranging from nanometers to micrometers in size), pastes, and threads of various size, films and sprays.
  • compositions may be fashioned in any size ranging from 50 nm to 500 ⁇ m, depending upon the particular use.
  • These compositions can be in the form of microspheres (porous or non-porous), microparticles, and/or nanoparticles.
  • These compositions can be formed, for example, by spray-drying methods, milling methods, coacervation methods, W/O (water-oil) emulsion methods, W/O/W emulsion methods, and solvent evaporation methods.
  • these compositions can include microemulsions, emulsions, liposomes and micelles.
  • compositions may also be readily applied as a “spray”, which solidifies into a film or coating for use as a device/implant surface coating or to line the tissues of the implantation site.
  • sprays may be prepared from microspheres of a wide array of sizes, including for example, from 0.1 ⁇ m to 3 ⁇ m, from 10 ⁇ m to 30 ⁇ m, and from 30 ⁇ m to 100 ⁇ m.
  • compositions of the present invention may also be prepared in a variety of paste or gel forms.
  • therapeutic compositions are provided which are liquid at one temperature (e.g., temperature greater than 37° C., such as 40° C., 45° C., 50° C., 55° C. or 60° C.), and solid or semi-solid at another temperature (e.g., ambient body temperature, or any temperature lower than 37° C.).
  • temperature greater than 37° C. such as 40° C., 45° C., 50° C., 55° C. or 60° C.
  • solid or semi-solid at another temperature e.g., ambient body temperature, or any temperature lower than 37° C.
  • Such “thermopastes” may be readily made utilizing a variety of techniques (see, e.g., PCT Publication WO 98/24427).
  • pastes may be applied as a liquid, which solidify in vivo due to dissolution of a water-soluble component of the paste and precipitation of encapsulated drug into the aqueous body environment.
  • These pastes and gels containing fibrosis-inducing agents are particularly useful for application to the surface of tissues which can be in contact with the implant or device.
  • the fibrosing agent or a composition comprising the fibrosing agent may be combined with a film or mesh or may be in the form or a film or mesh.
  • Films or meshes may take a variety of forms including, but not limited to, surgical meshes, membranes (e.g., barrier membranes), surgical sheets, surgical patches, surgical wraps, bandages, liquid bandages, surgical dressings, gauze, fabrics, tapes, surgical membranes, polymer matrices, shells, envelopes, tissue coverings, and other types of surgical matrices, and scaffolds.
  • membranes e.g., barrier membranes
  • surgical sheets e.g., surgical sheets, surgical patches, surgical wraps, bandages, liquid bandages, surgical dressings, gauze, fabrics, tapes, surgical membranes, polymer matrices, shells, envelopes, tissue coverings, and other types of surgical matrices, and scaffolds.
  • the device comprises or may be in the form of a film.
  • the film may be formed into one of many geometric shapes. Depending on the application, the film may be formed into the shape of a tube or may be a thin, elastic sheet of polymer. Generally, films are less than 5, 4, 3, 2, or 1 mm thick, more preferably less than 0.75 mm, 0.5 mm, 0.25 mm, or, 0.10 mm thick. Films can also be generated of thicknesses less than 50 ⁇ m, 25 ⁇ m or 10 ⁇ m.
  • Films generally are flexible with a good tensile strength (e.g., greater than 50, preferably greater than 100, and more preferably greater than 150 or 200 N/cm 2 ), good adhesive properties (i.e., adheres to moist or wet surfaces), and have controlled permeability.
  • Polymeric films (which may be porous or non-porous) are particularly useful for application to the surface of a device or implant as well as to the surface of tissue, cavity or an organ.
  • Films may be made by several processes, including for example, by casting, and by spraying, or may be formed at the treatment site in situ.
  • a sprayable formulation may be applied onto the treatment site which then forms into a solid film.
  • the device may comprise or be in the form of a mesh.
  • a mesh is a material composed of a plurality of fibers or filaments (i.e., a fibrous material), where the fibers or filaments are arranged in such a manner (e.g., interwoven, knotted, braided, overlapping, looped, knitted, interlaced, intertwined, webbed, felted, and the like) so as to form a porous structure.
  • a mesh is a pliable material, such that it has sufficient flexibility to be wrapped around a device.
  • the mesh may be sufficiently pliable so as to be capable of being wrapped around the external surface of a body passageway or cavity, or a portion thereof.
  • the mesh may be capable of providing support to the structure (e.g., the vessel or cavity wall).
  • the mesh may be adapted to release an amount of the therapeutic agent.
  • Mesh materials may take a variety of forms.
  • the mesh may be in a woven, knit, or non-woven form and may include fibers or filaments that are randomly oriented relative to each other or that are arranged in an ordered array or pattern.
  • a mesh may be in the form of a fabric, such as, for example, a knitted, braided, crocheted, woven, non-woven (e.g., a melt-blown or wet-laid) or webbed fabric.
  • a mesh may include a natural or synthetic biodegradable polymer that may be formed into a knit mesh, a weave mesh, a sprayed mesh, a web mesh, a braided mesh, a looped mesh, and the like.
  • a mesh or wrap has intertwined threads that form a porous structure, which may be, for example, knitted, woven, or webbed.
  • the structure and properties of the mesh used in a device depend on the application and the desired mechanical (i.e., flexibility, tensile strength, and elasticity), degradation properties, and the desired loading and release characteristics for the selected therapeutic agent(s).
  • the mesh should have mechanical properties, such that the device can remain sufficiently strong until the surrounding tissue has healed.
  • Factors that affect the flexibility and mechanical strength of the mesh include, for example, the porosity, fabric thickness, fiber diameter, polymer composition (e.g., type of monomers and initiators), process conditions, and the additives that are used to prepare the material.
  • the mesh possesses sufficient porosity to permit the flow of fluids through the pores of the fiber network and to facilitate tissue ingrowth.
  • the interstices of the mesh should be wide enough apart to allow light visible by eye, or fluids, to pass through the pores.
  • materials having a more compact structure also may be used.
  • the flow of fluid through the interstices of the mesh may depend on a variety of factors, including, for example, the stitch count or thread density.
  • the porosity of the mesh may be further tailored by, for example, filling the interstices of the mesh with another material (e.g., particles or polymer) or by processing the mesh (e.g., by heating) in order to reduce the pore size and to create non-fibrous areas.
  • Fluid flow through the mesh of the invention can vary depending on the properties of the fluid, such as viscosity, hydrophilicity/hydrophobicity, ionic concentration, temperature, elasticity, pseudoplasticity, particulate content, and the like.
  • the interstices of the mesh can be large enough so as to not prevent the release of impregnated or coated therapeutic agent(s) from the mesh, and the interstices preferably do not prevent the exchange of tissue fluid at the application site.
  • Mesh materials should be sufficiently flexible so as to be capable of conforming to the shape of a device surface or an anatomotical surface. In certain cases, the mesh material may be sufficiently flexible so as to be capable of being wrapped around all or a portion of the external surface of a body passageway or cavity.
  • Flexible mesh materials are typically in the form of flexible woven or knitted sheets having a thickness ranging from about 25 microns to about 3000 microns; preferably from about 50 to about 1000 microns.
  • Mesh materials for use in the practice of the invention typically range from about 100 to 400 microns in thickness.
  • the diameter and length of the fibers or filaments may range in size depending on the form of the material (e.g., knit, woven, or non-woven), and the desired elasticity, porosity, surface area, flexibility, and tensile strength.
  • the fibers may be of any length, ranging from short filaments to long threads (i.e., several microns to hundreds of meters in length). Depending on the application, the fibers may have a monofilament or a multifilament construction.
  • the mesh may include fibers that are of same dimension or of different dimensions, and the fibers may be formed from the same or different types of biodegradable polymers.
  • Woven materials may include a regular or irregular array of warp and weft strands and may include one type of polymer in the weft direction and another type (having the same or a different degradation profile from the first polymer) in the warp direction. The degradation profile of the weft polymer may be different than or the same as the degradation profile of the warp polymer.
  • knit materials may include one or more types (e.g., monofilament, multi-filament) and sizes of fibers and may include fibers made from the same or from different types of biodegradable polymers.
  • the structure of the mesh may impact the amount of therapeutic agent that may be loaded into or onto the device.
  • a fabric having a loose weave characterized by a low fiber density and high porosity can have a lower thread count, resulting in a reduced total fiber volume and surface area.
  • therapeutic agent ratio the amount of agent that may be loaded into or onto, with a fixed carrier: therapeutic agent ratio, the fibers can be lower than for a fabric having a high fiber density and lower porosity.
  • the mesh also should not invoke biologically detrimental inflammatory or toxic response, should be capable of being fully metabolized in the body, have an acceptable shelf life (of about at least one year or more), and be easily sterilized.
  • the device may include multiple mesh materials in any combination or arrangement.
  • a portion of the device may be a knitted material and another portion may be a woven material.
  • the device may more than one layer (e.g., a layer of woven material fused to a layer of knitted material or to another layer of the same type or a different type of woven material).
  • multi-layer constructions e.g., device having two or more layers of material
  • the mesh or film may be formed of or include a polymer.
  • the polymer may be a biodegradable or a non-biodegradable polymer, or a combination thereof.
  • Biodegradable compositions that may be used to prepare the mesh of film include polymers that comprise albumin, collagen, hyaluronic acid and derivatives, sodium alginate and derivatives, chitosan and derivatives gelatin, starch, cellulose polymers (for example methylcellulose, hydroxypropylcellulose, hydroxypropylmethylcellulose, carboxymethylcellulose, cellulose acetate phthalate, cellulose acetate succinate, hydroxypropylmethylcellulose phthalate), casein, dextran and derivatives, polysaccharides, poly(caprolactone), fibrinogen, poly(hydroxyl acids), poly(L-lactide) poly(D, L lactide), poly(D, L-lactide-co-glycolide), poly(L-lactide-co-glycolide), copolymers of lactic acid and glycolic acid, copolymers of ⁇ -caprolactone and lactide, copolymers of glycolide and ⁇ -caprolactone, copolymers of lact
  • compositions include copolymers of the above polymers as well as blends and combinations of the above polymers.
  • the mesh or film includes a biodegradable or resorbable polymer that is formed from one or more monomers selected from the group consisting of lactide, glycolide, e-caprolactone, trimethylene carbonate, 1,4-dioxan-2-one, 1,5-dioxepan-2-one, 1,4-dioxepan-2-one, hydroxyvalerate, and hydroxybutyrate.
  • the polymer may include, for example, a copolymer of a lactide and a glycolide.
  • the polymer includes a poly(caprolactone).
  • the polymer includes a poly(lactic acid), poly(L-lactide)/poly(D,L-Lactide) blends or copolymers of L-lactide and D,L-lactide.
  • the polymer includes a copolymer of lactide and e-caprolactone.
  • the polymer includes a polyester (e.g., a poly(lactide-co-glycolide).
  • the poly(lactide-co-glycolide) may have a lactide:glycolide ratio ranges from about 20:80 to about 2:98, a lactide:glycolide ratio of about 10:90, or a lactide:glycolide ratio of about 5:95.
  • the poly(lactide-co-glycolide) is poly(L-lactide-co-glycolide).
  • biodegradable materials include polyglactin, polyglycolic acid, autogenous, heterogenous, and xenogeneic tissue (e.g., pericardium or small intestine submucosa), and oxidized, regenerated cellulose. These meshes can be knitted, woven or non-woven meshes. Other examples of non-woven meshes include electrospun materials.
  • non-biodegradable compositions for use in forming films and meshes include ethylene-co-vinyl acetate copolymers, acrylic-based and methacrylic-based polymers (e.g., poly(acrylic acid), poly(methylacrylic acid), poly(methylmethacrylate), poly(hydroxyethylmethacrylate), poly(alkylcynoacrylate), poly(alkyl acrylates), poly(alkyl methacrylates)), polyolefins such as poly(ethylene) or poly(propylene), polyamides (e.g., nylon 6,6), poly(urethanes) (e.g.
  • acrylic-based and methacrylic-based polymers e.g., poly(acrylic acid), poly(methylacrylic acid), poly(methylmethacrylate), poly(hydroxyethylmethacrylate), poly(alkylcynoacrylate), poly(alkyl acrylates), poly(alkyl methacrylates)
  • polyolefins
  • fluorine containing polymers fluorinated
  • the film or mesh may be a biodegradable polymeric matrix that conforms to the tissue and releases the agent in a controlled release manner. See e.g., U.S. Pat. No. 6,461,640.
  • the film or mesh may be a self-adhering silicone sheet which is impregnated with an antioxidant and/or antimicrobial. See e.g., U.S. Pat. No. 6,572,878.
  • the film or mesh may be a pliable shield with attachment ports and fenestrations that is adapted to cover a bony dissection in the spine. See e.g., U.S. Pat. No. 5,868,745 and U.S.
  • the film or mesh may be a resorbable micro-membrane having a single layer of non-porous polymer base material of poly-lactide. See e.g., U.S. Pat. No. 6,531,146 and U.S. Application No. 2004/0137033.
  • the film or mesh may be a wound dressing garment composed of an outer pliable layer and a self-adhesive inner gel lining which serves as a dressing for contacting wounds. See e.g., U.S. Pat. No. 6,548,728.
  • the film or mesh may be a bandage with a scar treatment pad with a layer of silicone elastomer or silicone gel. See e.g., U.S.
  • the film or mesh may be a crosslinkable system with at least three reactive compounds each having a polymeric molecular core with at least one functional group. See e.g., U.S. Pat. No. 6,458,889.
  • the film or mesh may be composed of a prosthetic fabric having a 3-dimensional structure separating two surfaces in which one is open to post-surgical cell colonization and one is linked to a film of collagenous material. See e.g., U.S. Pat. No. 6,451,032.
  • the film or mesh may be composed by crosslinking two synthetic polymers, one having nucleophilic groups and the other having electrophilic groups, such that they form a matrix that may be used to incorporate a biologically active compound.
  • the film or mesh may be a conformable warp-knit fabric of oxidized regenerated cellulose or other bioresorbable material which acts like a physical barrier to prevent postoperative adhesions. See e.g., U.S. Pat. No. 5,007,916.
  • Meshes for use in the practice of the invention also are described in U.S. Pat. No. 6,575,887, and co-pending application, entitled “Perivascular Wraps,” filed Sep. 26, 2003 (U.S. Ser. No. (U.S. Ser. No. 10/673,046), which is hereby incorporated by reference in its entirety.
  • the fibrosing agent can be incorporated into a biodegradable or dissolvable film or mesh that is then applied to the treatment site prior or post implantation of the prosthesis/implant.
  • exemplary materials for the manufacture of these films or meshes are hyaluronic acid (crosslinked or non-crosslinked), cellulose derivatives (e.g., hydroxypropyl cellulose), PLGA, collagen and crosslinked poly(ethylene glycol).
  • Films and meshes which may be combined with one or more scarring agents according to the present invention, include commercially available products.
  • films and meshes into which a fibrosis-inducing agent can be incorporated include INTERCEED (Johnson & Johnson, Inc.), PRECLUDE (W.L. Gore), and POLYACTIVE (poly(ether ester) multiblock copolymers (Osteotech, Inc., Shrewsbury, N.J.), based on poly(ethylene glycol) and poly(butylene terephthalate), and SURGICAL absorbable hemostat gauze-like sheet from Johnson & Johnson.
  • Another mesh is a prosthetic polypropylene mesh with a bioresorbable coating called SEPRAMESH Biosurgical Composite (Genzyme Corporation, Cambridge, Mass.).
  • SEPRAMESH Biosurgical Composite Gene Corporation, Cambridge, Mass.
  • One side of the mesh is coated with a bioresorbable layer of sodium hyaluronate and carboxymethylcellulose, providing a temporary physical barrier that separates the underlying tissue and organ surfaces from the mesh.
  • the other side of the mesh is uncoated, allowing for complete tissue ingrowth similar to bare polypropylene mesh.
  • the fibrosis-inducing agent may be applied only to the uncoated side of SEPRAMESH and not to the sodium hyaluronate/carboxymethylcellulose coated side.
  • Other films and meshes include: (a) BARD MARLEX mesh (C.R.
  • SURGISIS GOLD and SURGISIS IHM soft tissue graft both from Cook Surgical, Inc. which are devices specifically configured for use to reinforce soft tissue in repair of inguinal hernias in open and laparoscopic procedures;
  • thin walled polypropylene surgical meshes such as are available from Atrium Medical Corporation (Hudson, N.H.) under the trade names PROLITE, PROLITE ULTRA, and LITEMESH;
  • COMPOSIX hernia mesh C.R.
  • VISILEX mesh from C.R. Bard, Inc.
  • C.R. Bard, Inc. which is a polypropylene mesh that is constructed with monofilament polypropylene
  • PERFIX Plug KUGEL Hernia Patch
  • 3D MAX mesh 3D MAX mesh
  • LHI mesh LHI mesh
  • DULEX mesh DULEX mesh
  • VENTRALEX Hernia Patch other types of polypropylene monofilament hernia mesh and plug products include HERTRA mesh 1, 2, and 2A, HERMESH 3, 4 & 5 and HERNIAMESH plugs T1, T2, and T3 from Herniamesh USA, Inc. (Great Neck, N.Y.).
  • Membrana Accurel Systems (Germany) sells the CELGARD microporous polypropylene fiber and membrane. Gynecare Worldwide, a division of Ethicon, Inc. sells a mesh material made from oxidized, regenerated cellulose known as INTERCEED TC7.
  • Methods for incorporating the fibrosing compositions onto or into the film or mesh include: (a) affixing (directly or indirectly) to the film or mesh a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier), (b) incorporating or impregnating into the film or mesh a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier (c) by coating the film or mesh with a substance such as a hydrogel which can in turn absorb the fibrosing composition, (d) constructing the film or mesh itself or a portion of the film or mesh with a fibrosing composition, or (e) by covalently binding the fibrosing agent directly to the film or mesh surface or to a linker (small molecule or polymer) that is coated or attached to the film or mesh surface.
  • a linker small molecule or polymer
  • the therapeutic agent(s) may be an integral part of the film or mesh (i.e., may reside within the fibers of the mesh).
  • the fibrosis inhibiting agent can be incorporated directly into the film or mesh or it can be incorporated into a secondary carrier (polymeric or non-polymeric), as described above, that is then incorporated into the film or mesh.
  • the film or mesh may be coated with a fibrosing agent or a composition that includes the fibrosing agent.
  • the coating may take the form of a surface-adherent coating, mask, film, gel, foam, or mold.
  • compositions may be in the form of, for example, gels, sprays, liquids, and pastes, or may be polymerized from monomeric or prepolymeric constituents in situ.
  • the composition may be a polymeric tissue coating which is formed by applying a polymerization initiator to the tissue and then covering it with a water-soluble macromer that is polymerizable using free radical initiators under the influence of UV light. See e.g., U.S. Pat. Nos. 6,177,095 and 6,083,524.
  • the composition may be an aqueous composition including a surfactant, pentoxifylline and a polyoxyalkylene polyether.
  • the composition may be a hydrogel-forming, self-solvating, absorbable polyester copolymers capable of selective, segmental association into compliant hydrogels mass upon contact with an aqueous environment. See e.g., U.S. Pat. No. 5,612,052.
  • the composition may be composed of fluent pre-polymeric material that is emitted to the tissue surface and then exposed to activating energy in situ to initiate conversion of the applied material to non-fluent polymeric form. See e.g., U.S. Pat. Nos. 6,004,547 and 5,612,050.
  • the composition may be composed of a gas mixture of oxygen present in a volume ratio of 1 to 20%.
  • the composition may be composed of an anionic polymer having an acid sulfate and sulfur content greater than 5% which acts to inhibit monocyte or macrophage invasion. See e.g., U.S. Pat. No. 6,417,173.
  • the composition may be composed of a non-gelling polyoxyalkylene composition with or without a therapeutic agent. See e.g., U.S. Pat. No. 6,436,425.
  • composition may be coated onto tissue surfaces and may be composed of an aqueous solution of a hydrophilic, polymeric material (e.g., polypeptides or polysaccharide) having greater than 50,000 molecular weight and a concentration range of 0.01% to 15% by weight. See e.g., U.S. Pat. No. 6,464,970.
  • a hydrophilic, polymeric material e.g., polypeptides or polysaccharide
  • compositions that can be combined with scarring agents in conjunction with films and meshes include, but are not limited to: (a) sprayable PEG-containing formulations such as COSEAL, SPRAYGEL, FOCALSEAL or DURASEAL; (b) hyaluronic acid-containing formulations such as RESTYLANE, HYLAFORM, PERLANE, SYNVISC, SEPRAFILM, SEPRACOAT, INTERGEL, (c) polymeric gels such as REPEL or FLOWGEL, (d) dextran sulfate gels such as the ADCON range of products, and (e) lipid based compositions such as ADSURF (Brittania Pharmaceuticals).
  • sprayable PEG-containing formulations such as COSEAL, SPRAYGEL, FOCALSEAL or DURASEAL
  • hyaluronic acid-containing formulations such as RESTYLANE, HYLAFORM, PERLANE, SYNVISC, SEPRAFILM, SEPRACO
  • the film or mesh Prior to implantation, the film or mesh may be trimmed or cut from a sheet of bulk material to match the configuration of the widened foramen, canal, or dissection region, or at a minimum, to overlay the exposed tissue area.
  • the film or mesh may be bent or shaped to match the particular configuration of the placement region.
  • the film or mesh may also be rolled in a cuff shape or cylindrical shape and placed around the exterior periphery of the desired tissue.
  • the film or mesh may be provided in a relatively large bulk sheet and then cut into shapes to mold the particular structure and surface topography of the tissue or device to be wrapped. Alternatively, the film or mesh may be pre-shaped into one or more patterns for subsequent use.
  • the films and meshes may be typically rectangular in shape and be placed at the desired location within the surgical site by direct surgical placement or by endoscopic techniques.
  • the film or mesh may be secured into place by wrapping it onto itself (i.e., self-adhesive), or by securing it with sutures, staples, sealant, and the like.
  • the film or mesh may adhere readily to tissue and therefore, additional securing mechanisms may not be required.
  • polymeric carriers are provided which are adapted to contain and release a hydrophobic fibrosis-inducing compound, and/or the carrier containing the hydrophobic compound, in combination with a carbohydrate, protein or polypeptide.
  • the polymeric carrier contains or comprises regions, pockets, or granules of one or more hydrophobic compounds.
  • hydrophobic compounds may be incorporated within a matrix which contains the hydrophobic fibrosis-inducing compound, followed by incorporation of the matrix within the polymeric carrier.
  • matrices can be utilized in this regard, including for example, carbohydrates and polysaccharides such as starch, cellulose, dextran, methylcellulose, sodium alginate, heparin, chitosan and hyaluronic acid and proteins or polypeptides such as albumin, collagen and gelatin.
  • hydrophobic compounds may be contained within a hydrophobic core, and this core contained within a hydrophilic shell.
  • polymeric carriers can be materials that are formed in situ.
  • the precursors can be monomers or macromers that contain unsaturated groups which can be polymerized or crosslinked.
  • the monomers or macromers can then, for example, be injected into the treatment area or onto the surface of the treatment area and polymerized or crosslinked in situ using a radiation source (e.g., visible or UV light) or a free radical system (e.g., potassium persulfate and ascorbic acid or iron and hydrogen peroxide).
  • a radiation source e.g., visible or UV light
  • a free radical system e.g., potassium persulfate and ascorbic acid or iron and hydrogen peroxide.
  • the polymerization or crosslinking step can be performed immediately prior to, simultaneously to, or post injection of the reagents into the treatment site.
  • compositions that undergo free radical polymerization or crosslinking reactions are described in WO 01/44307, WO 01/68720, WO 02/072166, WO 03/043552, WO 93/17669, and WO 00/64977, U.S. Pat. Nos. 5,900,245; 6,051,248; 6,083,524; 6,177,095; 6,201,065; 6,217,894; 6,639,014; 6,352,710; 6,410,645; 6,531,147; 5,567,435; 5,986,043; and 6,602,975, and U.S. Patent Application Publication Nos. 2002/012796, 2002/0127266, 2002/0151650, 2003/0104032, 2002/0091229, and 2003/0059906.
  • the reagents can undergo an electrophilic-nucleophilic reaction to produce a crosslinked matrix.
  • Polymers terminated with nucleophilic groups such as amine, sulfhydryl, hydroxyl, —PH 2 or CO—NH—NH 2 can be used as the nucleophilic reagents and polymers terminated with electrophilic groups such as succinimidyl, carboxylic acid, aldehyde, epoxide, isocyanate, vinyl, vinyl sulfone, maleimide, —S—S—(C 5 H 4 N) or activated esters, such as are used in peptide synthesis can be used as the electrophilic reagents.
  • a 4-armed thiol derivatized poly(ethylene glycol) e.g., pentaerythritol poly(ethylene glycol)ether tetra-sulfhydryl
  • a 4 armed NHS-derivatized polyethylene glycol e.g., pentaerythritol poly(ethylene glycol)ether tetra-succinimidyl glutarate
  • basic conditions pH>about 8
  • the electrophilic- or nucleophilic-terminated polymers can further comprise a polymer that can enhance the mechanical and/or adhesive properties of the in situ forming compositions.
  • This polymer can be a degradable or non-degradable polymer.
  • the polymer may be collagen or a collagen derivative, for example methylated collagen.
  • An example of an in situ forming composition uses pentaerythritol poly(ethylene glycol)ether tetra-sulfhydryl] (4-armed thiol PEG), pentaerythritol poly(ethylene glycol)ether tetra-succinimidyl glutarate] (4-armed NHS PEG) and methylated collagen as the reactive reagents.
  • composition when mixed with the appropriate buffers can produce a crosslinked hydrogel.
  • This composition when mixed with the appropriate buffers can produce a crosslinked hydrogel.
  • the in situ forming material polymer can be a polyester.
  • Polyesters that can be used in in situ forming compositions include poly(hydroxyesters).
  • the polyester can comprise the residues of one or more of the monomers selected from lactide, lactic acid, glycolide, glycolic acid, e-caprolactone, gamma-caprolactone, hydroxyvaleric acid, hydroxybutyric acid, beta-butyrolactone, gamma-butyrolactone, gamma-valerolactone, ?-decanolactone, d-decanolactone, trimethylene carbonate, 1,4-dioxane-2-one or 1,5-dioxepan-2-one.
  • Representative examples of these types of compositions are described in U.S. Pat. Nos. 5,874,500; 5,936,035; 6,312,725; 6,495,127 and PCT Publication Nos. WO 2004/028547.
  • the electrophilic-terminated polymer can be partially or completely replaced by a small molecule or oligomer that comprises an electrophilic group (e.g., disuccinimidyl glutarate).
  • a small molecule or oligomer that comprises an electrophilic group (e.g., disuccinimidyl glutarate).
  • the nucleophilic-terminated polymer can be partially or completely replaced by a small molecule or oligomer that comprises a nucleophilic group (e.g., dicysteine, dilysine, trilysine, etc.).
  • a nucleophilic group e.g., dicysteine, dilysine, trilysine, etc.
  • in situ forming materials include those based on the crosslinking of proteins (described in, for example, U.S. Pat. Nos. RE38158; 4,839,345; 5,514,379, 5,583,114; 6,310,036; 6,458,147; 6,371,975; U.S. Patent Application Publication Nos. 2004/0063613A1, 2002/0161399A1, and 2001/0018598A1, and PCT Publication Nos. WO 03/090683, WO 01/45761, WO 99/66964, and WO 96/03159) and those based on isocyanate or isothiocyanate capped polymers (see, e.g., PCT Publication No. WO 04/021983).
  • in situ forming materials can include reagents that comprise one or more cyanoacrylate groups. These reagents can be used to prepare a poly(alkylcyanoacrylate) or poly(carboxyalkylcyanoacrylate) (e.g., poly(ethylcyanoacrylate), poly(butylcyanoacrylate), poly(isobutylcyanoacrylate), poly(hexylcyanoacrylate), poly(methoxypropylcyanoacrylate), and poly(octylcyanoacrylate)).
  • a poly(alkylcyanoacrylate) or poly(carboxyalkylcyanoacrylate) e.g., poly(ethylcyanoacrylate), poly(butylcyanoacrylate), poly(isobutylcyanoacrylate), poly(hexylcyanoacrylate), poly(methoxypropylcyanoacrylate), and poly(octylcyanoacrylate)
  • cyanoacrylates examples include DERMABOND, INDERMIL, GLUSTITCH, VETBOND, HISTOACRYL, TISSUEMEND, TISSUMEND II, HISTOACRYL BLUE and ORABASE SOOTHE-N-SEAL LIQUID PROTECTANT.
  • the cyanoacrylate compositions can further comprise additives to stabilize the reagents or alter the rate of reaction of the cyanoacrylate.
  • additives for example, a trimethylene carbonate based polymer or an oxalate polymer of poly(ethylene glycol) or a ⁇ -caprolactone based copolymer can be mixed with a 2-alkoxyalkylcyanoacrylate (e.g., 2-methoxypropylcyanoacrylate).
  • a trimethylene carbonate based polymer or an oxalate polymer of poly(ethylene glycol) or a ⁇ -caprolactone based copolymer can be mixed with a 2-alkoxyalkylcyanoacrylate (e.g., 2-methoxypropylcyanoacrylate).
  • 2-alkoxyalkylcyanoacrylate e.g., 2-methoxypropylcyanoacrylate
  • the cyanoacrylate composition can be prepared by capping heterochain polymers with a cyanoacrylate group.
  • the cyanoacrylate-capped heterochain polymer preferably has at least two cyanoacrylate ester groups per chain.
  • the heterochain polymer can comprise an absorbable poly(ester), poly(ester-carbonate), poly(ether-carbonate) and poly(ether-ester).
  • the poly(ether-ester)s described in U.S. Pat. Nos. 5,653,992 and 5,714,159 can also be used as the heterochain polymers.
  • a triaxial poly( ⁇ -caprolactone-co-trimethylene carbonate) is an example of a poly(ester-carbonate) that can be used.
  • the heterochain polymer may be a polyether.
  • polyethers examples include poly(ethylene glycol), poly(propylene glycol) and block copolymers of poly(ethylene glycol) and poly(propylene glycol) (e.g., PLURONICS group of polymers including but not limited to PLURONIC F127 or F68). Representative examples of these compositions are described in U.S. Pat. No. 6,699,940.
  • the fibrosing agent can be coated onto the entire device or a portion of the device using the polymeric coatings described above. This can be accomplished, for example, by dipping, spraying, electrospinning, painting or by vacuum deposition.
  • coating compositions and methods described above there are various other coating compositions and methods that are known in the art. Representative examples of these coating compositions and methods are described in U.S. Pat. Nos.
  • the biologically active agent can be delivered with a non-polymeric agent.
  • non-polymeric agents include sucrose derivatives (e.g., sucrose acetate isobutyrate, sucrose oleate), sterols such as cholesterol, stigmasterol, beta-sitosterol, and estradiol; cholesteryl esters such as cholesteryl stearate; C 12 -C 24 fatty acids such as lauric acid, myristic acid, palmitic acid, stearic acid, arachidic acid, behenic acid, and lignoceric acid; C 18 -C 36 mono-, di- and triacylglycerides such as glyceryl monooleate, glyceryl monolinoleate, glyceryl monolaurate, glyceryl monodocosanoate, glyceryl monomyristate, glyceryl monodicenoate, glyceryl dipalmitate, gly
  • fibrosis-inducing agents include: hydroxypropyl cyclodextrin (Cserhati and Hollo, Int. J. Pharm. 108: 69-75, 1994), liposomes (see, e.g., Sharma et al., Cancer Res. 53: 5877-5881, 1993; Sharma and Straubinger, Pharm. Res. 11(60): 889-896, 1994; WO 93/18751; U.S. Pat. No. 5,242,073), liposome/gel (WO 94/26254), nanocapsules (Bartoli et al., J.
  • liquid emulsions foam, spray, gel, lotion, cream, ointment, dispersed vesicles, particles or droplets solid- or liquid-aerosols
  • microemulsions U.S. Pat. No. 5,330,756
  • polymeric shell nano- and micro-capsule
  • emulsions Tipent al., Pharm Res. 4: 62-165, 1987
  • nanospheres Hagan et al., Proc. Intern. Symp. Control Rel. Bioact. Mater. 22, 1995; Kwon et al., Pharm Res.
  • the fibrosis inducing agent can be incorporated into a composition that enhances osteointegration and/or osteogenesis.
  • these compositions include materials composed of beta-tricalcium phosphate (e.g., VITOSS, PROOSTEON 500R), hydroxyapatite or Ca 10 (PO 4 ) 6 OH (e.g., OSTEOGRAF, calcium carbonate or CaCO 3 , calcium sulfate (e.g., OSTEOSET and ALLOMATRIX), calcium phosphate (e.g., CALCIBON or NORIAN SRS) as well as synthetic bone fillers (e.g., CORTOSS) and processed bone fillers (e.g., BIOOSS). Representative examples of these materials are described in U.S.
  • the fibrosis-inducing agent can further comprise a secondary carrier.
  • the secondary carrier can be in the form of microspheres (e.g., PLGA, PLLA, PDLLA, PCL, gelatin, polydioxanone, poly(alkylcyanoacrylate)), nanospheres (e.g., PLGA, PLLA, PDLLA, PCL, gelatin, polydioxanone, poly(alkylcyanoacrylate)), liposomes, emulsions, microemulsions, micelles (e.g., SDS, block copolymers of the form X—Y, X—Y—X or Y—X—Y, where X is a poly(alkylene oxide) or an alkyl ether thereof and Y is a polyester (e.g., PLGA, PLLA, PDLLA, PCL, polydioxanone)), zeolites or cyclodextrins.
  • microspheres
  • these fibrosis-inducing agent/secondary carrier compositions can be a) incorporated directly into or onto the device, b) incorporated into a solution, c) incorporated into a gel or viscous solution, d) incorporated into the composition used for coating the device, or e) incorporated into or onto the device following coating of the device with a coating composition.
  • fibrosis-inducing agent loaded PLGA microspheres may be incorporated into a polyurethane coating solution which is then coated onto the device.
  • the device can be coated with a polyurethane and then allowed to partially dry such that the surface is still tacky.
  • a particulate form of the fibrosis-inducing agent or fibrosis-inducing agent/secondary carrier can then be applied to all or a portion of the tacky coating after which the device is dried.
  • the device can be coated with one of the coatings described above.
  • a thermal treatment process can then be used to soften the coating, after which the fibrosis-inducing agent or the fibrosis-inducing agent/secondary carrier is applied to the entire device or to a portion of the device (e.g., outer surface).
  • a coated device which inhibits or reduces an in vivo fibrotic reaction is further coated with a compound or composition which delays the release of and/or activity of the fibrosis-inducing agent.
  • agents include biologically inert materials such as gelatin, PLGA/MePEG film, PLA, polyurethanes, silicone rubbers, surfactants, lipids, or polyethylene glycol, as well as biologically active materials such as heparin (e.g., to induce coagulation).
  • the active agent on the device is top-coated with a physical barrier.
  • barriers can include non-degradable materials or biodegradable materials such as gelatin, PLGA/MePEG film, PLA, polyethylene glycol, or the like.
  • the rate of diffusion of the therapeutic agent in the barrier coat is slower that the rate of diffusion of the therapeutic agent in the coating layer.
  • the MePEG can dissolve out of the PLGA, leaving channels through the PLGA to an underlying layer containing the fibrosis-inducing agent (e.g., silk or cyclosporine A), which can then diffuse into the vessel wall and initiate its biological activity.
  • the fibrosis-inducing agent e.g., silk or cyclosporine A
  • a particulate form of the active agent may be coated onto the device using a polymer (e.g., PLG, PLA, or polyurethane).
  • a polymer e.g., PLG, PLA, or polyurethane.
  • a second polymer that dissolves slowly or degrades (e.g., MePEG-PLGA or PLG) and that does not contain the active agent, may be coated over the first layer. Once the top layer dissolves or degrades, it exposes the under coating, which allows the active agent to be exposed to the treatment site or to be released from the coating.
  • the outer layer of the coated device which induces an in vivo fibrotic response, is further treated to crosslink the outer layer of the coating.
  • This can be accomplished by subjecting the coated device to a plasma treatment process.
  • the degree of crosslinking and nature of the surface modification can be altered by changing the RF power setting, the location with respect to the plasma, the duration of treatment as well as the gas composition introduced into the plasma chamber.
  • Protection of a biologically active surface can also be utilized by coating the device or implant surface with an inert molecule that prevents access to the active site through steric hindrance, or by coating the surface with an inactive form of the fibrosis-inducing agent, which is later activated.
  • the device can be coated with an enzyme, which causes either release of the fibrosis-inducing agent or activates the fibrosis-inducing agent.
  • a suitable device surface coating includes an anti-coagulant such as heparin, which can be coated on top of the fibrosis-inducing agent such that the presence of the heparin or other anti-coagulant delays coagulation at the treatment site. As the heparin or other anticoagulant dissolves away, the anticoagulant activity may slow or stop, and the newly exposed fibrosis-inducing agent (e.g., silk or cyclosporine A) is capable of inhibiting or reducing fibrosis from occurring in the adjacent tissue.
  • an anti-coagulant such as heparin
  • the anticoagulant activity may slow or stop, and the newly exposed fibrosis-inducing agent (e.g., silk or cyclosporine A) is capable of inhibiting or reducing fibrosis from occurring in the adjacent tissue.
  • the device can be coated with an inactive form of the fibrosis-inducing agent, which is then activated once the device is deployed.
  • activation may be achieved by injecting another material into the treatment area after the device (as described below) is deployed or after the fibrosis-inducing agent has been administered to the treatment area (via, e.g., injections, spray, wash, drug delivery catheters or balloons).
  • the device may be coated with an inactive form of the fibrosis-inducing agent. Once the device is deployed, the activating substance is injected or applied into or onto the treatment site where the inactive form of the fibrosis-inducing agent has been applied.
  • a device may be coated with a biologically active fibrosis-inducing agent, in the usual manner.
  • the coating containing the active fibrosis-inducing agent may then be covered (e.g., coated) with polyethylene glycol.
  • the PEG and the fibrosing agent containing coating may be bonded through the formulation of a bond between reactive groups on the two layers.
  • an ester bond may be formed using a condensation reaction.
  • an esterase is injected into the treatment site around the outside of the implanted device. The esterase can cleave the bond between the ester and the fibrosis-inducing agent, thereby allowing the agent to initiate fibrosis.
  • a medical device may include a plurality of reservoirs within its structure, each reservoir configured to house and protect a therapeutic drug.
  • the reservoirs may be formed from divets in the device surface or micropores or channels in the device body.
  • the reservoirs are formed from voids in the structure of the device.
  • the reservoirs may house a single type of drug or more than one type of drug.
  • the druG(s) may be formulated with a carrier (e.g., a polymeric or non-polymeric material) that is loaded into the reservoirs.
  • the filled reservoir can function as a drug delivery depot which can release drug over a period of time dependent on the release kinetics of the drug from the carrier.
  • the reservoir may be loaded with a plurality of layers.
  • Each layer may include a different drug having a particular amount (dose) of drug, and each layer may have a different composition to further tailor the amount of drug that is released from the substrate.
  • the multi-layered carrier may further include a barrier layer that prevents release of the druG(s). The barrier layer can be used, for example, to control the direction that the drug elutes from the void.
  • the therapeutic compositions may also comprise additional ingredients such as surfactants (e.g., PLURONICS, such as F-127, L-122, L-101, L-92, L-81, and L-61), anti-inflammatory agents, anti-thrombotic agents, anti-infective agents, preservatives, anti-oxidants and/or anti-platelet agents.
  • surfactants e.g., PLURONICS, such as F-127, L-122, L-101, L-92, L-81, and L-61
  • anti-inflammatory agents e.g., F-127, L-122, L-101, L-92, L-81, and L-61
  • anti-inflammatory agents e.g., F-127, L-122, L-101, L-92, L-81, and L-61
  • anti-inflammatory agents e.g., F-127, L-122, L-101, L-92, L-81, and L-61
  • anti-inflammatory agents e.g., F-127
  • the therapeutic agent or carrier can also comprise radio-opaque, echogenic materials and magnetic resonance imaging (MRI) responsive materials (i.e., MRI contrast agents) to aid in visualization of the device under ultrasound, fluoroscopy and/or MRI.
  • MRI magnetic resonance imaging
  • a device may be made with or coated with a composition which is echogenic or radiopaque (e.g., made with echogenic or radiopaque with materials such as powdered tantalum, tungsten, barium carbonate, bismuth oxide, barium sulfate, metrazimide, iopamidol, iohexol, iopromide, iobitridol, iomeprol, iopentol, ioversol, ioxilan, iodixanol, iotrolan, acetrizoic acid derivatives, diatrizoic acid derivatives, iothalamic acid derivatives, ioxithalamic acid derivatives, metrizoic acid derivatives, iodamide, lypophylic agents, iodipamide and ioglycamic Acid or, by the addition of microspheres or bubbles which present an acoustic interface).
  • echogenic or radiopaque e.g
  • Echogenic coatings are described in, e.g., U.S. Pat. Nos. 6,106,473 and 6,610,016.
  • contrast agents e.g., gadolinium (III) chelates or iron oxide compounds
  • a medical device may include radio-opaque or MRI visible markers (e.g., bands) that may be used to orient and guide the device during the implantation procedure.
  • Medical implants may, alternatively, or in addition, be visualized under visible light, using fluorescence, or by other spectroscopic means.
  • Visualization agents that can be included for this purpose include dyes, pigments, and other colored agents.
  • the medical implant may further include a colorant to improve visualization of the implant in vivo and/or ex vivo. Frequently, implants can be difficult to visualize upon insertion, especially at the margins of implant.
  • a coloring agent can be incorporated into a medical implant to reduce or eliminate the incidence or severity of this problem. The coloring agent provides a unique color, increased contrast, or unique fluorescence characteristics to the device.
  • a solid implant in one aspect, includes a colorant such that it is readily visible (under visible light or using a fluorescence technique) and easily differentiated from its implant site.
  • a colorant can be included in a liquid or semi-solid composition.
  • a single component of a two component mixture may be colored, such that when combined ex-vivo or in-vivo, the mixture is sufficiently colored.
  • the coloring agent may be, for example, an endogenous compound (e.g., an amino acid or vitamin) or a nutrient or food material and may be a hydrophobic or a hydrophilic compound.
  • the colorant has a very low or no toxicity at the concentration used.
  • colorants that are safe and normally enter the body through absorption such as ⁇ -carotene.
  • Representative examples of colored nutrients include fat soluble vitamins such as Vitamin A (yellow); water soluble vitamins such as Vitamin B12 (pink-red) and folic acid (yellow-orange); carotenoids such as ⁇ -carotene (yellow-purple) and lycopene (red).
  • coloring agents include natural product (berry and fruit) extracts such as anthrocyanin (purple) and saffron extract (dark red).
  • the coloring agent may be a fluorescent or phosphorescent compound such as ⁇ -tocopherolquinol (a Vitamin E derivative) or L-tryptophan. Derivatives, analogues, and isomers of any of the above colored compounds also may be used.
  • the method for incorporating a colorant into an implant or therapeutic composition may be varied depending on the properties of and the desired location for the colorant. For example, a hydrophobic colorant may be selected for hydrophobic matrices.
  • the colorant may be incorporated into a carrier matrix, such as micelles. Further, the pH of the environment may be controlled to further control the color and intensity.
  • the composition of the present invention include one or more coloring agents, also referred to as dyestuffs, which will be present in an effective amount to impart observable coloration to the composition, e.g., the gel.
  • coloring agents include dyes suitable for food such as those known as F. D. & C. dyes and natural coloring agents such as grape skin extract, beet red powder, beta carotene, annato, carmine, turmeric, paprika, and so forth. Derivatives, analogues, and isomers of any of the above colored compound also may be used.
  • the method for incorporating a colorant into an implant or therapeutic composition may be varied depending on the properties of and the desired location for the colorant. For example, a hydrophobic colorant may be selected for hydrophobic matrices.
  • the colorant may be incorporated into a carrier matrix, such as micelles. Further, the pH of the environment may be controlled to further control the color and intensity.
  • compositions of the present invention include one or more preservatives or bacteriostatic agents, present in an effective amount to preserve the composition and/or inhibit bacterial growth in the composition, for example, bismuth tribromophenate, methyl hydroxybenzoate, bacitracin, ethyl hydroxybenzoate, propyl hydroxybenzoate, erythromycin, chlorocresol, benzalkonium chlorides, and the like.
  • additional examples of the preservative include paraoxybenzoic acid esters, chlorobutanol, benzyl alcohol, phenethyl alcohol, dehydroacetic acid, sorbic acid, and the like.
  • the compositions of the present invention include one or more bactericidal (also known as bacteriacidal) agents.
  • compositions of the present invention include one or more antioxidants, present in an effective amount.
  • antioxidants include sulfites, alpha-tocopherol and ascorbic acid.
  • devices and compositions are provided that may or may not be associated with a device, which release an agent which induces fibrosis in vivo upon deployment of the device or administration of the composition.
  • the fibrosis-inducing agent or composition that comprises the fibrosis-inducing agent is delivered locally or regionally to the treatment site from the device or composition.
  • the therapeutic composition should be biocompatible, and release one or more fibrosing agents over a period of several hours, days, or months.
  • the devices of the present invention may be configured to release the scarring agent at one or more phases, the one or more phases having similar or different performance (e.g., release) profiles.
  • the therapeutic agent may be made available to the tissue at amounts which may be sustainable, intermittent, or continuous; in one or more phases; and/or rates of delivery; effective to increase or promote any one or more components of fibrosis (or scarring), including: formation of new blood vessels (angiogenesis), migration and proliferation of connective tissue cells (such as fibroblasts or smooth muscle cells), deposition of extracellular matrix (ECM), and remodeling (maturation and organization of the fibrous tissue); or the agent can act as a vascular wall irritant.
  • angiogenesis new blood vessels
  • connective tissue cells such as fibroblasts or smooth muscle cells
  • ECM extracellular matrix
  • remodeling maturation and organization of the fibrous tissue
  • the release rate may be programmed to impact fibrosis (or scarring) by releasing the scarring agent at a time such that at least one of the components of fibrosis is promoted or increased.
  • the predetermined release rate may reduce agent loading and/or concentration as well as potentially providing minimal drug washout and thus, increases efficiency of drug effect.
  • Any one of at least one scarring agent(s) may perform one or more functions, including promoting the formation of new blood vessels (angiogenesis), promoting the migration and proliferation of connective tissue cells (such as fibroblasts or smooth muscle cells), promoting the deposition of extracellular matrix (ECM), promoting remodeling (maturation and organization of the fibrous tissue) and/or acting as a vascular wall irritant.
  • the rate of release may provide a sustainable level of the scarring agent to the treatment site.
  • the rate of release is substantially constant.
  • the rate may decrease and/or increase over time, and it may optionally include a substantially non-release period.
  • the release rate may comprise a plurality of rates.
  • the plurality of release rates may include rates selected from the group consisting of substantially constant, decreasing, increasing, and substantially non-releasing.
  • the total amount of scarring agent made available on, in or near the device may be in an amount ranging from about 0.01 ⁇ g (micrograms) to about 2500 mg (milligrams).
  • the scarring agent may be in the amount ranging from 0.01 ⁇ g to about 10 ⁇ g; or from 10 ⁇ g to about 1 mg; or from 1 mg to about 10 mg; or from 10 mg to about 100 mg; or from 100 mg to about 500 mg; or from 500 mg to about 2500 mg.
  • the surface amount of scarring agent on, in or near the device may be in an amount ranging from less than 0.01 ⁇ g to about 250 ⁇ g per mm 2 of device surface area.
  • the scarring agent may be in the amount ranging from less than 0.01 ⁇ g/mm 2 ; or from 0.01 ⁇ g to about 10 ⁇ g/mm 2 ; or from 10 ⁇ g to about 25 ⁇ g/mm 2 ; or from 25 ⁇ g to about 250 ⁇ g/mm 2 .
  • the scarring agent that is on, in or near the device may be released from the composition and/or device in a time period that may be measured from the time of implantation, which ranges from about less than 1 day to about 180 days.
  • the release time may also be from about less than 1 day to about 7 days; from 7 days to about 14 days; from 14 days to about 28 days; from 28 days to about 56 days; from 56 days to about 90 days; from 90 days to about 180 days.
  • “quick release” or “burst” therapeutic compositions are provided that release greater than 10%, 20%, or 25% (w/v) of a fibrosis-inducing agent over a period of 7 to 10 days.
  • Such “quick release” compositions should, within certain embodiments, be capable of releasing therapeutic levels (where applicable) of a desired fibrosing agent.
  • “slow release” therapeutic compositions are provided that release less than 1% (w/v) of a fibrosis-inducing agent over a period of 7 to 10 days.
  • therapeutic compositions that release either less than 1% (w/v) of a fibrosing-inducing agent over a period longer than 10 days or do not release the therapeutic composition at all, but maintain the composition for a very long period of time such as for the entire duration of the device placement in the body.
  • the amount of scarring agent released from the composition and/or device as a function of time may be determined based on the in vitro release characteristics of the agent from the composition.
  • the in vitro release rate may be determined by placing the scarring agent within the composition or device in an appropriate buffer such as 0.1M phosphate buffer (pH 7.4)) at 37° C. Samples of the buffer solution are then periodically removed for analysis by either HPLC or by gravimetric means, and the buffer is replaced to avoid any saturation effects.
  • the release of scarring agent per day may range from an amount ranging from about 0.0 ⁇ g (micrograms) to about 2500 mg (milligrams).
  • the scarring agent that may be released in a day may be in the amount ranging from 0.0 to 0.01 ⁇ g; 0.01 ⁇ g to about 10 ⁇ g; or from 10 ⁇ g to about 1 mg; or from 1 mg to about 10 mg; or from 10 mg to about 100 mg; or from 100 mg to about 500 mg; or from 500 mg to about 2500 mg.
  • the scarring agent is made available to the susceptible tissue site in a constant but substantially unchanging manner so that the agent remains at the tissue essentially permanently.
  • the scarring agent is made available to the susceptible tissue in a sustained and/or controlled manner which results in increased efficiency and/or efficacy.
  • the release rates may vary during either or both of the initial and subsequent release phases. There may also be additional phase(s) for release of the same substance(s) and/or different substance(s).
  • compositions of the present invention should preferably be have a stable shelf-life for at least several months and capable of being produced and maintained under sterile conditions.
  • the composition may be sterile either by preparing them under aseptic environment and/or they may be terminally sterilized using methods available in the art.
  • Many pharmaceuticals are manufactured to be sterile and this criterion is defined by the USP XXII ⁇ 1211>.
  • USP refers to U.S. Pharmacopeia (see www.usp.org, Rockville, Md.). Sterilization may be accomplished by a number of means accepted in the industry and listed in the USP XXII ⁇ 1211>, including gas sterilization, ionizing radiation or, when appropriate, filtration.
  • Sterilization may be maintained by what is termed asceptic processing, defined also in USP XXII >1211>.
  • Acceptable gases used for gas sterilization include ethylene oxide.
  • Acceptable radiation types used for ionizing radiation methods include gamma, for instance from a cobalt 60 source and electron beam. A typical dose of gamma radiation is 2.5 MRad.
  • Sterilization may also occur by terminally using gamma radiation or electron beam sterilization methods. Filtration may be accomplished using a filter with suitable pore size, for example 0.22 ⁇ m and of a suitable material, for instance polytetrafluoroethylene (e.g., TEFLON). A combination of these methods may also be used to prepare the composition in the sterile form.
  • compositions and devices of the present invention are contained in a container that allows them to be used for their intended purpose.
  • Properties of the container that are important are a volume of empty space to allow for the addition of a constitution medium, such as water or other aqueous medium, e.g., saline, acceptable light transmission characteristics in order to prevent light energy from damaging the composition in the container (refer to USP XXII ⁇ 661>), an acceptable limit of extractables within the container material (refer to USP XXII), an acceptable barrier capacity for moisture (refer to USP XXII ⁇ 671>) or oxygen.
  • oxygen penetration this may be controlled by including in the container, a positive pressure of an inert gas, such as high purity nitrogen, or a noble gas, such as argon.
  • Typical materials used to make containers for pharmaceuticals include USP Type I through III and Type NP glass (refer to USP XXII ⁇ 661>), polyethylene, TEFLON, silicone, and gray-butyl rubber.
  • USP Types I to III glass and polyethylene are preferred.
  • any of the previously described fibrosis inducing agents, or derivatives and analogues thereof, can be utilized to create variations of the above compositions without deviating from the spirit and scope of the invention. It should also be apparent that the agent can be utilized in a composition with or without polymer carrier and that altering the carrier does not deviate from the scope of this invention.
  • Suitable fibrosing agents include tissue irritants such tissue as silk, wool, asbestos, silica, bleomycin, neomycin, talcum powder, metallic beryllium, and copper are particularly suitable for the practice of this invention.
  • agents which may be incorporated into or onto the implant or device or released from the implant or device include extracellular matrix components such as fibrous structural proteins (e.g., fibrillar collagens, nonfibrillar collagen and elastins), adhesive glycoproteins (e.g., laminin and fibronectin), proteoglycans (e.g., heparin sulphate, chondroitin sulphate, dermatan sulphate), hyaluronan (e.g., hyaluronic acid), secreted protein acidic and rich in cysteine (SPARC), thrombospondins, tenacin, inhibitors of matrix metalloproteinases (e.g., TIMPs and synthetic TIMPs such as marimistat, batimistat, doxycycline, tetracycline, minocycline, TROCADE, Ro-1130830, CGS 27023A, BMS-275291) and polylysine.
  • fibrous structural proteins e
  • EGF epidermal growth factor
  • TGF- ⁇ transforming growth factor- ⁇
  • TGF-9-1 transforming growth factor-9-2, TGF-9-3
  • PDGF platelet-derived growth factor
  • fibroblast growth factor acidic—aFGF; and basic—bFGF
  • VEGF vascular endothelial growth factor
  • VEGF-B vascular endothelial growth factor
  • VEGF-C placental growth factor
  • PIGF vascular endothelial growth factor
  • IGF insulin-like growth factors
  • HGF hepatocyte hrowth factor
  • CTGF connective tissue growth factor
  • CSFs myeloid colony-stimulating factors
  • GM-CSF granulocyte-macrophage colony-stimulating factors
  • G-CSF macrophage colony-
  • a range of polymeric and non-polymeric materials can be used to incorporate the fibrosis-inducing agent onto or into a device. Coating of the device with these fibrosis-inducing agent containing compositions or with the fibrosis-inducing agent only is one process that can be used to incorporate the fibrosis-inducing agent into or onto the device.
  • Dip coating is an example of a coating process that can be used to associate the fibrosis-inducing agent with the device.
  • the fibrosis-inducing agent is dissolved in a solvent for the fibrosis agent and is then coated onto the device.
  • the solvent is an inert solvent for the device such that the solvent does not dissolve the medical device to any great extent and is not absorbed by the device to any great extent.
  • the device can be immersed, either partially or completely, in the fibrosis-inducing agent/solvent solution for a specific period of time. The rate of immersion into the fibrosis-inducing agent/solvent solution can be altered (e.g., 0.001 cm per sec to 50 cm per sec). The device can then be removed from the solution. The rate at which the device can be withdrawn from the solution can be altered (e.g., 0.001 cm per sec to 50 cm per sec).
  • the coated device can be air-dried. The dipping process can be repeated one or more times depending on the specific application. The device can be dried under vacuum to reduce residual solvent levels. This process can result in the fibrosis-inducing agent being coated on the surface of the device.
  • the solvent is one that can not dissolve the device but can be absorbed by the device. These solvents can thus swell the device to some extent.
  • the device can be immersed, either partially or completely, in the fibrosis-inducing agent/solvent solution for a specific period of time (seconds to days).
  • the rate of immersion into the fibrosis-inducing agent/solvent solution can be altered (e.g., 0.001 cm per sec to 50 cm per sec).
  • the device can then be removed from the solution.
  • the rate at which the device can be withdrawn from the solution can be altered (e.g., 0.001 cm per sec to 50 cm per sec).
  • the coated device can be air-dried. The dipping process can be repeated one or more times depending on the specific application.
  • the device can be dried under vacuum to reduce residual solvent levels. This process can result in the fibrosis-inducing agent being adsorbed into the medical device.
  • the fibrosis-inducing agent may also be present on the surface of the device. The amount of surface associated fibrosis-inducing agent may be reduced by dipping the coated device into a solvent for the fibrosis-inducing agent or by spraying the coated device with a solvent for the fibrosis-inducing agent.
  • the solvent is one that can be absorbed by the device and that can dissolve the device.
  • the device can be immersed, either partially or completely, in the fibrosis-inducing agent/solvent solution for a specific period of time (seconds to hours).
  • the rate of immersion into the fibrosis-inducing agent/solvent solution can be altered (e.g., 0.001 cm per sec to 50 cm per sec).
  • the device can then be removed from the solution.
  • the rate at which the device can be withdrawn from the solution can be altered (e.g., 0.001 cm per sec to 50 cm per sec).
  • the coated device can be air-dried.
  • the dipping process can be repeated one or more times depending on the specific application.
  • the device can be dried under vacuum to reduce residual solvent levels.
  • This process can result in the fibrosis-inducing agent being adsorbed into the medical device as well as being surface associated.
  • the exposure time of the device to the solvent may be such as to not incur significant permanent dimensional changes to the device.
  • the fibrosis-inducing agent may also be present on the surface of the device. The amount of surface associated fibrosis-inducing agent may be reduced by dipping the coated device into a solvent for the fibrosis-inducing agent or by spraying the coated device with a solvent for the fibrosis-inducing agent.
  • the fibrosis-inducing agent and a polymer are dissolved in a solvent, for both the polymer and the fibrosing agent, and are then coated onto the device.
  • the device can be a device that has not been modified or device that has been further modified by coating with a polymer, surface treated by plasma treatment, flame treatment, corona treatment, surface oxidation or reduction, surface etching, mechanical smoothing or roughening, or grafting prior to the coating process.
  • the surface of the device can be treated with a plasma polymerization method prior to coating of the scarring agent or scarring agent containing composition, such that a thin polymeric layer is deposited onto the device surface.
  • a plasma polymerization method prior to coating of the scarring agent or scarring agent containing composition, such that a thin polymeric layer is deposited onto the device surface.
  • Examples of such methods include parylene coating of devices and the use of various monomers such hydrocyclosiloxane monomers. Parylene coating may be especially advantageous if the device, or portions of the device, are composed of materials (e.g., stainless steel, nitinol) that do not allow incorporation of the therapeutic agent(s) into the surface layer using one of the above methods.
  • a parylene primer layer may be deposited onto the device using a parylene coater (e.g., PDS 2010 LABCOTER2 from Cookson Electronics) and a suitable reagent (e.g., di-p-xylylene or dichloro-di-p-xylylene) as the coating feed material.
  • a parylene coater e.g., PDS 2010 LABCOTER2 from Cookson Electronics
  • a suitable reagent e.g., di-p-xylylene or dichloro-di-p-xylylene
  • Parylene compounds are commercially available, for example, from Specialty Coating Systems, Indianapolis, Ind.), including PARYLENE N (di-p-xylylene), PARYLENE C (a monchlorinated derivative of PARYLENE N, and PARYLENE D, a dichlorinated derivative of Parylene N.J.).
  • the solvent is an inert solvent for the device such that the solvent does not dissolve the medical device to any great extent and is not absorbed by the device to any great extent.
  • the device can be immersed, either partially or completely, in the fibrosis-inducing agent/polymer/solvent solution for a specific period of time. The rate of immersion into the fibrosis-inducing agent/polymer/solvent solution can be altered (e.g., 0.001 cm per sec to 50 cm per sec). The device can then be removed from the solution. The rate at which the device can be withdrawn from the solution can be altered (e.g., 0.001 cm per sec to 50 cm per sec).
  • the coated device can be air-dried. The dipping process can be repeated one or more times depending on the specific application. The device can be dried under vacuum to reduce residual solvent levels. This process can result in the fibrosis-inducing agent/polymer being coated on the surface of the device.
  • the solvent is one that can not dissolve the device but can be absorbed by the device. These solvents can thus swell the device to some extent.
  • the device can be immersed, either partially or completely, in the fibrosis-inducing agent/polymer/solvent solution for a specific period of time (seconds to days).
  • the rate of immersion into the fibrosis-inducing agent/polymer/solvent solution can be altered (e.g., 0.001 cm per sec to 50 cm per sec).
  • the device can then be removed from the solution.
  • the rate at which the device can be withdrawn from the solution can be altered (e.g., 0.001 cm per sec to 50 cm per sec).
  • the coated device can be air-dried.
  • the dipping process can be repeated one or more times depending on the specific application.
  • the device can be dried under vacuum to reduce residual solvent levels. This process can result in the fibrosis-inducing agent/polymer being coated onto the surface of the device as well as the potential for the fibrosis-inducing agent being adsorbed into the medical device.
  • the fibrosis-inducing agent may also be present on the surface of the device.
  • the amount of surface associated fibrosis-inducing agent may be reduced by dipping the coated device into a solvent for the fibrosis-inducing agent or by spraying the coated device with a solvent for the fibrosis-inducing agent.
  • the solvent is one that can be absorbed by the device and that can dissolve the device.
  • the device can be immersed, either partially or completely, in the fibrosis-inducing agent/solvent solution for a specific period of time (seconds to hours).
  • the rate of immersion into the fibrosis-inducing agent/solvent solution can be altered (e.g., 0.001 cm per sec to 50 cm per sec).
  • the device can then be removed from the solution.
  • the rate at which the device can be withdrawn from the solution can be altered (e.g., 0.001 cm per sec to 50 cm per sec).
  • the coated device can be air-dried.
  • the dipping process can be repeated one or more times depending on the specific application.
  • the device can be dried under vacuum to reduce residual solvent levels.
  • the exposure time of the device to the solvent may be such that there is not significant permanent dimensional changes to the device (other than those associated with the coating itself).
  • the fibrosis-inducing agent may also be present on the surface of the device. The amount of surface associated fibrosis-inducing agent may be reduced by dipping the coated device into a solvent for the fibrosis-inducing agent or by spraying the coated device with a solvent for the fibrosis-inducing agent.
  • the device can be a device that has not been modified as well as a device that has been further modified by coating with a polymer (e.g., parylene), surface treated by plasma treatment, flame treatment, corona treatment, surface oxidation or reduction, surface etching, mechanical smoothing or roughening, or grafting prior to the coating process.
  • a polymer e.g., parylene
  • a suspension of the fibrosis-inducing agent in a polymer solution can be prepared.
  • the suspension can be prepared by choosing a solvent that can dissolve the polymer but not the fibrosis-inducing agent or a solvent that can dissolve the polymer and in which the fibrosis-inducing agent is above its solubility limit.
  • a device can be dipped into the suspension of the fibrosis-inducing agent and polymer solution such that the device is coated with a polymer that has a fibrosing agent suspended within it.
  • Spray coating is another type of coating process that can be used.
  • a solution or suspension of the fibrosis-inducing agent, with or without a polymeric or non-polymeric carrier is nebulized and directed to the device to be coated by a stream of gas.
  • spray devices such as an air-brush (for example models 2020, 360, 175, 100, 200, 150, 350, 250, 400, 3000, 4000, 5000, 6000 from Badger Air-brush Company, Franklin Park, Ill.), spray painting equipment, TLC reagent sprayers (for example Part # 14545 and 14654, Alltech Associates, Inc. Deerfield, Ill., and ultrasonic spray devices (for example those available from Sono-Tek, Milton, N.Y.).
  • air-brush for example models 2020, 360, 175, 100, 200, 150, 350, 250, 400, 3000, 4000, 5000, 6000 from Badger Air-brush Company, Franklin Park, Ill.
  • TLC reagent sprayers for example Part # 14545
  • the fibrosis-inducing agent is dissolved in a solvent for the fibrosis agent and is then sprayed onto the device.
  • the solvent is an inert solvent for the device such that the solvent does not dissolve the medical device to any great extent and is not absorbed by the device to any great extent.
  • the device can be held in place or the device can be mounted onto a mandrel or rod that has the ability to move in an X, Y or Z plane or a combination of these planes.
  • the device can be spray coated such that the device is either partially or completely coated with the fibrosis-inducing agent/solvent solution.
  • the rate of spraying of the fibrosis-inducing agent/solvent solution can be altered (e.g., 0.001 ml per sec to 10 ml per sec) to ensure that a good coating of the fibrosis-inducing agent is obtained.
  • the coated device can be air-dried.
  • the spray coating process can be repeated one or more times depending on the specific application.
  • the device can be dried under vacuum to reduce residual solvent levels. This process can result in the fibrosis-inducing agent being coated on the surface of the device.
  • the solvent is one that can not dissolve the device but can be absorbed by the device. These solvents can thus swell the device to some extent.
  • the device can be spray coated, either partially or completely, in the fibrosis-inducing agent/solvent solution. The rate of spraying of the fibrosis-inducing agent/solvent solution can be altered (e.g., 0.001 ml per sec to 10 ml per sec) to ensure that a good coating of the fibrosis-inducing agent is obtained.
  • the coated device can be air-dried.
  • the spray coating process can be repeated one or more times depending on the specific application.
  • the device can be dried under vacuum to reduce residual solvent levels.
  • This process can result in the fibrosis-inducing agent being adsorbed into the medical device.
  • the fibrosis-inducing agent may also be present on the surface of the device.
  • the amount of surface associated fibrosis-inducing agent may be reduced by dipping the coated device into a solvent for the fibrosis-inducing agent or by spraying the coated device with a solvent for the fibrosis-inducing agent.
  • the solvent is one that can be absorbed by the device and that can dissolve the device.
  • the device can be spray coated, either partially or completely, in the fibrosis-inducing agent/solvent solution.
  • the rate of spraying of the fibrosis-inducing agent/solvent solution can be altered (e.g., 0.001 ml per sec to 10 ml per sec) to ensure that a good coating of the fibrosis-inducing agent is obtained.
  • the coated device can be air-dried.
  • the spray coating process can be repeated one or more times depending on the specific application.
  • the device can be dried under vacuum to reduce residual solvent levels. This process can result in the fibrosis-inducing agent being adsorbed into the medical device as well as being surface associated.
  • the exposure time of the device to the solvent may be such as to not incur significant permanent dimensional changes to the device.
  • the fibrosis-inducing agent may also be present on the surface of the device. The amount of surface associated fibrosis-inducing agent may be reduced by dipping the coated device into a solvent for the fibrosis-inducing agent or by spraying the coated device with a solvent for the fibrosis-inducing agent.
  • the fibrosis-inducing agent and a polymer are dissolved in a solvent, for both the polymer and the fibrosing agent, and are then spray coated onto the device.
  • the device can be a device that has not been modified as well as a device that has been further modified by coating with a polymer (e.g., parylene), surface treated by plasma treatment, flame treatment, corona treatment, surface oxidation or reduction, surface etching, mechanical smoothing or roughening, or grafting prior to the coating process.
  • a polymer e.g., parylene
  • the solvent is an inert solvent for the device such that the solvent does not dissolve the medical device to any great extent and is not absorbed by the device to any great extent.
  • the device can be spray coated, either partially or completely, in the fibrosis-inducing agent/polymer/solvent solution for a specific period of time. The rate of spraying of the fibrosis-inducing agent/solvent solution can be altered (e.g., 0.001 ml per sec to 10 ml per sec) to ensure that a good coating of the fibrosis-inducing agent is obtained.
  • the coated device can be air-dried.
  • the spray coating process can be repeated one or more times depending on the specific application.
  • the device can be dried under vacuum to reduce residual solvent levels. This process can result in the fibrosis-inducing agent/polymer being coated on the surface of the device.
  • the solvent is one that can not dissolve the device but can be absorbed by the device. These solvents can thus swell the device to some extent.
  • the device can be spray coated, either partially or completely, in the fibrosis-inducing agent/polymer/solvent solution. The rate of spraying of the fibrosis-inducing agent/solvent solution can be altered (e.g., 0.001 ml per sec to 10 ml per sec) to ensure that a good coating of the fibrosis-inducing agent is obtained.
  • the coated device can be air-dried. The spray coating process can be repeated one or more times depending on the specific application.
  • the device can be dried under vacuum to reduce residual solvent levels.
  • This process can result in the fibrosis-inducing agent/polymer being coated onto the surface of the device as well as the potential for the fibrosis-inducing agent being adsorbed into the medical device.
  • the fibrosis-inducing agent may also be present on the surface of the device.
  • the amount of surface associated fibrosis-inducing agent may be reduced by dipping the coated device into a solvent for the fibrosis-inducing agent or by spraying the coated device with a solvent for the fibrosis-inducing agent.
  • the solvent is one that can be absorbed by the device and that can dissolve the device.
  • the device can be spray coated, either partially or completely, in the fibrosis-inducing agent/solvent solution.
  • the rate of spraying of the fibrosis-inducing agent/solvent solution can be altered (e.g., 0.001 ml per sec to 10 ml per sec) to ensure that a good coating of the fibrosis-inducing agent is obtained.
  • the coated device can be air-dried.
  • the spray coating process can be repeated one or more times depending on the specific application.
  • the device can be dried under vacuum to reduce residual solvent levels.
  • the exposure time of the device to the solvent may be such as to not incur significant permanent dimensional changes to the device (other than those associated with the coating itself).
  • the fibrosis-inducing agent may also be present on the surface of the device. The amount of surface associated fibrosis-inducing agent may be reduced by dipping the coated device into a solvent for the fibrosis-inducing agent or by spraying the coated device with a solvent for the fibrosis-inducing agent.
  • the device can be a device that has not been modified as well as a device that has been further modified by coating with a polymer (e.g., parylene), surface treated by plasma treatment, flame treatment, corona treatment, surface oxidation or reduction, surface etching, mechanical smoothing or roughening, or grafting prior to the coating process.
  • a polymer e.g., parylene
  • the fibrosis inducing agent can be attached directly to the device. This can be accomplished by using an adhesive (e.g., cyanoacrylate, polymer/solvent solution), using a thermal process and or by sewing the fibrosis agent into or onto the device.
  • the fibrosis inducing agent can be in the form of particles (irregular, regular, porous, spherical), threads, fibers, knits, weaves or electrospun material.
  • silk can be prepared as a knitted, woven or electrospun material. This material can then be placed on the surface of the device. Sutures and/or an adhesive can then be used to secure the silk material to the device.
  • the fibrosis inducing agent can be dissolved in a suitable solvent. This solution can then be applied to the device using an electrospraying or electrospinning process. Polymeric or non-polymeric additives can be added to this solution to assist in the electrospraying or electrospinning process and or to assist in the adhesion of the fibrosis inducing agent to the device. For example, silk can be dissolved in HFIP and this can then be electrosprayed or electrospun onto the device (e.g., stent).
  • the fibrosis-inducing agent can be incorporated into the device during or post manufacture of the device.
  • silk fibers could be woven into a hernia mesh to provide a product that contains the fibrosis-inducing agent that is incorporated into the device.
  • Medical devices and implants of the present invention may be utilized to induce a fibrotic reaction around the device/implant that results in an enhanced bond between the tissue and the prosthesis.
  • Such medical devices and implants provide a solution to the following common problems associated with a variety of clinical interventions.
  • DDD degenerative disc disease
  • the vertebral column is composed of vertebral bone plates separated by intervertebral discs that form strong joints and absorb spinal compression during movement.
  • the intervertebral disc is comprised of an inner gel-like substance called the nucleus pulposus which is surrounded by a tough fibrocartilagenous capsule called the annulus fibrosis.
  • the nucleus pulposus is composed of a loose framework of collagen fibrils and connective tissue cells (resembling fibroblasts and chondrocytes) embedded in a gelatinous matrix of glycosaminoglycans and water.
  • the annulus fibrosus is composed of numerous concentric rings of fibrocartilage that anchor into the vertebral bodies.
  • the most common cause of DDD occurs when tears in the annulus fibrosis create an area of localized weakness that allow bulging, herniation or sequestration of the nucleus pulposis and annulus fibrosis into the spinal canal and/or spinal foramena.
  • the bulging or herniated disc often compresses nerve tissue such as spinal cord fibers or spinal cord nerve root fibers. Pressure on the spinal cord or nerve roots from the damaged intervertebral disc results in neuronal dysfunction (numbness, weakness, tingling), crippling pain, bowel or bladder disturbances and can frequently cause long-term disability.
  • DDD DDD-induced fibrosis-inducing agent
  • microdiscectomy major surgical resection of the disc
  • spinal fusion fusion of adjacent vertebral bone plates using various techniques and devices
  • implantation of an artificial disc The present invention provides for the application of an adhesion or fibrosis-inducing agent in the surgical management of DDD.
  • the present invention provides injectable compositions that iriclude a bulking or filling agent and a fibrosing agent for direct injection into damaged intervertebral discs.
  • An injectable material containing a fibrosis-inducing agent that can be injected into an intervertebral disc space (alone or in combination with polymeric carrier, which may be in the form, e.g., of a gel, paste, or spray) is used to enhance scarring and support the annular ring of the disc (e.g., by inducing the production of fibrous tissue and fibrocartilage), thus reducing the risk of disc rupture and restoring disc function without surgery (embodiments for application during disc surgery are described below).
  • the injectable composition containing a fibrosis-inducing agent can further contain an agent that promotes bone growth if permanent fixation (immobilization) of adjacent vertebra is desired.
  • a needle is inserted into the intervertebral disc, a guidewire is advanced into the tissue and a dual lumen catheter (for many of the hydrogels described below such as COSEAL, COSTASIS, FLOSEAL, TISSEAL, VITOSS, and materials made from 4-armed thiol PEG (10K), 4-armed NHS PEG(10K) and methylated collagen, such as described above or a single lumen catheter (for materials such as cyanoacrylate, CORTOSS, bone cement, apatitehydroxyapatite, calcium phosphate, calcium sulfate, hyaluronic acid, proteins, carbohydrates, sclerosing agents, and the like) is advanced into the disc.
  • a dual lumen catheter for many of the hydrogels described below such as COSEAL, COSTASIS, FLOSEAL, TISSEAL, VITOSS, and materials made from 4-armed thiol PEG (10K), 4-armed NHS PEG(10K) and methylated collagen, such as described above or a
  • a needle coated with an ultrasound imaging coating formulation such as ECHO—COAT (Angiotech Pharmaceuticals, Inc.) or the addition of contrast agents (e.g., barium, tantalum, technitium, gadolinium, etc.) for localization by x-ray.
  • ECHO—COAT Angiotech Pharmaceuticals, Inc.
  • contrast agents e.g., barium, tantalum, technitium, gadolinium, etc.
  • a composition containing a fibrosis-inducing agent, with or without a bone morphogenic protein(s), and/or an osteogenic growth factor (such as transforming growth factor, platelet-derived growth factor, fibroblast growth factor) is injected via the catheter into the disc.
  • a fibrosis-inducing agent with or without a bone morphogenic protein(s), and/or an osteogenic growth factor (such as transforming growth factor, platelet-derived growth factor, fibroblast growth factor) is injected via the catheter into the disc.
  • an osteogenic growth factor such as transforming growth factor, platelet-derived growth factor, fibroblast growth factor
  • Chemonucleolysis agents such as collagenase, chymopapain or other tissue-degrading enzymes may also be used to chemically degrade the remaining disc tissue prior to the injection of the fibrosing composition.
  • the fibrosis-inducing agent with or without a bone morphogenic protein, and/or an osteogenic growth factor can encourage fibrous ankylosis, followed by bony ankylosis of the intervertebral space leading to increased stability and reduced pain.
  • the injectable material may contain a polymer system that can provide sustained release of the fibrosis-inducing agent, bone morphogenic protein, and/or osteogenic growth factor to enhance efficacy and reduce the need for repeat administrations of active agents.
  • the polymeric injection material suitable for delivery of a fibrosis-inducing agent, bone morphogenic protein, and/or growth factor that promotes bone growth can be either a non-degradable or a degradable material.
  • Suitable non-degradable materials include crosslinked compositions that comprise PVA, PVP, polyacrylamide, methyl methacrylate (MMA) and methyl methacrylate-styrene (MMA-styrene) which when mixed together form polymethyl methacrylate (PMMA) or bone cement (e.g., SIMPLEX P made by Stryker Howmedica, ZIMMER REGULAR and ZIMMER LOW VISCOSITY CEMENT, PALACOS, CMW-1 and CMW-2, ENDURANCE), synthetic cancellous bone void fillers (e.g., CORTOSS), pHEMA, poly(vinyl PEG), poly(styrene sulfonate), poly(acrylic acid), poly(methacrylic acid), as well as other polymers that are known to form hydrogels.
  • PMMA polymethyl methacrylate
  • MMA-styrene methyl methacrylate-styrene
  • synthetic cancellous bone void fillers e.g., CORT
  • compositions include blends and copolymers of the agents listed above.
  • Suitable degradable materials include, but are not limited to, resorbable ceramics composed of ⁇ -tricalcium phosphate (e.g., VITOSS and PROOSTEON 500R), hydroxyapatite or Ca 10 (PO 4 ) 6 OH (e.g., BIOOSS and OSTEOGRAF), calcium carbonate or CaCO 3 , calcium sulfate (e.g., OSTEOSET and ALLOMATRIX made by Wright Medical Technology, Inc.), calcium phosphate (e.g., CALCIBON or NORIAN SRS), crosslinked materials of PEG, gelatin, collagen, bone allografts (e.g., ALLOGRO (Allosource Corporation, Centennial, Colo.), ORTHOBLAST (GenSci Regeneration Sciences, Inc., Canada), OPTEFORM (Exactech, Inc., Gainesville, Fla.), GRAFTON (Osteotech, Inc., Eatontown
  • the injectable material also contains a biologically active agent capable of inducing fibrosis and ankylosis in the disc space.
  • the injectable material is loaded with a fibrosis-inducing agent and injected into the intervertebral disc to help repair the annulus and prevent herniation of the nucleus pulposis.
  • the injectable material contains biologically active agents capable of inducing bone growth such bone morphogenic proteins and growth factors (transforming growth factor, platelet-derived growth factor, fibroblast growth factor) to promote bony ankylosis and fusion of adjacent vertebra.
  • the injectable material can be utilized to deliver a sclerosant to the articular space.
  • Sclerosants include compounds such as ethanol, DMSO, surfactants, sucrose, NaCl, dextrose, glycerin, minocycline, tetracycline, doxycycline, polidocanol, sodium tetradecyl sulfate, sodium morrhuate, sotradecol and others.
  • the injectable material can further comprise agents such as glycerol, glycerin, PEG 200, triethyl citrate, and triacetin as plasticizers.
  • the injectable materials described above can be further modified to be comprised of, or contain, polymeric threads.
  • Polymeric threads have the ability to induce a fibroproliferative response from the surrounding tissue. These polymer threads can be degradable or non-degradable.
  • Degradable threads can be composed of degradable polyesters, polyanhydrides, poly(anhydride esters), poly(ester-amides), poly(ester-ureas), polyorthoesters, polyphosphoesters, polyphosphazines, cyanoacrylate polymers, collagen, chitosan, hyaluronic acid, chromic cat gut, alginates, starch, cellulose, cellulose esters, blends and copolymers thereof, as well as other known degradable polymers.
  • Non-degradable polymers that can be used include, but are not limited to, polyesters (e.g., PET), polyurethanes, silicones, PE, PP, PS, PAA, PMA, silk, blends, copolymers thereof as well as other known polymers.
  • the threads can be composed of a single composition or composed of a blend of differing compositions.
  • the polymeric threads themselves can be further modified through the addition of a polymeric coating applied to the threads.
  • the polymer used for coating the thread can be similar to that described above for the threads themselves.
  • the polymer coating may further comprise a biologically active agent that has the ability to induce a fibroproliferative or osteogenic response.
  • the agents that can be used are further described in the section (vi) below.
  • the injectable materials described above can be utilized to deliver a particulate material that has the ability to induce fibrosis in the intervertebral disc.
  • These particles can be either degradable or non-degradable and are similar to those described above for threads.
  • Additional particulate materials useful for the practice of this embodiment include silk, talc, starch, glass, silicates, silica, calcium phosphate, calcium sulfate, calcium carbonate, hydroxyapatite, synthetic mineral (e.g., VITOSS and CORTOSS, PMMA, silver nitrate, ceramic particles and other inorganic particles known in the art to induce a fibroprqliferative response followed by mineralization.
  • the particles used in this embodiment can be all of the same composition or a blend of differing compositions. These particles can also be used as a coating applied to the polymeric strands as described above.
  • the injectable materials can also be constructed such that it is comprised of both polymeric threads and particles.
  • the threads and particles used are similar to those described above and may be of uniform composition or blended composition. Virtually any combination of threads of differing compositions and particles of differing compositions can be utilized in this embodiment.
  • the hydrogel, the polymeric threads, and the particles can all be utilized to deliver one or more biologically active agents, as described below.
  • One specific composition comprises rods prepared from a methylated collagen-crosslinked poly(ethylene glycol) composition such as described above, which has powdered silk particles and/or mineral particles added to the composition prior to curing. Once deployed, the rod can absorb water, fill the disc space and adhere to any fibrocartilage or exposed bone. This expansion can prevent the rod from moving, while the powdered silk and/or mineral particles can initiate an ankylosing response. As the material starts to degrade, the material can support the bone tissue ingrowth that is initiated and potentiated by the particles. Bone morphogenic proteins and/or growth factors (described previously and below) are also useful for inclusion in this composition.
  • a sclerosant such as a surfactant (SDS), ethanolamine oleate or DMSO can be added.
  • SDS surfactant
  • ethanolamine oleate DMSO
  • the amino PEG can provide a gel that can take a longer time to degrade and can provide some positive charge to further attract cellular material.
  • Another embodiment consists of an injectable implant composed of silk fibers or from a polymerized version of the fibrosing agent itself (i.e., repeating units of the fibrosing agent polymerized together). Bone morphogenic proteins and/or growth factors (described previously and below) also may be added to this composition.
  • compositions suitable for use in minimally invasive intervertebral disc procedures involve the deployment of a biomaterial into the nucleus pulposis with or without the addition of a fibrosis-inducing agent, bone morphogenic protein(s), and/or a suitable growth factor(s).
  • compositions can be delivered into the intervertebral disc via specialized delivery catheters, an endoscope, a needle or other applicator, a surgically placed drain or access port, or other transdermal access device, including administration of: (a) fluids, suspensions, emulsions, microemulsions, microspheres, pastes, gels, microparticulates, sprays, aerosols, solid implants and other formulations which release a biologically active fibrosis-inducing agent(s); (b) microparticulate silk and/or silk strands (linear, branched, and/or coiled) either alone, or loaded with an additional fibrosis-inducing agent, bone morphogenic protein, and/or growth factor are also useful for directed injection into the intervertebral disc; (c) injectable collagen-containing formulations such as COSTASIS or materials made from 4-armed thiol PEG (10K), 4-armed NHS PEG(10K) and methylated collagen such as described above, either alone, or loaded
  • This hydrogel may further contain collagen, methylated collagen and/or gelatin.
  • This hydrogel can further comprise the fibrosis-inducing agents described above (e.g., silk powder or silk threads).
  • a radio-opaque material e.g., tantalum, barium, other metal, or a contrast material
  • the injected material can be visualized radiographically or by MRI.
  • fibrosis-inducing agents for use in spinal prostheses (e.g., devices and bulking agents) include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, and CTGF, as well as analogues and derivatives of the aforementioned.
  • the device may additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, or growth hormone) and/or a bone morphogenic protein (BMP) (e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, or BMP-7 or an analogue or derivative thereof).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, or growth hormone
  • BMP bone morphogenic protein
  • the device may comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • dexamethasone isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • dexamethasone isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , die
  • the patient For open surgical resection of a ruptured lumbar disc (laminectomy) the patient is placed in a modified kneeling position under general anesthesia. An incision is made in the posterior midline and the tissue is dissected away to expose the appropriate interspace; the ligamentum flavum is dissected and in some cases portions of the bony lamina are removed to allow adequate visualization. The nerve root is carefully retracted away to expose the herniated fragment and the defect in the annulus. Typically, the cavity of the disc is entered from the tear in the annulus and the loose fragments of the nucleus pulposus are removed with pituitary forceps.
  • any additional fragments of disc sequestered inside or outside of the disc space are also carefully removed and the disc space is forcefully irrigated to remove to remove any residual fragments. If tears are present in the dura, the dura is closed with sutures that are often augmented with fibrin glue. The tissue is then closed with absorbable sutures.
  • Microlumbar disc excision can be performed as an outpatient procedure and has largely replaced laminectomy as the intervention of choice for herniated discs.
  • a one inch incision is made from the spinous process above the disc affected to the spinous process below.
  • the tissue is dissected down to the ligamentum flavum and bone is removed from the lamina until the nerve root can be clearly identified.
  • the nerve root is carefully retracted and the tears in the annulus are visualized under magnification.
  • Microdisc forceps are used to remove disc fragments through the annular tear and any sequestered disc fragments are also removed.
  • the disc space is irrigated to remove any disc fragments, any dural tears are repaired and the tissue is closed with absorbable sutures.
  • anterior (abdominal) approaches can also be used for both open and endoscopic lumbar disc excision. Cervical and thoracic disc excisions are similar to lumbar procedures and can also be performed from a posterior approach (with laminectomy) or as an anterior discectomy with fusion.
  • the present invention provides injectable compositions to promote scarring of the annulus, scarring of dural defects and stabilization of adjacent vertebra.
  • the fibrosing agent or fibrosing agent containing composition is delivered under direct vision during open or endoscopic disc excision.
  • the composition containing the fibrosis-inducing agent is applied to the annulus or the dural defect directly (in open surgical procedures) or through the side port of an endoscope.
  • the fibrosis-inducing agent can assist in the production of strong fibrotic tissue in the annulus fibrosis at the previous site of herniation or rupture. This can reinforce the weak portion of the intervertebral disc and reduce the likelihood of subsequent re-rupture.
  • the fibrosis-inducing agent can assist in the healing of the dura and prevent complications such as CSF leakage.
  • the material may also be composed of a polymer system to provide sustained release of the fibrosis-inducing agent.
  • the material suitable for delivery of a fibrosis-inducing agent for the purposes of this invention can be composed of a non-degradable or a degradable material.
  • Suitable non-degradable materials can include crosslinked compositions that comprise PVA, PVP, polyacrylamide, methyl methacrylate (MMA) and methyl methacrylate styrene (MMA-styrene) which when mixed together form polymethyl methacrylate (PMMA) or bone cement (e.g., SIMPLEX P ZIMMER REGULAR or ZIMMER LOW VISCOSITY CEMENT, PALACOS, CMW-1, CMW-2 or ENDURANCE), synthetic cancellous bone void fillers (e.g., CORTOSS), PHEMA, poly(vinyl PEG), poly(styrene sulfonate), poly(acrylic acid), poly(methacrylic acid), as well as other polymers that are known to form hydrogels.
  • PMMA polymethyl methacrylate
  • MMA-styrene methyl methacrylate styrene
  • synthetic cancellous bone void fillers e.g., CORTOSS
  • PHEMA poly
  • compositions include blends and copolymers of the agents listed above.
  • Suitable degradable materials include, but are not limited to, resorbable ceramics composed of ⁇ -tricalcium phosphate (e.g., VITOSS and PROOSTEON 500R), hydroxyapatite or Ca 10 (PO 4 ) 6 OH (e.g., BIOOSS, OSTEOGRAF), calcium carbonate or CaCO 3 , calcium sulfate (e.g., OSTEOSET and ALLOMATRIX), calcium phosphate (e.g., CALCIBON or NORIAN SRS), crosslinked materials of PEG, gelatin, collagen, bone allografts (e.g., ALLOGRO, ORTHOBLAST, OPTEFORM, GRAFTON), mesenchymal stem cells, hyaluronic acid, hyaluronic acid derivatives, polysaccharides, carbohydrates, proteins (e.g., albumin, casein, whey proteins, plant proteins, and fish proteins), auto
  • One material that is of particular interest for use in annulus and dural repairs during intervertebral disc surgery is an injectable material prepared from a 4-armed thiol PEG (10K), a 4-armed NHS PEG(10K) and methylated collagen such as described above.
  • the injectable material also contains a biologically active agent capable of inducing fibrosis to reinforce the annulus fibrosis (to reduce the risk of repeat herniation or rupture) or assist in the repair of dural defects (to prevent CSF leaks).
  • Preferred biologically active agents for use in combination with the injectable material include fibrosis-inducing agents and growth factors (e.g., transforming growth factor, platelet-derived growth factor, fibroblast growth factor), whose dosages and release kinetics are all described in detail in section (vi) below.
  • growth factors e.g., transforming growth factor, platelet-derived growth factor, fibroblast growth factor
  • the materials described above can further modified to be comprised of, or contain, polymeric threads.
  • Polymeric threads have the ability to induce a fibroproliferative response in the annulus fibrosis or the dura. These polymer threads can be degradable or non-degradable.
  • Degradable threads can be composed of degradable polyesters, polyanhydrides, poly(anhydride esters), poly(ester-amides), poly(ester-ureas), polyorthoesters, polyphosphoesters, polyphosphazines, cyanoacrylate polymers, collagen, chitosan, hyaluronic acid, chromic cat gut, alginates, starch, cellulose, cellulose esters, blends and copolymers thereof, as well as other known degradable polymers.
  • Non-degradable polymers that can be used include, but are not limited to, polyesters (e.g., PET), polyurethanes, silicones, PE, PP, PS, PM, PMA, silk, blends, copolymers thereof.
  • the threads used can be composed of a single composition or composed of a blend of differing compositions.
  • the polymeric threads themselves can be further modified through the addition of a polymeric coating applied to the threads.
  • the polymer used for coating the thread can be similar to that described above for the threads themselves.
  • the polymer coating may further comprise a biologically active agent that has the ability to induce a fibroproliferative response.
  • the agents that can be used are further described in the section (vi) below.
  • the materials described above can also be utilized to deliver a particulate material that has the ability to induce fibrosis.
  • These particles can be either degradable or non-degradable and are similar to those described above for threads.
  • particulate materials useful for the practice of this embodiment include silk, talc, starch, glass, silicates, silica, calcium phosphate, calcium sulfate, calcium carbonate, hydroxyapatite, synthetic mineral (e.g., VITOSS and CORTOSS), PMMA, silver nitrate, ceramic particles and other inorganic particles known in the art to induce a fibroproliferative response followed by mineralization.
  • the particles used in this embodiment can be all of the same composition or a blend of differing compositions. These particles can also be used as a coating applied to the polymeric strands as described above.
  • the materials used in the present invention can also be constructed such that they are comprised of both polymeric threads and particles.
  • the threads and particles used are similar to those described above and may be of uniform composition or blended composition. Virtually any combination of threads of differing compositions and particles of differing compositions can be utilized in this embodiment.
  • the hydrogels e.g., injectable materials prepared from a 4-armed thiol PEG (10K), a 4-armed NHS PEG(10K) and methylated collagen
  • the polymeric threads, and the particles can all be utilized to deliver one or more biologically active agents, as described below.
  • compositions are suitable for use in open surgical disc resection and microdiscectomy. All involve the deployment of a biomaterial and a fibrosis-inducing agent to reinforce the annulus fibrosis or assist in dural repair.
  • the following compositions can be delivered during surgical disc resection and microdiscectomy either directly, using specialized delivery catheters, via an endoscope, or through a needle or other applicator: (a) fluids, suspensions, emulsions, microemulsions, microspheres, pastes, gels, microparticulates, sprays, aerosols, solid implants and other formulations which release a fibrosis-inducing agent(s); (b) microparticulate silk and/or silk strands (linear, branched, and/or coiled) either alone, or loaded with an additional fibrosis-inducing agent and/or growth factor; (c) collagen-containing formulations such as COSTASIS or materials made from 4-armed thiol PEG (10K), 4-armed NHS PEG (10
  • This hydrogel mayfurther contain collagen, methylated collagen and/or gelatin.
  • This hydrogel can further comprise the fibrosis-inducing agents described above (e.g., silk powder or silk threads). and/or (m) films, sponges or meshes such as INTERCEED, VICRYL mesh, and GELFOAM either alone, or loaded with a fibrosis-inducing agent and/or growth factor.
  • fibrosis-inducing agents for use in spinal prostheses (e.g., devices and bulking agents) include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, and CTGF, as well as analogues and derivatives of the aforementioned.
  • the device may additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone) and/or a bone morphogenic protein (BMP) (e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, or BMP-7 or an analogue or derivative thereof).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone
  • BMP bone morphogenic protein
  • the device may alone or additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • dexamethasone isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • dexamethasone isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3
  • Osteoporosis is a progressive degenerative bone disease characterized by decreased bone mineral density, degradation of bone microarchitecture and reduced bone strength. The weakened bone is often unable to withstand stress, or even normal weight-bearing activities, and is at an increased risk for sustaining fractures. Fractures are the most common clinical manifestation of osteoporosis and the condition is often asymptomatic until the breakage occurs. Osteoporosis is the cause of 1.3 million fractures each year in the U.S. and is estimated to cost the healthcare system over $10 billion annually. Fractures of the hip, wrist and other long bones are common in osteoporosis, but approximately 550,000 patients in the U.S. (700,000 worldwide) suffer vertebral compression fractures as a result of their disease.
  • the weakened cancellous bone of the vertebral column essentially collapses (compresses) under the weight placed on it during normal activities and the vertebra loses height (i.e., the center of the vertebra collapses and the two endplates of the vertebra move closer together). Compression of the vertebra leads to pain, a loss of height, curvature of the spine (kyphosis), and in some cases, breathing problems due to pressure placed on the chest cavity and lungs.
  • Vertebroplasty utilizes bone cement (polymethylmethacrylate —PMMA) injected under pressure into the fracture under x-ray guidance to stabilize the fracture, provide support and reduce pain. This procedure can often be performed as an outpatient and provides almost immediate symptomatic relief and early mobilization.
  • PMMA polymethylmethacrylate
  • Kyphoplasty involves the insertion of a balloon (KYPHX Inflatable Bone Tamp made by Kyphon Inc., Sunnyvale, Calif.) into the fracture which is then inflated inside the bone to create a void, stabilize the fracture and straighten the bone and spine (i.e., restore the vertebral height lost as a result of the compression fracture).
  • the surgeon then injects bone filler (typically PMMA or a calcium phosphate-based material) via specialized access devices (Inflation Syringe and Bone Access System also made by Kyphon, Inc. (Sunnyvale, Calif.) into the space under C-arm image-guided fluoroscopy to support the fractured vertebra).
  • Injecting the bone cement into the balloon-created cavity enables the injection to be performed under low pressure and reduces the incidence of neurological injury associated with cement leakage.
  • cement leakage occurs in 30-73% of patients versus only 8-9% of those treated with kyphoplasty.
  • the present invention provides injectable compositions that include a bulking or filling agent and a fibrosing agent for direct injection into vertebral compression fractures as part of vertebroplasty or kyphoplasty.
  • a material containing a fibrosis-inducing agent (alone or in combination with polymeric carrier, which may be in the form of, e.g., a gel, paste, or spray) is injected into a vertebral compression fracture can be used to promote the growth of endogenous scar tissue to fill the vertebral body defect, thus more closely mimicking normal tissue dynamics and reducing the incidence of adjacent vertebral fractures.
  • the injectable composition containing a fibrosis-inducing agent can further contain an agent that promotes bone growth (e.g., bone morphogenic proteins, growth factors, etc.).
  • an agent that promotes bone growth e.g., bone morphogenic proteins, growth factors, etc.
  • Suitable agents and methods for use in combination with a fibrosis-inducing agent include, but are not limited to, the use of a needle coated with ECHO—COAT or the addition of contrast agents (e.g., barium, tantalum, technitium, gadolinium) for localization by x-ray or MRI.
  • contrast agents e.g., barium, tantalum, technitium, gadolinium
  • the injectable material may also contain a polymer system that can provide sustained release of the fibrosis-inducing agent (with or without a concominant bone morphogenic protein, and/or osteogenic growth factor) to enhance efficacy and reduce the need for repeat administrations of active agents.
  • Preferred polymeric carriers for delivery of a injectable fibrosis-inducing agent (with or without a bone morphogenic protein, and/or growth factor that promotes bone growth) for the treatment of vertebral compression fractures are degradable materials which, after providing initial tissue support, are gradually replaced by the body's own scar tissue.
  • Suitable degradable materials for use in this embodiment include, but are not limited to, resorbable ceramics composed of ⁇ -tricalcium phosphate (e.g., VITOSS and PROOSTEON 500R), hydroxyapatite or Ca 10 (PO 4 ) 6 OH (e.g., BIOOSS and OSTEOGRAF), calcium carbonate or CaCO 3 , calcium sulfate (e.g., OSTEOSET and ALLOMATRIX), calcium phosphate (e.g., CALCIBON or NORIAN SRS), crosslinked materials of PEG, gelatin, collagen, bone allografts (e.g., ALLOGRO, ORTHOBLAST, OPTEFORM, GRAFTON), mesenchymal stem cells, hyaluronic acid (such as RESTYLANE, HYLAFORM, PERLANE, SYNVISC, SEPRAFILM, SEPRACOAT), hyaluronic acid derivatives, polysaccharides, carbohydrates, fibrinogen
  • Injectable PEG-containing formulations such as COSEAL, FOCALSEAL, SPRAYGEL or DURASEAL loaded with a fibrosis-inducing agent, bone morphogenic protein, and/or growth factor can also be used for injection into a vertebral compression fracture. Loading these materials with a fibrosis-inducing agent (with or without a bone morphogenic protein, and/or growth factor that promotes bone growth) can produce an injectable material that can provide initial support and symptomatic relief, but degrade with time as the body's own scar tissue grows in to repair the defect.
  • One injectable material that is of particular interest for injection into vertebral compression fractures is prepared from a 4-armed thiol PEG (10K), a 4-armed NHS PEG(10K) and methylated collagen such as described above.
  • the injectable material also contains a biologically active fibrosis-inducing agent (with or without a bone morphogenic protein, and/or growth factor that promotes bone growth).
  • the injectable material is loaded with a fibrosis-inducing agent is injected into a vertebral compression fracture to provide stability and symptomatic relief, form a scaffold that supports fibrous and bony ingrowth, deliver active agents that can promote repair, and degrade once tissue repair is complete.
  • the injectable material contains biologically active agents capable of inducing bone growth such bone morphogenic proteins and growth factors (transforming growth factor, platelet-derived growth factor, fibroblast growth factor) to promote bony ankylosis and fusion of adjacent vertebra.
  • biologically active agents capable of inducing bone growth
  • bone morphogenic proteins and growth factors transforming growth factor, platelet-derived growth factor, fibroblast growth factor
  • the injectable material may contain a fibrosis-inducing agent as well as a bone morphogenic protein and/or growth factors that promote bone growth.
  • a bone cement to deliver the fibrosis-inducing agent to a vertebral compression fracture.
  • Suitable non-degradable materials include crosslinked compositions that comprise PVA, PVP, polyacrylamide, methyl methacrylate (MMA) and methyl methacrylate styrene (MMA-styrene) which when mixed together form polymethyl methacrylate (PMMA) or bone cement (e.g., SIMPLEX P, ZIMMER REGULAR and ZIMMER LOW VISCOSITY CEMENT, PALACOS, CMW-1, CMW-2 or ENDURANCE).
  • synthetic cancellous bone void fillers e.g., CORTOSS), PHEMA, poly(vinyl PEG), poly(styrene sulfonate), poly(acrylic acid), poly(methacrylic acid), as well as other polymers that are known to form hydrogels.
  • Surgical adhesives containing cyanoacrylates such as DERMABOND, INDERMIL, GLUSTITCH, TISSUEMEND, VETBOND, HISTOACRYL BLUE and ORABASE SOOTHE-N-SEAL LIQUID PROTECTANT loaded with a fibrosis-inducing agent, bone morphogenic protein, and/or growth factor are also suitable for injection into vertebral compression fracture.
  • compositions include blends and copolymers of the agents listed above.
  • the material is loaded with a fibrosis-inducing agent (with or without a bone morphogenic protein, and/or growth factor that promotes bone growth) and injected into a vertebral compression fracture (as part of vertebroplasty or kyphoplasty) to stabilize the fracture and encourage the ingrowth of tissue.
  • a fibrosis-inducing agent with or without a bone morphogenic protein, and/or growth factor that promotes bone growth
  • a vertebral compression fracture as part of vertebroplasty or kyphoplasty
  • All of the injectable materials described above can be further modified to be comprised of, or contain, polymeric threads.
  • Polymeric threads have the ability to induce a fibroproliferative response from the surrounding tissue.
  • These polymer threads can be degradable or non-degradable.
  • Degradable threads can be composed of degradable polyesters, polyanhydrides, polyorthoesters, polyphosphoesters, polyphosphazines, cyanoacrylate polymers, collagen, chitosan, hyaluronic acid, chromic cat gut, alginates, starch, cellulose, cellulose esters, blends and copolymers thereof, as well as other known degradable polymers.
  • Non-degradable polymers that can be used include, but are not limited to, polyesters (e.g., PET), polyurethanes, silicones, PE, PP, PS, PM, PMA, silk, blends, copolymers thereof as well as other known polymers.
  • the threads used can be composed of a single composition or composed of a blend of differing compositions.
  • the polymeric threads themselves can be further modified through the addition of a polymeric coating applied to the threads.
  • the polymer used for coating the thread can be similar to that described above for the threads themselves.
  • the polymer coating may further comprise a biologically active agent that has the ability to induce a fibroproliferative or osteogenic response.
  • the fibrosis-inducing agents that can be used are further described in the section (vi) below.
  • the injectable materials described above can be utilized to deliver a particulate material that has the ability to induce fibrosis in an intervertebral fracture.
  • These particles can be either degradable or non-degradable and are similar to those described above for threads.
  • Microparticulate silk and/or silk strands (linear, branched, and/or coiled) either alone, or loaded with an additional fibrosis-inducing agent, bone morphogenic protein, and/or growth factor are also useful for directed injection into a vertebral compression fracture.
  • Additional particulate materials useful for the practice of this embodiment include talc, starch, glass, silicates, silica, calcium phosphate, calcium sulfate, calcium carbonate, hydroxyapatite, synthetic mineral (e.g., VITOSS and CORTOSS), PMMA, silver nitrate, ceramic particles and other inorganic particles known in the art to induce a fibroproliferative response followed by mineralization.
  • the particles used in this embodiment can be all of the same composition or a blend of differing compositions. These particles can also be used as a coating applied to the polymeric strands as described above.
  • the injectable materials can also be constructed such that it is comprised of both polymeric threads and particles.
  • the threads and particles used are similar to those described above and may be of uniform composition or blended composition. Virtually any combination of threads of differing compositions and particles of differing compositions can be utilized in this embodiment.
  • the hydrogels, the polymeric threads, and the particles can all be utilized to deliver one or more biologically active agents, as described below.
  • compositions comprising threads and/or particles is prepared from 4-armed thiol PEG (10K), 4-armed NHS PEG(10K) and methylated collagen such as described above and contains powdered silk particles (or silk threads) and/or mineral particles added to the composition prior to curing. Once deployed, the composition can absorb water, fill the fracture space and adhere to adjacent bone. This expansion can stabilize the fracture and restore vertebral height, while the powdered silk and/or mineral particles can initiate an ankylosing response. As the 4-armed thiol PEG (10K), 4-armed NHS PEG(10K) and methylated collagen composition starts to degrade, the material can support the bone tissue ingrowth that is initiated and potentiated by the particles.
  • Bone morphogenic proteins and/or growth factors are also useful for inclusion in this composition.
  • the amino PEG can provide a gel that can take a longer time to degrade and can provide some positive charge to further attract cellular material.
  • a second specific embodiment consists of an injectable implant composed of silk fibers or a polymerized version of the fibrosing agent itself (i.e., repeating units of the fibrosing agent polymerized together). Bone morphogenic proteins and/or growth factors (described previously and below) may also be added to this composition.
  • fibrosis-inducing agents for use in spinal prostheses (e.g., devices and bulking agents) include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, and CTGF, as well as analogues and derivatives of the aforementioned.
  • the device may additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone) and/or a bone morphogenic protein (BMP) (e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, or BMP-7 or an analogue or derivative thereof).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone
  • BMP bone morphogenic protein
  • the device may alone or additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • Surgical spinal fusion can be accomplished using a variety of procedures, implants and devices.
  • the vertebral canal is exposed through open surgery (either anteriorly and/or posteriorly) and all or parts of the damaged disc are removed sufficient to allow decompression of the affected cord or nerve roots.
  • Bone grafts autografts or allografts
  • bone substitutes are used to promote vertebral fusion, while the fixation devices serve to immobilize the region until bony fixation takes place.
  • implants and devices designed to splint the segments during the healing process include: fusion devices (including fusion baskets, fusion cage apparatus, interbody cages, interbody implants, fusion cage anchoring devices, fusion stabilization chamber, fusion cage anchoring plates), bone fixation devices (including anchoring bone plates, bone screws, and other fixation hardware) and tissue fillers/implants (including bone cement, allograft material, autograft material, collagen, and other biocompatible tissue fillers). All of these implants are suitable for coating with, or delivery of, a fibrosis-inducing agent(s) to promote healing and accelerate fusion of the vertebral bodies.
  • fusion devices including fusion baskets, fusion cage apparatus, interbody cages, interbody implants, fusion cage anchoring devices, fusion stabilization chamber, fusion cage anchoring plates
  • bone fixation devices including anchoring bone plates, bone screws, and other fixation hardware
  • tissue fillers/implants including bone cement, allograft material, autograft material, collagen, and other biocompatible tissue fillers. All
  • Spinal fusion cages are interbody devices that fit within the intervertebral space and/or the anterior region of the vertebral column. Fusion cages have various shapes including rectangular or cylindrical and a plurality of openings and helical threading. Fusion cages are often composed of an outer body and a hollow cavity that may or may not be used to insert bone growth-promoting material for stimulating bone fusion.
  • the prosthesis may be an interbody fusion cage that has an externally threaded stem projecting from a domed outer end which is fixed using an assembly of a plate, a fastener and bone screws. See e.g., U.S. Pat. No. 6,156,037.
  • the prosthesis may be a fusion cage with a threaded outer surface adapted for promoting fusion with bone structures when a bone-growth-inducing substance is packed into the cage body. See e.g., U.S. Pat. Nos. 4,961,740; 5,015,247; 4,878,915; and 4,501,269.
  • the prosthesis may be a generally tubular shell with a helical thread projecting with a plurality of pillars with holes to facilitate bone ingrowth and mechanical anchoring (see e.g., U.S. Pat. Nos. 6,071,310 and 5,489,308) or it may be biologically active and serve to promote fusion with the adjacent vertebral bone plates (see e.g., U.S. Pat. Nos. 5,489,308 and 6,520,993).
  • Other U.S. patents that describe threaded spinal implants include U.S. Pat. Nos. 5,263,953; 5,458,638; and 5,026,373.
  • the prosthesis may be a bone fixation device designed to promote vertebral fusion in order to limit movement between adjacent vertebrae.
  • a bone fixation device designed to promote vertebral fusion in order to limit movement between adjacent vertebrae.
  • bone dowels, rods, hooks, wires, wedges, plates, screws and other components may be used to fix the vertebral segments into place.
  • the fixation device may fit within the intervertebral space or it may encompass both the intervertebral space and the anterior region of the vertebral column or it may only encompass the anterior region of the vertebral column.
  • a bone fixation device may be used with a fusion cage to assist in stabilizing the device within the intervertebral area.
  • the prosthesis may be in the form of a solid annular body having a plurality of discrete bone-engaging teeth protruding on the superior and inferior surfaces and having a central opening that may be filled with a bone growth-promoting material.
  • the prosthesis may have a disk-like body with weld-like raised parts disposed on opposite surfaces to enhance lateral stability in situ. See e.g., U.S. Pat. No. 4,917,704.
  • the prosthesis may be composed of opposite end pieces that maintain the height of the intervertebral space with an integral central element that is smaller in diameter wherein osteogenic material is disposed within the annular pocket between the end pieces.
  • the prosthesis may be composed of first and second side surfaces extending parallel to each other with upper and lower surfaces that engage the adjacent vertebrae. See e.g., U.S. Pat. No. 5,716,415.
  • the prosthesis may be a fusion stabilization chamber composed of a hollow intervertebral spacer and an end portion with at least one hole for affixing into the surrounding bone. See e.g., U.S. Pat. No. 6,066,175.
  • the prosthesis may be composed of a metallic body tapering conically from the ventral to the dorsal end and having a plurality of fishplates extending from opposite sides with openings for bone screws.
  • the prosthesis may be composed of a pair of plates which may have protrusions for engaging the adjacent vertebrae and an alignment device disposed between the engaging plates for separating the plates to maintain them in lordotic alignment. See e.g., U.S. Pat. No. 6,576,016.
  • the prosthesis may be a plurality of implants that are inserted side by side into the disc space to promote bone fusion across an intervertebral space. See e.g., U.S. Pat. No. 5,522,899.
  • the prosthesis may be an anchoring device composed of an anchoring plate with a central portion configured for attachment to a vertebral implant (e.g., fusion cage) and the end portions adapted to fasten in a fixed manner to a bony segment of the vertebra. See e.g., U.S. Pat. No. 6,306,170.
  • the prosthesis may be a bone fixation apparatus composed of a bone plate and a fastener apparatus (e.g., bone screws). See e.g., U.S. Pat. Nos. 6,342,055; 6,454,769; 6,602,257; and 6,620,163.
  • Spinal prostheses which may be combined with one or more fibrosis-inducing agents according to the present invention, include commercially available products. Examples include: the INTERFIX Threaded Fusion Device (by Medtronic Sofamor Danek, Memphis, Term.), the BAK/C Cervical Interbody Fusion System and the CERVI-LOK Cervical Fixation System (by Centerpulse SPINE-TECH, Minneapolis, Minn.), the SC-ACUFIX Anterior Cervical Plate System (by Spinal Concepts, Austin, Tex.), the ACROFLE TDR prostheses and the CHARITE Artificial Disc (by DePuy Spine, Inc., Raynham, Mass.), the PRODISC system and PRODISC Cervical-C IDE disc replacement (by Synthes-Stratec, Switzerland) and the PROSTHETIC DISC NUCLEUS (by Raymedica, Inc., Minneapolis, Minn.).
  • the INTERFIX Threaded Fusion Device by Medtronic Sofamor Danek, Memphis,
  • the present invention provides spinal fusion devices (including fusion baskets, fusion cage apparatus, interbody cages, interbody implants, fusion cage anchoring devices, fusion stabilization chamber, fusion cage anchoring plates; bone fixation devices including anchoring bone plates, bone screws, and other fixation hardware; and tissue fillers/implants including bone cement, allograft material, autograft material, collagen, and other biocompatible tissue fillers) that include a fibrosis-inducing agent or a composition that includes a fibrosis-inducing agent to promote scarring and fixation of the device into the surrounding bone.
  • spinal fusion devices including fusion baskets, fusion cage apparatus, interbody cages, interbody implants, fusion cage anchoring devices, fusion stabilization chamber, fusion cage anchoring plates; bone fixation devices including anchoring bone plates, bone screws, and other fixation hardware; and tissue fillers/implants including bone cement, allograft material, autograft material, collagen, and other biocompatible tissue fillers
  • a spinal fusion device is coated with a fibrosing agent or a composition that includes the fibrosing agent to enhance healing.
  • the fibrosing agent may be incorporated into the glue/cement that holds the spinal fusion device in place.
  • the spinal fusion device is covered (all or in part) with a silk mesh or lattice to encourage scarring and anchoring into the surrounding bone.
  • a silk mesh or lattice can be coated onto all or a portion of the surface of fusion cage or other bone fixation hardware to encourage scarring and anchoring into the surrounding bone.
  • Methods for incorporating fibrosing compositions onto or into the spinal fusion devices include: (a) directly affixing to the device a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier); (b) directly incorporating into the device a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier); (c) by coating the device with a substance such as a hydrogel which can in turn absorb the fibrosing composition; (d) by interweaving a fibrosing composition (for example a silk strand or another polymeric thread which releases a fibrosis-inducing agent) into the device structure; (e) by inserting the device into a sleeve or mesh which is comprised of, or coated with,
  • the coating process can be performed in such a manner as to (a) coat the surfaces of the device that is in contact with the bone, (b) coat the surfaces of the device that are not in contact with the bone or (c) coat all or parts of both the bone-contacting and non-bone contacting surfaces of the device.
  • the fibrosis-inducing agent can be mixed with the materials that are used in the construction of the device such that the fibrosing agent is incorporated into the final device.
  • fibrosing agents for use in spinal fusion devices include fusion baskets, fusion cage apparatus, interbody cages, interbody implants, fusion cage anchoring devices, fusion stabilization chamber, fusion cage anchoring plates; bone fixation devices including anchoring bone plates, bone screws, and other fixation hardware; and tissue fillers/implants including bone cement, allograft material, autograft material, collagen, and other biocompatible tissue fillers) include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, and CTGF, as well as analogues and derivatives of the aforementioned.
  • the device may additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone) and/or a bone morphogenic protein (BMP) (e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, or BMP-7 or an analogue or derivative thereof).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone
  • BMP bone morphogenic protein
  • the device may alone or additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • the damaged vertebral segment may be treated using a intervertebral disc prosthesis that maintains vertebral anatomy and movement within the vertebral joint. This is often conducted when damage to more than one vertebral segment occurs.
  • intervertebral disc prostheses or “artificial disc” refers to implants and/or devices that are located in, on, or near the spine and which enhance the ability of the spine to perform its function in the patient.
  • intervertebral disc prostheses include, without limitation, artificial spinal discs and related devices including vertebral implants, vertebral disc prostheses, lumbar disc implants, cervical disc implants, implantable intervertebral prostheses, spinal prostheses, artificial discs, prosthetic implants, prosthetic spinal discs, spinal disc endoprostheses, spinal implants, artificial spinal discs, intervertebral implants, implantable spinal grafts, artificial lumbar discs, spinal nucleus implants, and intervertebral disc spacers.
  • artificial spinal discs and related devices including vertebral implants, vertebral disc prostheses, lumbar disc implants, cervical disc implants, implantable intervertebral prostheses, spinal prostheses, artificial discs, prosthetic implants, prosthetic spinal discs, spinal disc endoprostheses, spinal implants, artificial spinal discs, intervertebral implants, implantable spinal grafts, artificial lumbar discs, spinal nucleus implants, and intervertebral disc spacers.
  • An artificial disc suitable for combining with a fibrosis-inducing agent according to the present invention may be composed of a single material or several materials including, without limitation, allograft bone material (see e.g., U.S. Pat. No. 6,143,033), metals (see e.g., U.S. Pat. No. 4,955,908), and/or synthetic materials (see e.g., U.S. Pat. Nos. 6,264,695; 6,419,706; 5,824,093; and 4,911,718).
  • the prosthesis must be biocompatible and may consist of biodegradable or non-biodegradable components depending on the intended function of the device. See e.g., U.S. Pat. No.
  • the intervertebral disc prosthesis may be biologically inert and serve as a mechanical means of stabilizing the vertebral column (see e.g., U.S. Pat. Nos. 4,955,908 and 5,716,415) or as a means of preserving spinal function.
  • the prosthesis may be an alternative to spinal fusion.
  • the prosthesis may be a disc designed to provide normal movement between vertebral bone plates.
  • the artificial disc may be intended to mimic the natural shock absorbent function of the natural disc.
  • the artificial disc may be composed of a center core and end elements that support the disc against the adjacent vertebra or it may be intended to replace only a portion of the natural intervertebral disc (e.g., nucleus pulposus).
  • the artificial disc may be in the form of an elastomeric section sandwiched between two rigid plates. See e.g., U.S. Pat. Nos. 6,162,252; 5,534,030; 5,017,437; and 5,031,437.
  • the intervertebral disc prosthesis may be an elongated prosthetic disc nucleus composed of a hydrogel core and a constraining flexible jacket that allows the core to deform and reform. See e.g., U.S. Pat. No. 5,824,093.
  • the artificial disc may be composed of a rigid superior and inferior concaval-convex elements and a nuclear body which is located between the concave surfaces to permit movement. See e.g., U.S. Pat. No.
  • the artificial disc may be a partial spinal prosthesis composed of a core made of an elastic material such as silicone polymer or an elastomer which is covered by a casing made of a rigid material which is in contact with the adjacent vertebrae. See e.g., U.S. Pat. No. 6,419,706.
  • the intervertebral disc prosthesis may replace only the nucleus pulposus tissue by using a spinal nucleus implant comprised of a swellable, biomimetic plastic with a hydrophobic and hydrophilic phase which can be expanded in situ to conform to the natural size and shape. See e.g., U.S. Pat. No. 6,264,695.
  • the artificial disc may be composed of a central core formed from a biocompatible elastomer wrapped by multi-layered laminae made from elastomer and fibers. See e.g., U.S. Pat. No. 4,911,718.
  • the intervertebral disc prosthesis may be composed of a fluid-filled inner bladder with an outer layer of strong, inert fibers intermingled with a bioresorbable material which promotes tissue ingrowth. See e.g., U.S. Pat. No. 4,772,287.
  • the present invention provides intervertebral disc prostheses that include a fibrosis-inducing agent or a composition that includes a fibrosis-inducing agent to promote scarring and fixation of the device into the surrounding bone and yet retain the flexibility of the natural disc.
  • an artificial disc is coated with a fibrosis-inducing agent (or a composition that includes a fibrosis-inducing agent) to enhance healing and the formation of fibrous tissue similar to the annulus fibrosis.
  • the fibrosing agent may be incorporated into the glue/cement that holds the artificial disc in place.
  • the intervertebral disc prosthesis is covered (all or in part) with a silk mesh or lattice to encourage scarring and anchoring of the implant into the surrounding bone.
  • Methods for incorporating fibrosing compositions onto or into intervertebral disc prostheses include: (a) directly affixing to the device a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier); (b) directly incorporating into the device a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier); (c) by coating the device with a substance such as a hydrogel which can in turn absorb the fibrosing composition; (d) by interweaving a fibrosing composition (for example a silk strand or another polymeric thread which releases a fibrosis-inducing agent) into the device structure; (e) by inserting the device into a sleeve or mesh which is comprised of, or coated with
  • the coating process can be performed in such a manner as to (a) coat the surfaces of the device that is in contact with the vertebral bone, (b) coat the surfaces of the device that are not in contact with the bone or (c) coat all or parts of both the bone-contacting and non-bone contacting surfaces of the device.
  • the fibrosing agent can be mixed with the materials that are used to make the device such that the fibrosing agent is incorporated into the final prosthetic intervertebral disc.
  • the therapeutic agent can be incorporated directly into the formulation (for example, direct incorporation of the fibrosis-inducing agent into the swellable, biomimetic polymers used to create an artificial nucleus pulposus tissue that expands in situ to conform to the natural size and shape of the intervertebral disc core).
  • the fibrosis-inducing agent can be incorporated into a secondary carrier (e.g., micelles, liposomes, emulsions, microspheres, nanospheres etc, as described above) that are then used in the construction of, or as constituents of, an artificial disc.
  • fibrosis-inducing agents for use in spinal prostheses (e.g., devices and bulking agents) include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, and CTGF, as well as analogues and derivatives of the aforementioned.
  • the device may additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone) and/or a bone hormone) and/or a bone morphogenic protein (BMP) (e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, or BMP-7 or an analogue or derivative thereof).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone
  • BMP bone morphogenic protein
  • the device may alone or additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • the exact dose administered can vary with the amount injected or with the device size, surface area and design. However, certain principles can be applied in the application of this art. Drug dose can be calculated as a function of dose per unit area (of the portion of the device being coated), total drug dose administered can be measured, and appropriate surface concentrations of active drug can be determined. Regardless of the method of application of the drug to the spinal prostheses, the exemplary fibrosing agents, used alone or in combination, should be administered under the following dosing guidelines:
  • the total dose of talc delivered from a spinal prosthesis, or coated onto the surface of a spinal prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of talc released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of talc as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • talc should be applied to a spinal prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • talc is released from the surface of a spinal prosthesis or from composition (e.g., a bulking agent) such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • Drug concentrations in a bulking agent or other such material should be within the range described above except values are in mm 3 .
  • talc may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of talc (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as talc is administered at half the above parameters, a compound half as potent as talc is administered at twice the above parameters, etc.).
  • the total dose of silk delivered from a spinal prosthesis, or coated onto the surface of a spinal prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of silk released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of silk as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • silk should be applied to a spinal prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release silk at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the spinal prosthesis such that a minimum concentration of 0.01 nM to 1000 ⁇ M of silk is delivered to the tissue.
  • silk is released from the surface of a spinal prosthesis or from an injectable composition (e.g., a bulking agent) such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • silk may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of silk (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as silk is administered at half the above parameters, a compound half as potent as silk is administered at twice the above parameters, etc.).
  • the total dose of chitosan delivered from a spinal prosthesis, or coated onto the surface of a spinal prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of chitosan released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of chitosan as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • chitosan should be applied to a spinal prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • chitosan is released from the surface of a spinal prosthesis or from an injectable composition (e.g., a bulking agent) such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • a composition e.g., a bulking agent
  • chitosan may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of chitosan (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as chitosan is administered at half the above parameters, a compound half as potent as chitosan is administered at twice the above parameters, etc.).
  • the total dose of polylysine delivered from a spinal prosthesis, or coated onto the surface of a spinal prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of polylysine released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of polylysine as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • the dose per unit area of the device should fall within the range of 0.05 ⁇ g-10 ⁇ g per mm 2 of surface area coated.
  • polylysine should be applied to a spinal prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • polylysine As specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release polylysine at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the spinal prosthesis such that a minimum concentration of 0.01 nM to 1000 ⁇ M of polylysine is delivered to the tissue.
  • polylysine is released from the surface of a spinal prosthesis or from a composition (e.g., a bulking agent) such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • polylysine may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of polylysine with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as polylysine is administered at half the above parameters, a compound half as potent as polylysine is administered at twice the above parameters, etc.).
  • the total dose of fibronectin delivered from a spinal prosthesis, or coated onto the surface of a spinal prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of fibronectin released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of fibronectin as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • talc should be applied to a spinal prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • fibronectin is released from the surface of a spinal prosthesis or from a composition (e.g., a bulking agent) such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • a composition e.g., a bulking agent
  • fibronectin may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of fibronectin (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as fibronectin is administered at half the above parameters, a compound half as potent as fibronectin is administered at twice the above parameters, etc.).
  • the total dose of bleomycin delivered from a spinal prosthesis, or coated onto the surface of a spinal prosthesis should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg). In one embodiment, the total amount of bleomycin released from the prosthesis should be in the range of 0.10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of bleomycin as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • bleomycin should be applied to a spinal prosthesis surface at a dose of 0.005 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • bleomycin is released from the surface of a spinal prosthesis or from a composition (e.g., a bulking agent) such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • a composition e.g., a bulking agent
  • bleomycin may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of bleomycin with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as bleomycin is administered at half the above parameters, a compound half as potent as bleomycin is administered at twice the above parameters, etc.).
  • the total dose of CTGF delivered from a spinal prosthesis, or coated onto the surface of a spinal prosthesis should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg). In one embodiment, the total amount of CTGF released from the prosthesis should be in the range of 0.10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of CTGF as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • CTGF should be applied to a spinal prosthesis surface at a dose of 0.005 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release CTGF at differing rates
  • the above dosing parameters should be utilized in combination with the release rate of the drug from the spinal prosthesis such that a minimum concentration of 0.001 nM to 1000 ⁇ M of CTGF is delivered to the tissue.
  • CTGF is released from the surface of a spinal prosthesis or from a composition (e.g., a bulking agent) such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • a composition e.g., a bulking agent
  • CTGF may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of CTGF (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as CTGF is administered at half the above parameters, a compound half as potent as CTGF is administered at twice the above parameters, etc.).
  • the device may additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone) and/or a bone morphogenic protein (BMP) (e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, or BMP-7 or an analogue or derivative thereof.
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone
  • BMP bone morphogenic protein
  • Bone morphogenic protein(s) are to be used in formulations at concentrations that range from 0.001 ⁇ g/ml to approximately 20 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • formulation type e.g., gel, liquid, solid, semi-solid
  • formulation chemistry e.g., gel, liquid, solid, semi-solid
  • duration of required application e.g., type of medical device interface and formulation volume and or surface area coverage required.
  • the bone morphogenic protein is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.001 ⁇ g to 500 mg); preferred 1 ⁇ g to 250 mg.
  • the dose is per unit area of 0.001 ⁇ g-1000 ⁇ g per mm 2 ; with a preferred dose of 0.01 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 9 -10 ⁇ 4 M of bone morphogenic protein is to be maintained on the device surface.
  • Inflammatory cytokines are to be used in formulations at concentrations that range from 0.0001 ⁇ g/ml to approximately 20 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • the inflammatory cytokine is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 100 mg); preferred 0.001 ⁇ g to 50 mg.
  • the dose is per unit area of 0.0001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 10 -10 ⁇ 4 g/ml of inflammatory cytokine is to be maintained on the device surface.
  • the device may alone or additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof. Doses used are those concentrations which are demonstrated to stimulate cell proliferation (see Example 16).
  • the proliferative agents are to be used in formulations at concentrations that range from 0.1 ng/ml to 25 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • formulation type e.g., gel, liquid, solid, semi-solid
  • formulation chemistry e.g., duration of required application
  • type of medical device interface e.g., aqueous containing formulation volume
  • formulation volume e.g., a coating thickness
  • the proliferative agent is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 200 mg); preferred 0.001 ⁇ g to 100 mg.
  • the dose is per unit area of 0.00001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.0001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 11 -10 ⁇ 6 M of proliferative agent is to be maintained on the device surface.
  • any of the previously described fibrosis inducing agents, or derivatives and analogues thereof, can be utilized to create variations of the above compositions without deviating from the spirit and scope of the invention. It should also be apparent that the agent can be utilized in a composition with or without polymer carrier and that altering the carrier does not deviate from the scope of this invention.
  • some aspects of the present invention are: a method comprising introducing into an intervertebral disc space of a patient in need thereof, a therapeutically effective amount of a fibrosing agent or a composition comprising a fibrosing agent, where the fibrosing agent induces a fibrotic response at the intervertebral disc space of the patient, thereby providing the patient with a beneficial result.
  • the beneficial result is the repair of a spinal disc; the beneficial result is fibrous ankylosis; the beneficial result is bony ankylosis; the agent promotes regeneration; the agent promotes angiogenesis; the agent promotes fibroblast migration; the agent promotes fibroblast proliferation; the agent promotes deposition of extracellular matrix (ECM); the agent promotes remodeling, i.e., the maturation and organization of fibrous tissue; the agent is an arterial vessel wall irritant; the fibrosing agent is or comprises silk; the fibrosing agent is or comprises silkworm silk; the fibrosing agent is or comprises spider silk; the fibrosing agent is or comprises recombinant silk; the fibrosing agent is or comprises raw silk; the fibrosing agent is or comprises hydrolyzed silk; the fibrosing agent is or comprises acid-treated silk; the fibrosing agent is or comprises acylated silk; the fibrosing agent is in the form of
  • joint implants refer to implants that are designed to replace joints that have been physically impaired or damaged.
  • joint implants include, without limitation, orthopedic implants, orthopedic prostheses, modular implants, prosthetic joints, modular prostheses, joint prostheses, partial prostheses, hip implants, knee implants, shoulder implants and digit implants.
  • Other types of orthopedic implants that may be used in conjunction with joint implants include, e.g., hardware, such as internal and external fixation devices, pins, plates and screws.
  • the orthopedic implant is an internal fixation implant.
  • Internal fixation implants are medical devices that can be implanted (usually permanently) into a patient in minimally invasive orthopedic reconstructions and are often indicated for immobilization and stabilization of extremity fractures and unstable fractures.
  • intramedullary fixation devices such as intermedullary nails and plate and screw combinations; intramedullary rods, vertical transarticular pins for stabilization of severe ankle fractures, plates (e.g., plates made from titanium, stainless steel, and the like), plates with prongs to support subchondral bone, dorsal plates for volar applications, elastic plates, screws, clips, pins, staples, pegs, wires, sublaminar wires, and metal prostheses for holding vertebrae in place.
  • Open reduction internal fixation is a method of surgically repairing a fractured bone that typically involves either the use of plates and screws or an intramedullary (IM) rod to align and stabilize fractures.
  • IM rods can be inserted into the bone marrow canal in the center of the long bones of the extremities (e.g., femur or tibia).
  • the orthopedic implant is a component (e.g., a pin, wire, stopper, or dowel) of an external fixation device or an implanted portion (i.e., a portion that is situated within the body of the patient) of an external fixation device (also referred to herein as an “external fixation implant”).
  • External fixation devices are medical devices that can be used to immobilize bones to allow a fracture to heal.
  • External fixation devices are used in a variety of minimally invasive orthopedic surgeries as an alternative to other types of fixation devices, such as casts and internal fixation devices.
  • external fixation may be accomplished by placing pins or screws into the bone on both sides of the fracture. The pins are then secured together outside the skin with clamps and rods which can form an external frame.
  • An external fixation device typically includes a scaffold or frame that has attached to it wires, pins, and the like which is placed outside of an extremity, such as a limb. The device remains in place until healing has occurred, at which point it is then removed, leaving no foreign material in the extremity.
  • External fixation devices may take a variety of forms and may have monolateral, multiplanar or hybrid constructions.
  • a monolateral fixation device includes a bar or rail with attached pins that transfix a bone (e.g., a femur).
  • a multiplanar external fixation device can include rings or sections of rings, with attached pins and/or wires, which are used to secure fixation of a bone.
  • a hybrid system can include a frame consisting of both rings (multiplanar) and bars (monolateral).
  • External fixation devices also may be classified by their function, for example, the device may be stationary or moving. Stationary devices may be used for alignment of the bony fragments (e.g., for acute stabilization of fractures) and remain in place from the time of application to removal. Moving fixation devices, in contrast, may be used in gradual reduction of acute extremity fractures. The configuration of a moving fixation device can change over time for gradual correction.
  • External fixation devices may be used to treat a variety of conditions.
  • an external fixation device may be used for the fixation of injuries such as joint fractures.
  • External fixation can provide for acute or gradual fracture reduction.
  • external fixation devices may be used in the treatment of juxta-articular fractures, open fractures, and fractures with bone loss, including, for example, fractures near joints such as distal radius, proximal tibial plateau, and distal tibial pilon fractures.
  • Other applications of external fixation devices include reconstructive orthopedic procedures such as treatment of deformities, bone loss, contractures, treatment of non-unions (hypertrophic or atrophic), and limb length discrepancy.
  • a modular prosthesis is a prosthesis that has multiple (two or more) components, which can be assembled to form a unitary biomechanical structure.
  • Various features of the components can be adjusted by the surgeon prior to implantation of the prosthesis so as to accommodate the needs of each patient.
  • a modular prosthesis can have component that can be independently adjusted (rotationally and axially) by the surgeon, or the length of a component may be changed.
  • Modular prostheses can be used in a variety of surgical procedures.
  • the modular prosthesis may be an adjustable long bone prosthesis that can be adjusted within the patient to account for discrepancies in the measurement of a long bone to be replaced.
  • Prosthetic joints having modular components exist for replacement of the hip, knee, and ankle joints.
  • Other representative examples of modular orthopedic prostheses include a modular femoral stem, modular shoulder prosthesis, and modular elbow prostheses.
  • the long-term cause of failure for many artificial joints is loosening occurring over time between the implant and the surrounding bone that anchors the implant in place. Inadequate bone and tissue growth may lead to unsuccessful acute incorporation of the implant or late loosening may occur with time. In the case of the hip, for example, up to 5% of patients can suffer from joint loosening by 10 years post implant. Symptoms include pain that can become debilitating and ultimately lead to repeat surgery and possible revision of the implant.
  • the hip implant replaces the head of femur (i.e., ball) and/or the acetabulum (i.e., socket) of the joint.
  • the hip joint is replaced due to irreparable damage caused by non-inflammatory degenerative joint disease (e.g., osteoarthritis, post traumatic arthritis), inflammatory degenerative joint disease (e.g., rheumatoid arthritis, infectious arthritis), trauma (e.g., fracture of the pelvis or hip), congenital hip dysplasia, or joint dislocation and other fracture-induced damage to the femur and/or acetabulum.
  • non-inflammatory degenerative joint disease e.g., osteoarthritis, post traumatic arthritis
  • inflammatory degenerative joint disease e.g., rheumatoid arthritis, infectious arthritis
  • trauma e.g., fracture of the pelvis or hip
  • congenital hip dysplasia e.g., congenital hip dysplasia, or joint dislocation and other fracture-induced damage
  • Hip implants typically include two or three component systems, which include the femoral stem or shank, the femoral neck, and the spherical ball which adapts to the acetabulum or prosthetic acetabular cup.
  • the femoral stem, neck and ball, as well as the acetabular cup may be composed of metal (e.g., titanium, titanium alloy, cobalt-chromium or chromium-molybdenum) or polymer composite.
  • the hip implant may be cemented into the bone using bone cement (e.g., methylmethacrylate) or the hip implant may be fixed using a cementless surface treatment (e.g., porous coating, such as hydroxyapatite porous coating, or spongy coating) whereby the hip implant allows bony growth from the femur to anchor it into place.
  • bone cement e.g., methylmethacrylate
  • a cementless surface treatment e.g., porous coating, such as hydroxyapatite porous coating, or spongy coating
  • hip implants may be used to provide a full hip replacement.
  • the hip implant may be a three-modular designed total prosthesis with primary fixation, which may include a partially threaded elongated pin for insertion into the femoral body, which provides rotational adjustment between the body and the pin for various alignments and size combinations. See e.g., U.S. Pat. No. 4,938,773.
  • the hip implant may be composed of a ball, neck and fixation element with a bearing element that is adapted to restrain dislocations of the ball and provide a means for selecting the orientation of the fixation element. See e.g., U.S. Pat. No. 6,042,611.
  • the hip implant may be designed of two mutually articulating components composed of a cobalt chromium alloy with one having a low carbon content and the other component having a high carbon content. See e.g., U.S. Pat. No. 5,904,720.
  • hip implants may be adapted for cementing into place to ensure the implant is stabilized in the accurate position.
  • hip implants may be composed of cement spacers along the shaft which, upon implantation within the medullary canal of the femur, allows for optimal thickness of the cement mantle. See e.g., U.S. Pat. No. 5,314,489.
  • hip implants may be modular in which components may be adjusted to adapt to the host's shape or dimensions.
  • the hip implant may be a modular hip prosthesis composed of a plurality of removable, different size tubular sleeves that may be used to extend the femoral stem component or neck size which allows the implant to be custom fitted to a particular host. See e.g., U.S. Pat. No. 5,507,830.
  • hip implants may be designed to provide shock absorbency within the joint.
  • the hip implant may be composed of an elongate element that extends coaxially from the ball section that slidably extends into a chamber that contains a spring for shock absorbency. See e.g., U.S. Pat. No. 5,389,107.
  • the hip implant may be a modular shock absorbent prosthesis designed to have adjustable femoral stem, neck and ball, as well as adjustable tension due to its unique coupling modular spring mechanism. See e.g., U.S. Pat. No. 6,336,941.
  • hip implants may be composed of a composite material to provide greater stiffness or retention within the femur.
  • the hip implant may be composed of a plurality of layers of fibers (e.g., composed of carbon, ceramic, metal or fiberglass) in a matrix (e.g., a polymeric matrix) where the fibers may be substantially unidirectional in each respective layer. See e.g., U.S. Pat. Nos. 5,522,904, 5,163,962, 5,064,439 and 4,892,552.
  • the hip implant may have a stem composed of an inner metal core and an outer composite shell having fibers bonded with a thermoplastic resin and which the distal end is adapted to be inserted into a cavity formed in a bone.
  • the hip implant may be composed of an expandable material that absorbs body fluid and expands within an opening of the bone of the host's body such that a portion of the implant is retained within the bone and a portion of the implant is outside the bone. See e.g., U.S. Pat. No. 6,361,565.
  • hip implants may be only partial hip replacements.
  • the hip implant may be a prosthetic acetabular cup assembly being composed of a bearing component for receiving a ball attached to a femur and a shell component for attachment to an acetabulum. See e.g., U.S. Pat. No. 5,049,158.
  • Still other hip implants may be revision hip prostheses which have design features to augment the fixation of the implant into an area with bone-deficiency.
  • the hip implant may be a long stem hip joint prosthetic device having a long distal section of the femoral component which extends beyond the isthmus of the femur when implanted in the medullary canal and is designed with a specially curved distal section.
  • Hip implants which may be combined with one or more drugs according to the present invention, include numerous commercially available products, for example, the S—ROM Total Hip System and the AML Total Hip System from DePuy Orthopaedics, Inc. (Warsaw, Ind.).
  • the present invention provides hip prostheses that include a fibrosis-inducing agent or a composition that includes a fibrosis-inducing agent to promote scarring to provide fixation of the device into the surrounding bone.
  • the hip prosthesis is coated with a fibrosing agent or a composition that includes the fibrosing agent.
  • the fibrosing agent may be incorporated into a glue or cement that holds the prosthesis in place.
  • the hip prosthesis is covered (all or in part) with a silk mesh or lattice to encourage scarring and anchoring into the surrounding bone.
  • a silk mesh or lattice can be coated onto all or a portion of the surface of the implant stem to encourage scarring and anchoring into the surrounding bone.
  • compositions can further include one or more fibrosis-inducing agents to promote the formation of granulation tissue.
  • Methods for incorporating fibrosing compositions onto or into the orthopedic implants include: (a) directly affixing to the device a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier); (b) directly incorporating into the device a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier); (c) by coating the device with a substance such as a hydrogel which can in turn absorb the fibrosing composition; (d) by interweaving fibrosing composition coated thread (or the polymer itself formed into a thread) into the device structure; (e) by inserting the device into a sleeve or mesh which is comprised of or coated with a fibrosing composition
  • the coating process can be performed in such a manner as to a) coat the surfaces of the device that is in contact with the bone, b) coat the surfaces of the device that are not in contact with the bone or c) coat all or parts of both the bone-contacting and non-bone contacting surface of the device.
  • the fibrosing agent can be mixed with the materials that are used to make the device such that the fibrosing agent is incorporated into the final device.
  • fibrosing agents for use in hip prostheses implants include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, and CTGF, as well as analogues and derivatives of the aforementioned.
  • the exact dose administered can vary with device size, surface area and design. However, certain principles can be applied in the application of this art. Drug dose can be calculated as a function of dose per unit area (of the portion of the device being coated), total drug dose administered can be measured and appropriate surface concentrations of active drug can be determined. Regardless of the method of application of the drug to the hip prostheses, the exemplary fibrosing agents, used alone or in combination, should be administered under the following dosing guidelines:
  • the total dose of talc delivered from a hip prosthesis, or coated onto the surface of a hip prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of talc released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of talc as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • talc should be applied to a hip prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • talc is released from the surface of a hip prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months. For example, talc may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of talc (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as talc is administered at half the above parameters, a compound half as potent as talc is administered at twice the above parameters, etc.).
  • the total dose of silk delivered from a hip prosthesis, or coated onto the surface of a hip prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of silk released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of silk as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • silk should be applied to a hip prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release silk at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the hip prosthesis such that a minimum concentration of 0.01 nM to 1000 ⁇ M of silk is delivered to the tissue.
  • silk is released from the surface of a hip prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months. For example, silk may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of silk (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as silk is administered at half the above parameters, a compound half as potent as silk is administered at twice the above parameters, etc.).
  • the total dose of chitosan delivered from a hip prosthesis, or coated onto the surface of a hip prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of chitosan released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of chitosan as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • chitosan should be applied to a hip prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • chitosan is released from the surface of a hip prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • chitosan may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of chitosan (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as chitosan is administered at half the above parameters, a compound half as potent as chitosan is administered at twice the above parameters, etc.).
  • the total dose of polylysine delivered from a hip prosthesis, or coated onto the surface of a hip prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of polylysine released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of polylysine as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • the dose per unit area of the device should fall within the range of 0.05 ⁇ g-10 ⁇ g per mm 2 of surface area coated.
  • polylysine should be applied to a hip prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • polylysine As specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release polylysine at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the hip prosthesis such that a minimum concentration of 0.01 nM to 1000 ⁇ M of polylysine is delivered to the tissue.
  • polylysine is released from the surface of a hip prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • polylysine may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of polylysine with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as polylysine is administered at half the above parameters, a compound half as potent as polylysine is administered at twice the above parameters, etc.).
  • the total dose of fibronectin delivered from a hip prosthesis, or coated onto the surface of a hip prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of fibronectin released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of fibronectin as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • fibronectin should be applied to a hip prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • fibronectin is released from the surface of a hip prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • fibronectin may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of fibronectin (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as fibronectin is administered at half the above parameters, a compound half as potent as fibronectin is administered at twice the above parameters, etc.).
  • the total dose of bleomycin delivered from a hip prosthesis, or coated onto the surface of a hip prosthesis should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg). In one embodiment, the total amount of bleomycin released from the prosthesis should be in the range of 0.10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of bleomycin as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • bleomycin should be applied to a hip prosthesis surface at a dose of 0.005 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • bleomycin is released from the surface of a hip prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • bleomycin may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of bleomycin with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as bleomycin is administered at half the above parameters, a compound half as potent as bleomycin is administered at twice the above parameters, etc.).
  • the total dose of CTGF delivered from a hip prosthesis, or coated onto the surface of a hip prosthesis should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg). In one embodiment, the total amount of CTGF released from the prosthesis should be in the range of 0.10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of CTGF as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • CTGF should be applied to a hip prosthesis surface at a dose of 0.005 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release CTGF at differing rates
  • the above dosing parameters should be utilized in combination with the release rate of the drug from the hip prosthesis such that a minimum concentration of 0.001 nM to 1000 ⁇ M of CTGF is delivered to the tissue.
  • CTGF is released from the surface of a hip prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • CTGF may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of CTGF (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as CTGF is administered at half the above parameters, a compound half as potent as CTGF is administered at twice the above parameters, etc.).
  • the device may additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone) and/or a bone morphogenic protein (BMP) (e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, or BMP-7 or an analogue or derivative thereof).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone
  • BMP bone morphogenic protein
  • Bone morphogenic protein(s) are to be used in formulations at concentrations that range from 0.001 ⁇ g/ml to approximately 20 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • formulation type e.g., gel, liquid, solid, semi-solid
  • formulation chemistry e.g., gel, liquid, solid, semi-solid
  • duration of required application e.g., type of medical device interface and formulation volume and or surface area coverage required.
  • the bone morphogenic protein is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.001 ⁇ g to 500 mg); preferred 1 ⁇ g to 250 mg.
  • the dose is per unit area of 0.001 ⁇ g-1000 ⁇ g per; with a preferred dose of 0.01 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 9 -10 ⁇ 4 M of bone morphogenic protein is to be maintained on the device surface.
  • Inflammatory cytokines are to be used in formulations at concentrations that range from 0.0001 ⁇ g/ml to approximately 20 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • the inflammatory cytokine is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 100 mg); preferred 0.001 ⁇ g to 50 mg.
  • the dose is per unit area of 0.0001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 10 -10 ⁇ 4 g/ml of inflammatory cytokine is to be maintained on the device surface.
  • the device may alone or additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3, diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof. Doses used are those concentrations which are demonstrated to stimulate cell proliferation (see Example 16).
  • the proliferative agents are to be used in formulations at concentrations that range from 0.1 ng/ml to 25 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • formulation type e.g., gel, liquid, solid, semi-solid
  • formulation chemistry e.g., duration of required application
  • type of medical device interface e.g., aqueous containing formulation volume
  • formulation volume e.g., a coating thickness
  • the proliferative agent is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 200 mg); preferred 0.001 ⁇ g to 100 mg.
  • the dose is per unit area of 0.00001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.0001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 11 -10 ⁇ 6 M of proliferative agent is to be maintained on the device surface.
  • any of the previously described fibrosis inducing agents, or derivatives and analogues thereof, can be utilized to create variations of the above compositions without deviating from the spirit and scope of the invention. It should also be apparent that the agent can be utilized in a composition with or without polymer carrier and that altering the carrier does not deviate from the scope of this invention.
  • the present invention provides knee implants that induce fibrosis or adhesion of the implant into the surrounding tissue.
  • Knee replacement surgery is generally indicated for patients with severe knee pain and disability caused by damage to their articular cartilage as a result of rheumatoid arthritis, osteoarthritis or trauma. It is highly successful procedure in relieving pain and restoring joint function. Knee arthroplasty procedures are broadly categorized as primary or revision and are either unicompartmental (partial) or total. Knee prostheses (referred to herein as knee implants) can be used to replace all or a portion of the knee joint.
  • TKA total knee arthroplasty
  • the diseased cartilage surfaces of the thighbone (femur), the shinbone (tibia) and the kneecap (patella) are replaced by prostheses made of metal alloys (e.g., titanium- or cobalt/chromium-based alloys) and high-grade plastics and polymeric materials (e.g., ultrahigh-density polyethylene).
  • metal alloys e.g., titanium- or cobalt/chromium-based alloys
  • high-grade plastics and polymeric materials e.g., ultrahigh-density polyethylene
  • Most of the other structures of the knee, such as the connecting ligaments remain intact.
  • Up to three bone surfaces may be replaced during a TKA: the distal ends (condyles) of the femur, the proximal surface of the tibia and the posterior surface of the patella.
  • Components are designed so that metal always articulates against plastic, which provides smooth movement and results in minimal wear.
  • Knee joint implants typically have three components (i.e., a femoral, a tibial, and a patellar component).
  • the metal femoral component curves around the end of the thighbone and has an interior groove so the patella can move up and down smoothly against the bone as the knee bends and straightens.
  • one large piece is used to resurface the end of the bone. If only one condyle of the femur is damaged, a smaller piece may be used (unicompartmental knee replacement) to resurface just that part of the bone.
  • Some designs have an internal post with a circular-shaped device (cam) that works with a corresponding tibial component to help prevent the femur from sliding forward too far on the tibia when the knee is bent.
  • the tibial component is a flat metal platform with a polyethylene cushion.
  • the cushion may be part of the platform (fixed) or separate (mobile) with either a flat surface (PCL-retaining) or a raised, sloping surface (PCL-substituting).
  • the patellar component is a dome-shaped piece of polyethylene that duplicates the shape of the kneecap anchored to a flat metal plate.
  • Knee implants suitable for combining with one or more fibrosis-inducing agents according to the present invention include numerous commercially available products. These include, for example, the NEXGEN LEGACY Knee Posterior Stabilized (LPS) and NEXGEN LEGACY LPS Femoral Component from Zimmer.
  • LPS NEXGEN LEGACY Knee Posterior Stabilized
  • knee implants suitable for the delivery of fibrosis-inducing agents include Stryker Howmedica Osteonics DURACON Total Knee System, SCORPIO Knee System, and SCORPIO Cruciate Retaining Single Axis Knee; implants available from DePuy Orthopaedics such as the LCS Total Knee System, P.F.C. Sigma RP Platform Knee System, Keane Uni-Compartmental Knee System, P.F.C. Sigma Uni-Compartmental Knee System, AMK Total Knee System, P.F.C. Sigma Knee System (Cruciate-Retaining), the P.F.C.
  • the present invention provides knee prostheses that include a fibrosis-inducing agent or a composition that includes a fibrosis-inducing agent to promote scarring and fixation of the device into the surrounding bone.
  • the knee prosthesis is coated with a fibrosing agent or a composition that includes the fibrosing agent.
  • the fibrosing agent may be incorporated into the glue or cement that holds the prosthesis in place.
  • the knee prosthesis is covered (all or in part) with a silk mesh or lattice to encourage scarring and anchoring into the surrounding bone.
  • a silk mesh or lattice can be coated onto all or a portion of the surface of the implant stem to encourage scarring and anchoring into the surrounding bone.
  • compositions can further include one or more fibrosis-inducing agents to promote the formation of granulation tissue.
  • Methods for incorporating fibrosing compositions onto or into the orthopedic implants include: (a) directly affixing to the device a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier); (b) directly incorporating into the device a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier); (c) by coating the device with a substance such as a hydrogel which can in turn absorb the fibrosing composition; (d) by interweaving fibrosing composition coated thread (or the polymer itself formed into a thread) into the device structure; (e) by inserting the device into a sleeve or mesh which is comprised of or coated with a fibrosing composition
  • the coating process can be performed in such a manner as to a) coat the surfaces of the device that is in contact with the bone, b) coat the surfaces of the device that are not in contact with the bone or c) coat all or parts of both the bone-contacting and non-bone contacting surface of the device.
  • the fibrosing agent can be mixed with the materials that are used to make the device such that the fibrosing agent is incorporated into the final device.
  • fibrosing agents for use in knee prostheses include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, and CTGF, as well as analogues and derivatives of the aforementioned.
  • the exact dose administered can vary with device size, surface area and design. However, certain principles can be applied in the application of this art. Drug dose can be calculated as a function of dose per unit area (of the portion of the device being coated), total drug dose administered can be measured and appropriate surface concentrations of active drug can be determined. Regardless of the method of application of the drug to the knee prostheses, the exemplary fibrosing agents, used alone or in combination, should be administered under the following dosing guidelines:
  • the total dose of talc delivered from a knee prosthesis, or coated onto the surface of a knee prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of talc released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of talc as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • talc should be applied to a knee prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • talc is released from the surface of a knee prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months. For example, talc may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of talc (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as talc is administered at half the above parameters, a compound half as potent as talc is administered at twice the above parameters, etc.).
  • the total dose of silk delivered from a knee prosthesis, or coated onto the surface of a knee prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of silk released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of silk as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • silk should be applied to a knee prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release silk at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the knee prosthesis such that a minimum concentration of 0.01 nM to 1000 ⁇ M of silk is delivered to the tissue.
  • silk is released from the surface of a knee prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months. For example, silk may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of silk (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as silk is administered at half the above parameters, a compound half as potent as silk is administered at twice the above parameters, etc.).
  • the total dose of chitosan delivered from a knee prosthesis, or coated onto the surface of a knee prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of chitosan released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of chitosan as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • chitosan should be applied to a knee prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • chitosan is released from the surface of a knee prosthesis (e.g., a bulking agent) such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • a knee prosthesis e.g., a bulking agent
  • chitosan may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of chitosan (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as chitosan is administered at half the above parameters, a compound half as potent as chitosan is administered at twice the above parameters, etc.).
  • the total dose of polylysine delivered from a knee prosthesis, or coated onto the surface of a knee prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of polylysine released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of polylysine as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • the dose per unit area of the device should fall within the range of 0.05 ⁇ g-10 ⁇ g per mm 2 of surface area coated.
  • polylysine should be applied to a knee prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • polylysine As specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release polylysine at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the knee prosthesis such that a minimum concentration of 0.01 nM to 1000 ⁇ M of polylysine is delivered to the tissue.
  • polylysine is released from the surface of a knee prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • polylysine may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of polylysine with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as polylysine is administered at half the above parameters, a compound half as potent as polylysine is administered at twice the above parameters, etc.).
  • the total dose of fibronectin delivered from a knee prosthesis, or coated onto the surface of a knee prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of fibronectin released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of fibronectin as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • fibronectin should be applied to a knee prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • fibronectin is released from the surface of a knee prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • fibronectin may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of fibronectin (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as fibronectin is administered at half the above parameters, a compound half as potent as fibronectin is administered at twice the above parameters, etc.).
  • the total dose of bleomycin delivered from a knee prosthesis, or coated onto the surface of a knee prosthesis should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg). In one embodiment, the total amount of bleomycin released from the prosthesis should be in the range of 0.10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of bleomycin as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • bleomycin should be applied to a knee prosthesis surface at a dose of 0.005 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • bleomycin is released from the surface of a knee prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • bleomycin may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of bleomycin with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as bleomycin is administered at half the above parameters, a compound half as potent as bleomycin is administered at twice the above parameters, etc.).
  • the total dose of CTGF delivered from a knee prosthesis, or coated onto the surface of a knee prosthesis should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg). In one embodiment, the total amount of CTGF released from the prosthesis should be in the range of 0.10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of CTGF as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • CTGF should be applied to a knee prosthesis surface at a dose of 0.005 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release CTGF at differing rates
  • the above dosing parameters should be utilized in combination with the release rate of the drug from the knee prosthesis such that a minimum concentration of 0.001 nM to 1000 ⁇ M of CTGF is delivered to the tissue.
  • CTGF is released from the surface of a knee prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • CTGF may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of CTGF (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as CTGF is administered at half the above parameters, a compound half as potent as CTGF is administered at twice the above parameters, etc.).
  • the device may additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone) and/or a bone morphogenic protein (BMP) (e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, or BMP-7 or an analogue or derivative thereof).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone
  • BMP bone morphogenic protein
  • Bone morphogenic protein(s) are to be used in formulations at concentrations that range from 0.001 ⁇ g/ml to approximately 20 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • formulation type e.g., gel, liquid, solid, semi-solid
  • formulation chemistry e.g., gel, liquid, solid, semi-solid
  • duration of required application e.g., type of medical device interface and formulation volume and or surface area coverage required.
  • the bone morphogenic protein is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.001 ⁇ g to 500 mg); preferred 1 ⁇ g to 250 mg.
  • the dose is per unit area of 0.001 ⁇ g-1000 ⁇ g per mm 2 ; with a preferred dose of 0.01 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 9 -10 ⁇ 4 M of bone morphogenic protein is to be maintained on the device surface.
  • Inflammatory cytokines are to be used in formulations at concentrations that range from 0.0001 ⁇ g/ml to approximately 20 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • the inflammatory cytokine is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 100 mg); preferred 0.001 ⁇ g to 50 mg.
  • the dose is per unit area of 0.0001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 10 -10 ⁇ 4 g/ml of inflammatory cytokine is to be maintained on the device surface.
  • the device may alone or additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • Doses used are those concentrations which are demonstrated to stimulate cell proliferation (see, e.g., Example 16).
  • the proliferative agents are to be used in formulations at concentrations that range from 0.1 ng/ml to 25 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • formulation type e.g., gel, liquid, solid, semi-solid
  • formulation chemistry e.g., duration of required application
  • type of medical device interface e.g., aqueous containing formulation volume
  • formulation volume e.g., a coating thickness
  • the proliferative agent is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 200 mg); preferred 0.001 ⁇ g to 100 mg.
  • the dose is per unit area of 0.00001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.0001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 11 -10 ⁇ 6 M of proliferative agent is to be maintained on the device surface.
  • any of the previously described fibrosis inducing agents, or derivatives and analogues thereof, can be utilized to create variations of the above compositions without deviating from the spirit and scope of the invention. It should also be apparent that the agent can be utilized in a composition with or without polymer carrier and that altering the carrier does not deviate from the scope of this invention.
  • Shoulder joint reconstruction is typically indicated to alleviate pain and restore lost function arising from medical conditions such as fractures, osteoarthritis, rheumatoid arthritis, avascular necrosis, and tumor growth (benign or malignant).
  • Hemiarthroplasties partial shoulder implants
  • Total shoulder replacement implanting of both the humeral and glenoid components
  • Joint replacement in conjunction with excision of a tumor is fairly rare, occurring in less than one percent of patients who receive shoulder replacement surgeries. In a cancer patient, removal of bone may necessitate partial or total replacement of the joint.
  • shoulder prostheses have been described (see, e.g., U.S. Pat. Nos. 6,494,913; 6,193,758; 6,168,628; 6,102,953; 6,045,582; 5,961,555; 5,593,448; 5,549,682; and 5,108,440).
  • Shoulder implants suitable for combining with one or more fibrosis-inducing agents according to the present invention include numerous commercially available products.
  • shoulder implants manufactured by DePuy Orthopaedics (e.g., GLOBAL TX Total Shoulder System, GLOBAL Shoulder Eccentric Head, GLOBAL Total Shoulder System), Biomet (e.g., Bio-Modular, Bi-Angular/Bi-Polar, Proximal Humeral Replacement, and Integrated Shoulder System), Stryker Howmedica Osteonics (e.g., SOLAR Shoulder Bipolar Heads, Humeral Heads, Humeral Components, and Glenoid Components), Sulzer (e.g., Anatomical Shoulder and Select Shoulder), Zimmer (Bigliani/Flatow Shoulder), and Smith & Nephew Orthopaedics (e.g., COFIELD 2 Total Shoulder System, NEER II Total Shoulder System, and Modular Shoulder System).
  • DePuy Orthopaedics e.g., GLOBAL TX Total Shoulder System, GLOBAL Shoulder Eccentric Head,
  • the present invention provides shoulder prostheses that include a fibrosis-inducing agent or a composition that includes a fibrosis-inducing agent to promote scarring and fixation of the device into the surrounding bone.
  • the shoulder prosthesis is coated with a fibrosing agent or a composition that includes the fibrosing agent.
  • the fibrosing agent may be incorporated into the glue or cement that holds the prosthesis in place.
  • the shoulder prosthesis is covered (all or in part) with a silk mesh or lattice to encourage scarring and anchoring into the surrounding bone.
  • a silk mesh or lattice can be coated onto all or a portion of the surface of the implant stem to encourage scarring and anchoring into the surrounding bone.
  • compositions can further include one or more fibrosis-inducing agents to promote the formation of granulation tissue.
  • Methods for incorporating fibrosing compositions onto or into the orthopedic implants include: (a) directly affixing to the device a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier); (b) directly incorporating into the device a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier); (c) by coating the device with a substance such as a hydrogel which can in turn absorb the fibrosing composition; (d) by interweaving fibrosing composition coated thread (or the polymer itself formed into a thread) into the device structure; (e) by inserting the device into a sleeve or mesh which is comprised of or coated with a fibrosing composition
  • the coating process can be performed in such a manner as to a) coat the surfaces of the device that is in contact with the bone, b) coat the surfaces of the device that are not in contact with the bone or c) coat all or parts of both the bone-contacting and non-bone contacting surface of the device.
  • the fibrosing agent can be mixed with the materials that are used to make the device such that the fibrosing agent is incorporated into the final device.
  • fibrosing agents for use in shoulder prostheses include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, and CTGF, as well as analogues and derivatives of the aforementioned.
  • the exact dose administered can vary with device size, surface area and design. However, certain principles can be applied in the application of this art. Drug dose can be calculated as a function of dose per unit area (of the portion of the device being coated), total drug dose administered can be measured and appropriate surface concentrations of active drug can be determined. Regardless of the method of application of the drug to the shoulder prostheses, the exemplary fibrosing agents, used alone or in combination, should be administered under the following dosing guidelines:
  • the total dose of talc delivered from a shoulder prosthesis, or coated onto the surface of a shoulder prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of talc released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of talc as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • talc should be applied to a shoulder prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • talc is released from the surface of a shoulder prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months. For example, talc may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of talc (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as talc is administered at half the above parameters, a compound half as potent as talc is administered at twice the above parameters, etc.).
  • the total dose of silk delivered from a shoulder prosthesis, or coated onto the surface of a shoulder prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of silk released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of silk as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • silk should be applied to a shoulder prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release silk at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the shoulder prosthesis such that a minimum concentration of 0.01 nM to 1000 ⁇ M of silk is delivered to the tissue.
  • silk is released from the surface of a shoulder prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months. For example, silk may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of silk (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as silk is administered at half the above parameters, a compound half as potent as silk is administered at twice the above parameters, etc.).
  • the total dose of chitosan delivered from a shoulder prosthesis, or coated onto the surface of a shoulder prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of chitosan released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of chitosan as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • chitosan should be applied to a shoulder prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • chitosan is released from the surface of a shoulder prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • chitosan may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of chitosan (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as chitosan is administered at half the above parameters, a compound half as potent as chitosan is administered at twice the above parameters, etc.).
  • the total dose of polylysine delivered from a shoulder prosthesis, or coated onto the surface of a shoulder prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of polylysine released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of polylysine as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • the dose per unit area of the device should fall within the range of 0.05 ⁇ g-10 ⁇ g per mm 2 of surface area coated.
  • polylysine should be applied to a shoulder prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • polylysine As specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release polylysine at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the shoulder prosthesis such that a minimum concentration of 0.01 nM to 1000 ⁇ M of polylysine is delivered to the tissue.
  • polylysine is released from the surface of a shoulder prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • polylysine may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of polylysine with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as polylysine is administered at half the above parameters, a compound half as potent as polylysine is administered at twice the above parameters, etc.).
  • the total dose of fibronectin delivered from a shoulder prosthesis, or coated onto the surface of a shoulder prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of fibronectin released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of fibronectin as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • fibronectin should be applied to a shoulder prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • fibronectin is released from the surface of a shoulder prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • fibronectin may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of fibronectin (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as fibronectin is administered at half the above parameters, a compound half as potent as fibronectin is administered at twice the above parameters, etc.).
  • the total dose of bleomycin delivered from a shoulder prosthesis, or coated onto the surface of a shoulder prosthesis should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg). In one embodiment, the total amount of bleomycin released from the prosthesis should be in the range of 0.10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of bleomycin as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • bleomycin should be applied to a shoulder prosthesis surface at a dose of 0.005 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • bleomycin is released from the surface of a shoulder prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • bleomycin may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of bleomycin with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as bleomycin is administered at half the above parameters, a compound half as potent as bleomycin is administered at twice the above parameters, etc.).
  • the total dose of CTGF delivered from a shoulder prosthesis, or coated onto the surface of a shoulder prosthesis should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg). In one embodiment, the total amount of CTGF released from the prosthesis should be in the range of 0.10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of CTGF as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • CTGF should be applied to a shoulder prosthesis surface at a dose of 0.005 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release CTGF at differing rates
  • the above dosing parameters should be utilized in combination with the release rate of the drug from the shoulder prosthesis such that a minimum concentration of 0.001 nM to 1000 ⁇ M of CTGF is delivered to the tissue.
  • CTGF is released from the surface of a shoulder prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • CTGF may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of CTGF (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as CTGF is administered at half the above parameters, a compound half as potent as CTGF is administered at twice the above parameters, etc.).
  • the device may additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone) and/or a bone morphogenic protein (BMP) (e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, or BMP-7 or an analogue or derivative thereof).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone
  • BMP bone morphogenic protein
  • Bone morphogenic protein(s) are to be used in formulations at concentrations that range from 0.001 ⁇ g/ml to approximately 20 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • formulation type e.g., gel, liquid, solid, semi-solid
  • formulation chemistry e.g., gel, liquid, solid, semi-solid
  • duration of required application e.g., type of medical device interface and formulation volume and or surface area coverage required.
  • the bone morphogenic protein is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.001 ⁇ g to 500 mg); preferred 1 ⁇ g to 250 mg.
  • the dose is per unit area of 0.001 ⁇ g-1000 ⁇ g per mm 2 ; with a preferred dose of 0.01 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 9 -10 ⁇ 4 M of bone morphogenic protein is to be maintained on the device surface.
  • Inflammatory cytokines are to be used in formulations at concentrations that range from 0.0001 ⁇ g/ml to approximately 20 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • the inflammatory cytokine is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 100 mg); preferred 0.001 ⁇ g to 50 mg.
  • the dose is per unit area of 0.0001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 10 -10 ⁇ 4 g/ml of inflammatory cytokine is to be maintained on the device surface.
  • the device may alone or additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • Doses used are those concentrations which are demonstrated to stimulate cell proliferation (see, e.g., Example 16).
  • the proliferative agents are to be used in formulations at concentrations that range from 0.1 ng/ml to 25 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • formulation type e.g., gel, liquid, solid, semi-solid
  • formulation chemistry e.g., duration of required application
  • type of medical device interface e.g., aqueous containing formulation volume
  • formulation volume e.g., a coating thickness
  • the proliferative agent is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 200 mg); preferred 0.001 ⁇ g to 100 mg.
  • the dose is per unit area of 0.00001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.0001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 11 -10 ⁇ 6 M of proliferative agent is to be maintained on the device surface.
  • any of the previously described fibrosis inducing agents, or derivatives and analogues thereof, can be utilized to create variations of the above compositions without deviating from the spirit and scope of the invention. It should also be apparent that the agent can be utilized in a composition with or without polymer carrier and that altering the carrier does not deviate from the scope of this invention.
  • the tissue cavity into which the artificial joint is placed can be treated with a fibrosis-inducing agent prior to, during, or after the implantation of the prosthetic joint.
  • a fibrosis-inducing agent prior to, during, or after the implantation of the prosthetic joint.
  • This can be accomplished in several ways including: (a) topical application of the fibrosing agent into the anatomical space where the artificial joint can be placed (particularly useful for this embodiment is the use of polymeric carriers which release the fibrosing agent over a period ranging from several hours to several weeks—fluids, suspensions, emulsions, microemulsions, microspheres, pastes, gels, microparticulates, sprays, aerosols, solid implants and other formulations which release a fibrosing agent can be delivered into the region where the prosthetic joint can be inserted); (b) microparticulate silk and/or silk strands (linear, branched, and/or coiled) for directed delivery into the implantation site; (
  • This hydrogel may further contain collagen, methylated collagen and/or gelatin.
  • This hydrogel can further comprise the fibrosis-inducing agents described above (e.g., silk powder or silk threads).(m) films, sponges or meshes such as INTERCEED, VICRYL mesh, and GELFOAM loaded with a fibrosis-inducing agent applied to the implantation site (or the implant/device surface).
  • fibrosis-inducing agents for infiltration into the tissues surrounding a joint prosthesis include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, and CTGF, as well as analogues and derivatives of the aforementioned.
  • the exact dose administered into the tissue surrounding the implant can vary with device size, surface area and design. However, certain principles can be applied in the application of this art. Drug dose can be calculated as a function of dose per unit area (of the implanted portion of the device), total drug dose administered can be measured and appropriate surface concentrations of active drug can be determined. Regardless of the method of application of the drug, the exemplary fibrosing agents, used alone or in combination, should be administered under the following dosing guidelines:
  • the total dose of talc delivered should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of talc released from around the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of talc as a function of the surface area of the implanted portion of the device
  • talc is released such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • talc may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of talc (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as talc is administered at half the above parameters, a compound half as potent as talc is administered at twice the above parameters, etc.).
  • the total dose of silk delivered into the tissue surrounding a prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of silk released around the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of silk as a function of the surface area of the portion of the device which is implanted
  • the above dosing parameters should be utilized in combination with the release rate of the drug such that a minimum concentration of 0.01 nM to 1000 ⁇ M of silk is delivered to the tissue.
  • silk is released into the tissue surrounding a prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • silk may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of silk (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as silk is administered at half the above parameters, a compound half as potent as silk is administered at twice the above parameters, etc.).
  • the total dose of chitosan delivered into the tissue surrounding a prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of chitosan released around the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of chitosan as a function of the surface area of the portion of the device which is implanted
  • chitosan As specific (polymeric and non-polymeric) drug delivery vehicles can release chitosan at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug such that a minimum concentration of 0.01 nM to 1000 ⁇ M of chitosan is delivered to the tissue.
  • chitosan is released into the tissue surrounding a prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • chitosan may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of chitosan (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as chitosan is administered at half the above parameters, a compound half as potent as chitosan is administered at twice the above parameters, etc.).
  • the total dose of polylysine delivered into the tissue surrounding a prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of polylysine released should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of polylysine as a function of the surface area of the implanted portion of the device) should fall within the range of 0.05 ⁇ g-10 ⁇ g per mm 2 .
  • polylysine As specific (polymeric and non-polymeric) drug delivery vehicles can release polylysine at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug such that a minimum concentration of 0.01 nM to 1000 ⁇ M of polylysine is delivered to the tissue.
  • polylysine is released into the region surrounding a prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • polylysine may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of polylysine with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as polylysine is administered at half the above parameters, a compound half as potent as polylysine is administered at twice the above parameters, etc.).
  • the total dose of fibronectin delivered into the tissue surrounding a prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of fibronectin released should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of fibronectin as a function of the surface area of the portion of the device which is implanted
  • fibronectin As specific (polymeric and non-polymeric) drug delivery vehicles can release fibronectin at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug such that a minimum concentration of 0.01 nM to 1000 ⁇ M of fibronectin is delivered to the tissue surrounding the prosthesis.
  • fibronectin is released adjacent to the artificial joint such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • fibronectin may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of fibronectin (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as fibronectin is administered at half the above parameters, a compound half as potent as fibronectin is administered at twice the above parameters, etc.).
  • the total dose of bleomycin delivered into the tissue surrounding a prosthesis should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg). In one embodiment, the total amount of bleomycin released should be in the range of 0.10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of bleomycin as a function of the surface area of the portion of the device which is implanted
  • bleomycin As specific (polymeric and non-polymeric) drug delivery vehicles can release bleomycin at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug such that a minimum concentration of 0.001 nM to 1000 ⁇ M of bleomycin is delivered to the tissue surrounding the joint prosthesis.
  • bleomycin is released around the prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • bleomycin may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of bleomycin with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as bleomycin is administered at half the above parameters, a compound half as potent as bleomycin is administered at twice the above parameters, etc.).
  • the total dose of CTGF delivered into the tissue surrounding a prosthesis should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg). In one embodiment, the total amount of CTGF released should be in the range of 0.10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of CTGF as a function of the surface area of the portion of the device which is implanted should fall within the range of 0.005 ⁇ g-10 ⁇ g per mm 2 .
  • CTGF As specific (polymeric and non-polymeric) drug delivery vehicles can release CTGF at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug such that a minimum concentration of 0.001 nM to 1000 ⁇ M of CTGF is delivered to the tissue surrounding the artificial joint.
  • CTGF is released such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • CTGF may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of CTGF (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as CTGF is administered at half the above parameters, a compound half as potent as CTGF is administered at twice the above parameters, etc.).
  • the device may additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone) and/or a bone morphogenic protein (BMP) (e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, or BMP-7 or an analogue or derivative thereof).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone
  • BMP bone morphogenic protein
  • Bone morphogenic protein(s) are to be used in formulations at concentrations that range from 0.001 ⁇ g/ml to approximately 20 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • formulation type e.g., gel, liquid, solid, semi-solid
  • formulation chemistry e.g., gel, liquid, solid, semi-solid
  • duration of required application e.g., type of medical device interface and formulation volume and or surface area coverage required.
  • the bone morphogenic protein is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.001 ⁇ g to 500 mg); preferred 1 ⁇ g to 250 mg.
  • the dose is per unit area of 0.001 ⁇ g-1000 ⁇ g per mm 2 ; with a preferred dose of 0.01 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 9 -10 4 M of bone morphogenic protein is to be maintained on the device surface.
  • Inflammatory cytokines are to be used in formulations at concentrations that range from 0.0001 ⁇ g/ml to approximately 20 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • the inflammatory cytokine is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 100 mg); preferred 0.001 ⁇ g to 50 mg.
  • the dose is per unit area of 0.0001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 10 -10 ⁇ 4 g/ml of inflammatory cytokine is to be maintained on the device surface.
  • the device may alone or additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • Doses used are those concentrations which are demonstrated to stimulate cell proliferation (see, e.g., Example 16).
  • the proliferative agents are to be used in formulations at concentrations that range from 0.1 ng/ml to 25 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • formulation type e.g., gel, liquid, solid, semi-solid
  • formulation chemistry e.g., duration of required application
  • type of medical device interface e.g., aqueous containing formulation volume
  • formulation volume e.g., a coating thickness
  • the proliferative agent is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 200 mg); preferred 0.001 ⁇ g to 100 mg.
  • the dose is per unit area of 0.00001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.0001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 11 -10 ⁇ 6 M of proliferative agent is to be maintained on the device surface.
  • any of the previously described fibrosis inducing agents, or derivatives and analogues thereof, can be utilized to create variations of the above compositions without deviating from the spirit and scope of the invention. It should also be apparent that the agent can be utilized in a composition with or without polymer carrier and that altering the carrier does not deviate from the scope of this invention.
  • the present invention provides dental devices and implants that include a fibrosis or adhesion-inducing agent to assist in the incorporation of the implant into the surrounding tissue.
  • a fibrosis or adhesion-inducing agent to assist in the incorporation of the implant into the surrounding tissue.
  • a variety of devices is used in dental applications. Representative examples include dental implants and guided bone regeneration devices.
  • a dental implant of specific importance is a small titanium fixture that serves as a replacement for the root portion of a missing natural tooth.
  • the dental implant is placed in the bone of the upper or lower jaw and functions as an anchor for the replacement tooth. They may be used to support the replacement of a single missing tooth or a complete functional set for individuals who have lost many or all of their teeth.
  • Dental implants can be implanted in the bone (endosteal) or on the bone (subperiosteal). Endosteal implants are the most commonly used type of implant. There are various types of endosteal implants, which may include screws, cylinders or blades surgically placed into the jawbone. Each implant holds one or more prosthetic teeth. This type of implant is generally used as an alternative for patients with bridges or removable dentures. Subperiosteal implants are placed on top of the jaw with the metal framework's posts protruding through the gum to hold the prosthesis. These types of implants are used for patients who are unable to wear conventional dentures and who have minimal bone height.
  • the fibrosing agent may be incorporated into the glue or cement that holds the device in place.
  • the dental device is covered (all or in part) with a silk mesh or lattice to encourage scarring and anchoring into the surrounding bone.
  • a silk mesh or lattice can be coated onto all or a portion of the surface of the implant stem to encourage scarring and anchoring into the surrounding bone.
  • the device used to deliver a fibrosis-inducing agent may be a guided tissue regeneration (GTR) device, such as a GTR membrane.
  • GTR membrane is a resorbable or non-resorbable membrane made of biologically or non-biologically derived material. GTR membranes may be used in conjunction with a dental implant or to treat bone loss. GTR membranes may be made from a variety of materials, including, e.g., collagen (e.g., porcine collagen, types I and II), PTFE, polylactic acid, lactide and glycolide polymers, and ePTFE). GTR membranes are commercially available from W.L.
  • Gore & Associates Newark, Del.
  • Guidor e.g., GORE-TEX and GORE-RESOLUT regenerative material
  • Guidor Atrix Laboratories, Inc. (Fort Collins, Colo.), Geistlich Biomaterials, Inc. (e.g., BIO-GIDE), LifeCore Biomedical, Inc. (Chaska, Minn.), Ethicon Inc. (e.g., VICRYL), THM Biomedical now known as Kensey Nash Corporation (Exton, Pa.), and Suzler Calcitek, Inc. (Carlsbad, Calif.).
  • the dental device suitable for combining with a fibrosis-inducing agent is used for guided bone regeneration (GBR) to augment insufficient bone tissue and guide regrowth.
  • GBR devices include, e.g., resorbable bone substitutes for filling bony defects.
  • Such devices may consist of biomaterials (e.g., demineralized bone and bovine-derived materials) and synthetic materials, such as crystalline hydroxyapatite and calcium sulfate.
  • a variety of dental bone substitutes are commercially available, including the following products: OSTEOGRAF/N, OSTEOGRAF/LD, OSTEOGRAF/D, AND PERMARIDGE (all from Ceramad), bioactive glass, such as PERIOGLAS (U.S. Biomaterials), OSTEOGEN (Impladent, Inc.), VITOSS and CORTOSS.
  • the present invention provides dental implants containing a fibrosis-inducing agent for use in the treatment of common periodontal conditions.
  • periodontal disease is an inflammatory disease of the supporting structures of the teeth, including the ligaments, cementum, periosteum, alveolar bone and adjacent gingiva which anchor the teeth in place.
  • the condition begins with bleeding of the gums, but can progress to loosening of the teeth, receding gums, abscesses in pockets between the gums and the teeth, and necrotizing ulcerative gingivitis.
  • procedures such as gingivectomy, gingivoplasty, and correction of the bony architecture of the teeth may be required for treatment of the condition.
  • Dental implants have been developed in an attempt to control the healing process and optimize tissue regeneration.
  • Commonly used implants include permanent implants, such as e-PTFE membranes (e.g., GORE-TEX from W.L. Gore).
  • Commonly used implants include, e.g., BIOMEND, available from Sulzer Medica, Inc. (Houston, Tex.), which is a collagen membrane composed of compressed Type I collagen matrix derived from bovine Achilles tendon.
  • the collagen membrane (supplied as sheets, e.g., 15 mm ⁇ 20 mm; 20 mm ⁇ 30 mm; and 30 mm ⁇ 40 mm) is cut to the appropriate size and shape, hydrated and placed as a barrier between the overlying gingival tissue and the debrided periodontal defect; the barrier can be sutured in place, but this is not always required.
  • the membrane is placed snugly against the tooth root and draped over the surrounding alveolar bone (extending at least 3 mm beyond the defect margins) to effectively maintain the regenerative space.
  • Primary closure with mucoperiosteal flaps over the collagen membrane is important as exposure of the membrane to the oral cavity can result in premature degradation.
  • the barrier prevents faster growing epithelial tissue from entering the region and allows the slower growing periodontal ligament and bone cells to repopulate the area and effect appropriate healing.
  • the collagen membrane is bioresorbable, is retained for 6 to 7 weeks, and is fully absorbed by host enzymes (e.g., collagenase) within 8 weeks.
  • collagen-based implants may be used in the practice of the invention.
  • Representative examples of such implants include those that are used in variety of dental procedures including: COLLATAPE (Sulzer Medica, Inc.), which is a collagen-based implant used in the repair of minor oral wounds, closure of grafted sites and repair of Schneiderian Membranes; COLLACOTE (Sulzer Medica, Inc.), a collagen-based wound dressing used for palatal donor sites and in mucosal flaps; and COLLAPLUG (Sulzer Medica, Inc.), a solid collagen-based implant used in the repair of larger tissue defects such extraction sites or biopsy sites.
  • the present invention provides dental devices that include a fibrosis-inducing agent or a composition that includes a fibrosis-inducing agent to promote fibrosis in the periodontal pocket.
  • the dental device or material used to fill or maintain the periodontal pocket is coated with, composed of, or contains a fibrosing agent or a composition that includes a fibrosing agent.
  • compositions can further include one or more fibrosis-inducing agents to promote the formation of fibrous tissue around the dental implant.
  • Methods for incorporating fibrosing compositions onto or into the dental implant include: (a) directly affixing to the dental hardware a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier); (b) directly incorporating into the dental hardware a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier); (c) by coating the dental hardware with a substance such as a hydrogel which can in turn absorb the fibrosing composition; (d) by interweaving a thread coated with a fibrosis-inducing composition (or the a fibrosis-inducing polymer itself formed into
  • the coating process can be performed in such a manner as to (a) coat the surfaces of the device that is in contact with the bone, (b) coat the surfaces of the device that are not in contact with the bone or (c) coat all or parts of both the bone-contacting and non-bone contacting surface of the device.
  • the fibrosing agent can be mixed with the materials that are used to make the device such that the fibrosing agent is incorporated into the final device.
  • polymeric gels, pastes, injectables, solutions, microparticles and solid implants placed into the periodontal pocket are a preferred form of locally delivering a fibrosis-inducing agent. All involve the deployment of a biomaterial containing a fibrosis-inducing agent into the surgically-created periodontal pocket (as described above).
  • the practice of this embodiment can be performed in several ways including: (a) topical application of the fibrosing agent onto the periodontal pocket (particularly useful for this embodiment is the use of polymeric carriers which release the fibrosing agent over a period ranging from several hours to several weeks—fluids, suspensions, emulsions, microemulsions, microspheres, pastes, gels, microparticulates, sprays, aerosols, solid implants and other formulations which release a fibrosing agent and can be delivered into the region via specialized delivery catheters or other applicators); (b) placement of microparticulate silk and/or silk strands (linear, branched, and/or coiled) into the periodontal pocket; (c) sprayable collagen-containing formulations such as COSTASIS or materials made from 4-armed thiol PEG (10K), a 4-armed NHS PEG(10K) and methylated collagen such as described above, either alone, or loaded with a fibrosis-inducing agent, applied into period
  • a radio-opaque material such as tantalum, barium, other metal, or contrast material
  • the contrast agent may be a water soluble or water insoluble radio-opaque material.
  • fibrosing agents for use in dental prostheses include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, and CTGF, as well as analogues and derivatives of the aforementioned.
  • the device may additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone) or a bone morphogenic protein (BMP) (e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, or BMP-7 or an analogue or derivative thereof).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone
  • BMP bone morphogenic protein
  • the exact dose administered can vary with device size, surface area and design. However, certain principles can be applied in the application of this art. Drug dose can be calculated as a function of dose per unit area (of the portion of the device being coated), total drug dose administered can be measured and appropriate surface concentrations of active drug can be determined. Regardless of the method of application of the drug to the dental prostheses or periodontal implant, the exemplary fibrosing agents, used alone or in combination, should be administered under the following dosing guidelines:
  • the total dose of talc delivered from a dental prosthesis, or coated onto the surface of a dental prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of talc released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of talc as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • talc should be applied to a dental prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • talc is released from the surface of a dental prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months. For example, talc may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of talc (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as talc is administered at half the above parameters, a compound half as potent as talc is administered at twice the above parameters, etc.).
  • the total dose of silk delivered from a dental prosthesis, or coated onto the surface of a dental prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of silk released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of silk as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • silk should be applied to a dental prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release silk at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the dental prosthesis such that a minimum concentration of 0.01 nM to 1000 ⁇ M of silk is delivered to the tissue.
  • silk is released from the surface of a dental prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months. For example, silk may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of silk (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as silk is administered at half the above parameters, a compound half as potent as silk is administered at twice the above parameters, etc.).
  • the total dose of chitosan delivered from a dental prosthesis, or coated onto the surface of a dental prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of chitosan released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of chitosan as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • chitosan should be applied to a dental prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • chitosan is released from the surface of a dental prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • chitosan may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of chitosan (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as chitosan is administered at half the above parameters, a compound half as potent as chitosan is administered at twice the above parameters, etc.).
  • the total dose of polylysine delivered from a dental prosthesis, or coated onto the surface of a dental prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of polylysine released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of polylysine as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • the dose per unit area of the device should fall within the range of 0.05 ⁇ g-10 ⁇ g per mm 2 of surface area coated.
  • polylysine should be applied to a dental prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • polylysine As specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release polylysine at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the dental prosthesis such that a minimum concentration of 0.01 nM to 1000 ⁇ M of polylysine is delivered to the tissue.
  • polylysine is released from the surface of a dental prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • polylysine may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of polylysine with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as polylysine is administered at half the above parameters, a compound half as potent as polylysine is administered at twice the above parameters, etc.).
  • the total dose of fibronectin delivered from a dental prosthesis, or coated onto the surface of a dental prosthesis should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of fibronectin released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of fibronectin as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • talc should be applied to a dental prosthesis surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • fibronectin is released from the surface of a dental prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • fibronectin may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of fibronectin (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as fibronectin is administered at half the above parameters, a compound half as potent as fibronectin is administered at twice the above parameters, etc.).
  • the total dose of bleomycin delivered from a dental prosthesis, or coated onto the surface of a dental prosthesis should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg). In one embodiment, the total amount of bleomycin released from the prosthesis should be in the range of 0.10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of bleomycin as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • bleomycin should be applied to a dental prosthesis surface at a dose of 0.005 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • bleomycin is released from the surface of a dental prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • bleomycin may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of bleomycin with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as bleomycin is administered at half the above parameters, a compound half as potent as bleomycin is administered at twice the above parameters, etc.).
  • the total dose of CTGF delivered from a dental prosthesis, or coated onto the surface of a dental prosthesis should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg). In one embodiment, the total amount of CTGF released from the prosthesis should be in the range of 0.10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of CTGF as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • CTGF should be applied to a dental prosthesis surface at a dose of 0.005 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release CTGF at differing rates
  • the above dosing parameters should be utilized in combination with the release rate of the drug from the dental prosthesis such that a minimum concentration of 0.001 nM to 1000 ⁇ M of CTGF is delivered to the tissue.
  • CTGF is released from the surface of a dental prosthesis such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • CTGF may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of CTGF (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as CTGF is administered at half the above parameters, a compound half as potent as CTGF is administered at twice the above parameters, etc.).
  • Bone morphogenic protein(s) e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, or BMP-7 or an analogue or derivative thereof
  • formulations e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, or BMP-7 or an analogue or derivative thereof
  • concentrations range from 0.001 ⁇ g/ml to approximately 20 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • the bone morphogenic protein is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.001 ⁇ g to 500 mg); preferred 1 ⁇ g to 250 mg.
  • the dose is per unit area of 0.001 ⁇ g-1000 ⁇ g per mm 2 ; with a preferred dose of 0.01 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 9 -10 ⁇ 4 M of bone morphogenic protein is to be maintained on the device surface.
  • Inflammatory cytokines are to be used in formulations at concentrations that range from 0.0001 ⁇ g/ml to approximately 20 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • the inflammatory cytokine is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 100 mg); preferred 0.001 ⁇ g to 50 mg.
  • the dose is per unit area of 0.0001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 10 -10 ⁇ 4 g/ml of inflammatory cytokine is to be maintained on the device surface.
  • the device may alone or additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3, diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof. Doses used are those concentrations which are demonstrated to stimulate cell proliferation (see, e.g., Example 16).
  • the proliferative agents are to be used in formulations at concentrations that range from 0.0.1 ng/ml to 25 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • formulation type e.g., gel, liquid, solid, semi-solid
  • formulation chemistry e.g., duration of required application
  • type of medical device interface e.g., aqueous containing formulation volume
  • formulation volume e.g., a coating thickness
  • the proliferative agent is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 200 mg); preferred 0.001 ⁇ g to 100 mg.
  • the dose is per unit area of 0.00001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.0001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 11 -10 ⁇ 6 M of proliferative agent is to be maintained on the device surface.
  • any of the previously described fibrosis inducing agents, or derivatives and analogues thereof, can be utilized to create variations of the above compositions without deviating from the spirit and scope of the invention. It should also be apparent that the agent can be utilized in a composition with or without polymer carrier and that altering the carrier does not deviate from the scope of this invention.
  • the present invention provides orthopedic implants that include a fibrosis-inducing agent or a composition that includes a fibrosis-inducing agent to promote scarring and fixation of the device into the surrounding bone or tissue.
  • the orthopedic implant is an orthopedic “hardware” device that has been coated with a fibrosing agent or a fibrosing agent containing composition.
  • orthopedic hardware devices include internal and external fixation devices, fixation screws (degradable or non-degradable), interferential screws (degradable and non-degradable), trochanteric screws, plates, wires (e.g., K-wires), pins, and nails used in fracture repairs, reconstructive procedures, and joint fusion procedures (e.g., ankle fusions, cervical and lumbar spinal fusions).
  • Compositions also are provided for coating devices used in fusion procedures and superior repair of fractures.
  • Orthopedic implants such as, for example, fixation screws, pins, plates, nails, wires and plates coated with a fibrosing agent, coated with a composition containing a fibrosing agent, or composed of a polymer that releases a fibrosing agent (particularly for polymeric, biodegradable orthopedic hardware) are used to encourage better anchorage of the implant into the surrounding bone.
  • the fibrosing agent may be incorporated into the glue or cement that holds the implant in place.
  • the orthopedic hardware is covered (all or in part) with a silk mesh or lattice to encourage scarring and anchoring into the surrounding bone.
  • a silk mesh or lattice can be coated onto all or a portion of the surface of the implant stem to encourage scarring and anchoring into the surrounding bone.
  • the orthopedic implant is a collagen implant for use as a substitute for autogenous or allogenous bone grafts.
  • collagen implants have been developed for use in orthopedic surgery as a substitute for autogenous or allogenous bone grafts.
  • Collagen is the principle organic component of bone and can be combined with mineral formulations, autogenous bone marrow, bone graft, and/or growth factors (such as BMPs) for use as a bone substitute or a skeletal repair product.
  • Typical applications include, but are not restricted to, total joint replacement surgery (e.g., artificial hips, knees, etc.), spinal fusion surgery, long bone fractures, repair of traumatic bone defects, voids, or gaps, to augment an autograft, and as a bone filler at bone graft harvesting sites.
  • Examples of commercially available collagen-based bone grafts include COLLAGRAFT Paste and COLLAGRAFT Strips made by Angiotech Pharmaceuticals, Inc.
  • COLLAGRAFT is a combination of highly purified Type I bovine dermal fibrillar collagen and a mixture of 65% hydroxyapatite and 35% tricalcium phosphate. This material closely resembles human bone and is resorbed and replaced with bone during the healing process. Representative examples of bone grafts are described in U.S. Pat. Nos. 6,083,522 and 6,280,474 and in PCT Publication No. WO 98/52498.
  • compositions can further include one or more fibrosis-inducing agents to promote the formation of granulation tissue (described further in section (iii) below).
  • Methods for incorporating fibrosing compositions onto or into the orthopedic implants include: (a) directly affixing to the device a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier); (b) directly incorporating into the device a fibrosing composition (e.g., by either a spraying process or dipping process as described above, with or without a carrier); (c) by coating the device with a substance such as a hydrogel which can in turn absorb the fibrosing composition; (d) by interweaving into the device a thread coated with a fibrosing composition (or a polymeric version of the fibrosing agent is itself formed into a thread); (e) by inserting the device into a sleeve or mesh which is comprised of, or coated with, a fibrosing composition; (f) constructing the device itself or a portion of the device with a fibrosing composition (particularly effective for biodegradable orthopedic hardware and collagen
  • the coating process can be performed in such a manner as to (a) coat the surfaces of the device that is in contact with the bone; (b) coat the surfaces of the device that are not in contact with bone, or (c) coat all or parts of both the bone-contacting and non-bone contacting surface of the device.
  • fibrosing agents for use in the coating of orthopedic hardware include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, and/or CTGF as well as analogues and derivatives of the aforementioned.
  • the correct administration and dosage is the same as that described previously in section 2(i), 2(ii) and 2(iii) for artificial hips, knees and shoulder prostheses.
  • the present invention provides injectable compositions to promote scarring and fixation (immobilization) of a joint without the need for open surgery.
  • a composition including an adhesion or fibrosis-inducing agent may be injected into an arthritic or damaged joint to promote scarring and fixation (i.e., immobilization) of the joint (particularly interphalageal joints, tarsal-metatarsal joints, metacarpal joints, ankle joints, knee joints, proximal tibia-fibular joint, hip joint, sacro-iliac joint, acromio-clavicular joint, sterno-clavicular joint and facet joints in the cervical, thoracic, and lumbar spine).
  • a needle is inserted into the joint cavity, a guidewire is advanced into the joint space, a dual lumen catheter (for many of the hydrogels described below such as a material made from 4-armed thiol PEG (10K), a 4-armed NHS PEG(10K) and methylated collagen such as described above, COSEAL, COSTASIS, FLOSEAL, TISSEAL, VITOSS) or a single lumen catheter (for materials such as cyanoacrylate, CORTOSS, bone cement, hydroxyapatite, calcium phosphate, calcium sulfate, hyaluronic acid, proteins, carbohydrates, sclerosing agents, and the like) is advanced over the guidewire into the articular space, the guidewire is removed, and a composition containing a fibrosis-inducing agent, bone morphogenic protein(s), and/or osteogenic growth factor (such as transforming growth factor, platelet-derived growth factor, fibroblast growth factor) is injected via the catheter into joint until the joint space
  • Agents such as collagenase, chymopapain, or other tissue-degrading enzymes may also be used to chemically degrade the remaining cartilage prior to, or during, the injection of the joint-fusing composition.
  • the fibrosis-inducing agent, bone morphogenic protein, and/or osteogenic growth factor can encourage fibrous ankylosis, followed by bony ankylosis of the treated joint, leading to decreased (or complete loss of) range of motion, stability, and/or reduced pain.
  • techniques can be used to enhance visualization of needle (or catheter) placement within the joint space including, but not limited to, the use of a needle coated with ECHO—COAT, the injection of air to enable localization by ultrasound, or the addition of contrast agents (barium, tantalum, technitium, gadolinium, and the like) for localization by x-ray or MRI.
  • contrast agents barium, tantalum, technitium, gadolinium, and the like
  • the fibrosing agent and/or osteogenic agent is delivered under direct vision during arthroscopic evaluation of the joint.
  • the composition containing the fibrosis-inducing agent, bone morphogenic protein, and/or osteogenic growth factor is injected into the articular space through the side port of an arthroscope, preferably after the remaining articular cartilage has been mechanically or chemically debrided.
  • the fibrosis-inducing agent may also be delivered directly to the tissue during open joint fusion surgery to enhance the efficacy of this procedure.
  • the injectable material may be also composed of an injectable polymer system for use in minimally invasive joint fusion. Additionally, the polymer system can provide sustained release of the fibrosis-inducing agent, bone morphogenic protein, and/or osteogenic growth factor to enhance efficacy and reduce the need for repeated intra-articular administrations of active agents.
  • the injection material suitable for delivery of a fibrosis-inducing agent, bone morphogenic protein, and/or growth factor that promotes bone growth for the purposes of this invention can be composed of a non-degradable or a degradable material.
  • Suitable non-degradable materials can include crosslinked compositions that comprise PVA, PVP, polyacrylamide, methyl methacrylate (MMA) and methyl methacrylate styrene (MMA-styrene) which when mixed together form polymethyl methacrylate (PMMA) or bone cement (e.g., SIMPLEX P, ZIMMER REGULAR and ZIMMER LOW VISCOSITY CEMENT, PALACOS, CMW-1 and CMW-2, ENDURANCE, synthetic cancellous bone void fillers (e.g., CORTOSS), pHEMA, poly(vinyl PEG), poly(styrene sulfonate), poly(acrylic acid), poly(methacrylic acid), as well as other polymers that are known to form hydrogels.
  • PMMA polymethyl methacrylate
  • MMA-styrene methyl methacrylate styrene
  • synthetic cancellous bone void fillers e.g., CORTOSS
  • pHEMA poly(
  • compositions include blends and copolymers of the agents listed above.
  • Suitable degradable materials include, but are not limited to, resorbable ceramics composed of ⁇ -tricalcium phosphate (e.g., VITOSS, PROOSTEON 500R), hydroxyapatite or Ca 10 (PO 4 ) 6 OH (e.g., BIOOSS, OSTEOGRAF), calcium carbonate or CaCO 3 , calcium sulfate (e.g., OSTEOSET and ALLOMATRIX), calcium phosphate (e.g., CALCIBON or NORIAN SRS), crosslinked materials of PEG, gelatin, collagen, bone allografts (e.g., ALLOGRO, ORTHOBLAST, OPTEFORM, GRAFTON), mesenchymal stem cells, hyaluronic acid, hyaluronic acid derivatives, polysaccharides, carbohydrates, proteins (e.g., albumin, casein, whey proteins, plant proteins, or fish proteins, and
  • the injectable material also contains a biologically active agent capable of inducing fibrosis and ankylosis in the treated joint.
  • Preferred biologically active agents include fibrosis-inducing agents, bone morphogenic proteins, and growth factors (transforming growth factor, platelet-derived growth factor, fibroblast growth factor), whose dosages and release kinetics are all described in detail in section (iii) below.
  • the injectable material can be utilized to deliver a sclerosant to the articular space.
  • Sclerosants include compounds such as ethanol, DMSO, surfactants, sucrose, NaCl, dextrose, glycerin, minocycline, tetracycline, doxycycline, polidocanol, sodium tetradecyl sulfate, sodium morrhuate, sotradecol and others.
  • the hydrogel can further comprise agents such as glycerol, glycerin, PEG 200, triethyl citrate, and triacetin as plasticizers.
  • the injectable materials described above can further modified to be comprised of, or contain, polymeric threads.
  • Polymeric threads have the ability to induce a fibroproliferative response from the surrounding tissue.
  • These polymer threads can be degradable or non-degradable.
  • Degradable threads can be composed of degradable polyesters, polyanhydrides, poly(anhydride esters), poly(ester-amides), poly(ester-ureas), polyorthoesters, polyphosphoesters, polyphosphazines, cyanoacrylate polymers, collagen, chitosan, hyaluronic acid, chromic cat gut, alginates, starch, cellulose, cellulose esters, blends and copolymers thereof, as well as other known degradable polymers.
  • Non-degradable polymers that can be used include, but are not limited to, polyesters (e.g., PET), polyurethanes, silicones, PE, PP, PS, PAA, PMA, silk, blends, copolymers thereof as well as others known polymers.
  • the threads used can be composed of a single composition or composed of a blend of differing compositions.
  • the polymeric threads themselves can be further modified through the addition of a polymeric coating applied to the threads.
  • the polymer used for coating the thread can be similar to that described above for the threads themselves.
  • the polymer coating may further comprise a biologically active agent that has the ability to induce a fibroproliferative or osteogenic response.
  • the agents that can be used are further described in the section (iii) below.
  • the injectable materials described above can be utilized to deliver a particulate material that has the ability to induce ankylosis in the joint.
  • These particles can be either degradable or non-degradable and are similar to those described above for threads.
  • particulate materials useful for the practice of this embodiment include talc, starch, glass, silicates, silica, calcium phosphate, calcium sulfate, calcium carbonate, hydroxyapatite, synthetic mineral (VITOSS and CORTOSS), PMMA, silver nitrate, ceramic particles and other inorganic particles known in the art to induce a fibroproliferative response followed by mineralization.
  • the particles used in this embodiment can be all of the same composition or a blend of differing compositions. These particles can also be used as a coating applied to the polymeric strands as described above.
  • the injectable material can also be constructed such that it is comprised of both polymeric threads and particles.
  • the threads and particles used are similar to those described above and may be of uniform composition or blended composition. Virtually any combination of threads of differing compositions and particles of differing compositions can be utilized in this embodiment.
  • the hydrogel, the polymeric threads, and the particles can all be utilized to deliver one or more biologically active agents, as described below.
  • One specific composition comprises rods prepared from a methylated collagen-crosslinked poly(ethylene glycol) composition such as described above which has powdered silk particles and/or mineral particles added to the composition prior to curing. Once deployed, the rod can absorb water, fill the joint space and adhere to any articular cartilage or exposed bone. This expansion can prevent the rod from moving, while the powdered and/or mineral silk can initiate an ankylosing response. As the material starts to degrade, the material can support the bone tissue ingrowth that is initiated and potentiated by the particles. Bone morphogenic proteins and/or growth factors (described previously and below) are also useful for the addition to this composition.
  • a sclerosant such as a surfactant (SDS), ethanolamine oleate or DMSO can be added.
  • SDS surfactant
  • ethanolamine oleate DMSO
  • the amino PEG can provide a gel that can take a longer time to degrade and can provide some positive charge to further attract cellular material.
  • a second specific embodiment consists of an injectable implant composed of silk fibers or a polymerized version of the fibrosing agent itself (i.e., repeating units of the fibrosing agent polymerized together).
  • the addition of bone morphogenic proteins and/or growth factors is also useful for the addition to this composition.
  • compositions suitable for use in minimally invasive joint fusion procedures involve the deployment of a biomaterial into the joint space, with or without, the addition of a fibrosis-inducing agent, bone morphogenic protein(s), and/or a suitable growth factor(s).
  • compositions can be delivered into the joint via specialized delivery catheters, an endoscope (arthroscope; typically via a sideport), a needle or other applicator, a surgically placed drain or access port, or other transdermal access device, including administration of: (a) fluids, suspensions, emulsions, microemulsions, microspheres, pastes, gels, microparticulates, sprays, aerosols, solid implants and other formulations which release a biologically active agent(s); (b) microparticulate silk and/or silk strands (linear, branched, and/or coiled) either alone, or loaded with an additional fibrosis-inducing agent, bone morphogenic protein, and/or growth factor are also useful for directed injection into the joint; (c) injectable collagen-containing formulations such as COSTASIS or materials prepared from a 4-armed thiol PEG (10K), a 4-armed NHS PEG (10K) and methylated collagen such as described above, either alone, or loaded with a
  • This hydrogel may further contain collagen, methylated collagen and/or gelatin.
  • This hydrogel can further comprise the fibrosis-inducing agents described above (e.g., silk powder or silk threads).
  • a radio-opaque material such as tantalum, barium, other metal, or contrast material
  • the injected material can be visualized radiographically or MRI.
  • fibrosing agents for use in minimally invasive joint fusion procedures include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, CTGF, bone morphogenic proteins, and/or osteogenic growth factors (such as transforming growth factor, platelet-derived growth factor, fibroblast growth factor) as well as analogues and derivatives of the aforementioned.
  • the device may alone or additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone) or a bone morphogenic protein (BMP) (e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, or BMP-7 or an analogue or derivative thereof).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone
  • BMP bone morphogenic protein
  • the device may alone or additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • Exemplary fibrosing and osteogenic agents for use in minimally invasive joint fusion include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, CTGF, bone morphogenic proteins, and/or osteogenic growth factors (such as transforming growth factor, platelet-derived growth factor, fibroblast growth factor) as well as analogues and derivatives of the aforementioned.
  • osteogenic growth factors such as transforming growth factor, platelet-derived growth factor, fibroblast growth factor
  • Drug dose can vary depending upon the particular joint being treated. However, certain principles can be applied in the application of this art. Drug dose can be calculated as a function of dose per unit volume (of the amount being injected), total drug dose administered can be measured and appropriate surface concentrations of active drug can be determined. Regardless of the method of application of the drug to the affected joint, the exemplary fibrosing agents, bone morphogenic proteins, and/or osteogenic growth factors (such as transforming growth factor, platelet-derived growth factor, fibroblast growth factor), used alone or in combination, should be administered under the following dosing guidelines:
  • the total dose of talc administered into a joint in any single injection should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of talc administered should be in the range of 10 ⁇ g to 50 mg. The dose per unit volume injected should fall within the range of 0.05 ⁇ g-10 ⁇ g per mm 3 . In one embodiment, talc is released from the injectable such that ankylosis in the joint is promoted for a period ranging from several hours to several months.
  • talc may be released in effective concentrations for a period ranging from 2-12 weeks.
  • analogues and derivatives of talc (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as talc is administered at half the above parameters, a compound half as potent as talc is administered at twice the above parameters, etc.).
  • the total dose of silk delivered to the joint in any single injection should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of silk administered to the joint should be in the range of 10 ⁇ g to 50 mg. The dose per unit volume injected should fall within the range of 0.05 ⁇ g-10 ⁇ g per mm 3 .
  • the above dosing parameters should be utilized in combination with the release rate of the drug from the carrier such that a minimum concentration of 0.01 nM to 1000 ⁇ M of silk is continuously delivered to the tissue over the desired therapeutic time period.
  • silk is released into the joint such that ankylosis is promoted for a period ranging from several hours to several months.
  • silk may be released in effective concentrations for a period ranging from 2-12 weeks.
  • analogues and derivatives of silk (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as silk is administered at half the above parameters, a compound half as potent as silk is administered at twice the above parameters, etc.).
  • the total dose of chitosan delivered into the joint should not exceed 100 mg (range of 1 ⁇ g to 100 mg).
  • the total amount of chitosan administered into the joint in any single injection should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit volume injected should fall within the range of 0.05 ⁇ g-10 ⁇ g per mm 3 .
  • chitosan As specific (polymeric and non-polymeric) drug delivery vehicles can release chitosan at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the carrier such that a minimum concentration of 0.01 nM to 1000 ⁇ M of chitosan is continuously delivered to the joint tissue.
  • chitosan is released into the joint such that ankylosis is promoted for a period ranging from several hours to several months.
  • chitosan may be released in effective concentrations for a period ranging from 2-12 weeks.
  • analogues and derivatives of chitosan (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as chitosan is administered at half the above parameters, a compound half as potent as chitosan is administered at twice the above parameters, etc.).
  • the total dose of polylysine delivered into the joint in a single injection should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of polylysine delivered to the joint should be in the range of 10 ⁇ g to 50 mg. The dose per unit volume injected should fall within the range of 0.05 ⁇ g-10 ⁇ g per mm 3 . In another embodiment, polylysine should be injected into the joint at a dose of 0.05-10 ⁇ g/mm 3 .
  • polylysine As specific (polymeric and non-polymeric) drug delivery vehicles can release polylysine at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the carrier such that a minimum concentration of 0.01 nM to 1000 ⁇ M of polylysine is continuously delivered to the joint tissue.
  • polylysine is administered to the joint such that ankylosis is promoted for a period ranging from several hours to several months.
  • polylysine may be released in effective concentrations for a period ranging from 2-12 weeks.
  • analogues and derivatives of polylysine with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as polylysine is administered at half the above parameters, a compound half as potent as polylysine is administered at twice the above parameters, etc.).
  • the total dose of fibronectin delivered into the joint in a single injection should not exceed 100 mg (range of 1 ⁇ g to 100 mg).
  • the total amount of fibronectin injected into the joint should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit volume of the injection should fall within the range of 0.05 ⁇ g-10 ⁇ g per mm 3 .
  • talc should be administered at a dose of 0.05-10 ⁇ g/mm 3 of injected material.
  • fibronectin As specific (polymeric and non-polymeric) drug delivery vehicles can release fibronectin at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the carrier such that a minimum concentration of 0.01 nM to 1000 ⁇ M of fibronectin is continuously delivered to the tissue.
  • fibronectin is released into the joint such that ankylosis is promoted for a period ranging from several hours to several months.
  • fibronectin may be released in effective concentrations for a period ranging from 2-12 weeks.
  • analogues and derivatives of fibronectin (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as fibronectin is administered at half the above parameters, a compound half as potent as fibronectin is administered at twice the above parameters, etc.).
  • the total dose of bleomycin administered to a joint in a single injection should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg). In one embodiment, the total amount of bleomycin injected into the joint should be in the range of 0.10 ⁇ g to 50 mg. The dose per unit volume injected should fall within the range of 0.005 ⁇ g-10 ⁇ g per mm 3 .
  • bleomycin As specific (polymeric and non-polymeric) drug delivery vehicles can release bleomycin at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the carrier such that a minimum concentration of 0.001 nM to 1000 ⁇ M of bleomycin is continuously delivered to the joint.
  • bleomycin is released from the injection such that ankylosis in the joint is promoted for a period ranging from several hours to several months.
  • bleomycin may be released in effective concentrations for a period ranging from 2-12 weeks.
  • analogues and derivatives of bleomycin with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as bleomycin is administered at half the above parameters, a compound half as potent as bleomycin is administered at twice the above parameters, etc.).
  • the total dose of CTGF administered to the joint in a single injection should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg).
  • the total amount of CTGF injected into the joint should be in the range of 0.10 ⁇ g to 50 mg.
  • the dose per unit volume of the injection should fall within the range of 0.005 ⁇ g-10 ⁇ g per mm 3 .
  • CTGF should be injected at a dose of 0.005-10 ⁇ g/mm 3 .
  • CTGF As specific (polymeric and non-polymeric) drug delivery vehicles can release CTGF at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the carrier such that a minimum concentration of 0.001 nM to 1000 ⁇ M of CTGF is continuously delivered to the joint.
  • CTGF is released from the injectable such that ankylosis in the joint is promoted for a period ranging from several hours to several months.
  • CTGF may be released in effective concentrations for a period ranging from 2-12 weeks.
  • analogues and derivatives of CTGF (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as CTGF is administered at half the above parameters, a compound half as potent as CTGF is administered at twice the above parameters, etc.).
  • the device may alone or additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone) or a bone morphogenic protein (BMP) (e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, or BMP-7 or an analogue or derivative thereof).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone
  • BMP bone morphogenic protein
  • Inflammatory cytokines are to be used in formulations at concentrations that range from 0.0001 ⁇ g/ml to approximately 20 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • the inflammatory cytokine is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 100 mg); preferred 0.001 ⁇ g to 50 mg.
  • the dose is per unit area of 0.0001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 10 -10 ⁇ 4 g/ml of inflammatory cytokine is to be maintained on the device surface.
  • Bone morphogenic protein(s) are to be used in formulations at concentrations that range from 0.001 ⁇ g/ml to approximately 20 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • formulation type e.g., gel, liquid, solid, semi-solid
  • formulation chemistry e.g., gel, liquid, solid, semi-solid
  • duration of required application e.g., type of medical device interface and formulation volume and or surface area coverage required.
  • the bone morphogenic protein is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.001 ⁇ g to 500 mg); preferred 1 ⁇ g to 250 mg.
  • the dose is per unit area of 0.001 ⁇ g-1000 ⁇ g per mm 2 ; with a preferred dose of 0.01 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 9 -10 ⁇ 4 M of bone morphogenic protein is to be maintained on the device surface.
  • the device may alone or additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • Doses used are those concentrations which are demonstrated to stimulate cell proliferation (Example 16).
  • the proliferative agents are to be used in formulations at concentrations that range from 0.01 ng/mL to 25 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • formulation type e.g., gel, liquid, solid, semi-solid
  • formulation chemistry e.g., duration of required application
  • type of medical device interface e.g., aqueous containing formulation volume
  • formulation volume e.g., a coating thickness
  • the proliferative agent is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 200 mg); preferred 0.001 ⁇ g to 100 mg.
  • the dose is per unit area of 0.00001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.0001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 11 -10 ⁇ 6 M of proliferative agent is to be maintained on the device surface.
  • any of the previously described fibrosis-inducing agents, bone morphogenic proteins, or osteogenic growth factors, or derivatives and analogues thereof, can be utilized to create variations of the above compositions without deviating from the spirit and scope of the invention. It should also be apparent that the agent can be utilized in a composition with or without polymer carrier and that altering the carrier does not deviate from the scope of this invention.
  • tubal ligation and vasectomy have a low failure rate (approximately 1%), recently there have been advancements in making the procedures less invasive. This is particularly true for tubal ligation where a surgical procedure, either open or endoscopic, is required to “clip” the fallopian tubes. Newer implants have been designed to obstruct the fallopian tubes (or vas deferens in the male) through the non-surgical placement of implants that block the interior lumen of the reproductive tract.
  • the present invention provides compositions, implants and devices that include a fibrosis-inducing agent to promote scarring of the walls of the reproductive tract in the vicinity of the implant or device. The result is the formation of permanent scar tissue between the walls of the fallopian tube (or vas deferens) that completely obstructs the lumen, prevents the movement of the gametes through the tract, and lowers the failure rate of the procedure (measured as the prevention of unwanted pregnancies).
  • a preferred embodiment of the present invention involves delivering a fibrosis-inducing agent in combination with a variety of devices and implants designed for placement in the fallopian tubes without the need for surgery.
  • all are intended to be placed transvaginally (i.e., the device or implant is inserted into the vagina, through the uterus, and placed into the interior lumen of the fallopian tube), thus eliminating the need for surgical access to the external (intra-abdominal/pelvic) surface of the fallopian tube via the abdomen.
  • these implants obstruct the fallopian tube from the inside (luminal surface) and can be performed in a conscious patient in much the same manner as a gynecological exam.
  • fallopian tube implants suitable for delivering a fibrosis-inducing agent that enhances tubal occlusion include: implantable, intrafallopian, female sterilization devices (such as those described in U.S. Pat. Nos. 6,245,090; 6,068,626; and 3,675,639); occlusive wire or coil fallopian tube implants (such as those described in U.S. Pat. No. 5,601,600); transcatheter occluding implants (such as those described in U.S. Pat. No. 6,245,090); and fallopian tube stents (for example those described in U.S. Pat. No. 5,474,089).
  • contraceptive uterine implants such as intrauterine devices (IUDs) can also be suitable for use in this embodiment.
  • the ESSURE device is a catheter-delivered stent filled with fiber (a soft micro-insert) designed to occlude the fallopian tubes (Conceptus, Inc., San Carlos, Calif.) and is described in U.S. Pat. Nos. 6,176,240; 6,526,979; 5,601,600; and 5,746,769.
  • the ECLIPSE from Ovion is a self-expanding nitinol stent filled with polyester fibers that is delivered transvaginally via a catheter into the fallopian tubes.
  • Other contraceptive fallopian tube implants include porous plastic fibers (Adiana, Redwood, Calif.) and single rod implants such as IMPLANON from Organon Corporation (West Orange, N.J.).
  • the aforementioned contraceptive implants can be adapted to release an agent which induces fibrosis or adhesion within the fallopian tube.
  • the result can be enhanced scarring around the implant, more complete (and permanent) filling and/or occlusion of the lumen of the fallopian tube, and a reduction in the likelihood that female or male reproductive cells can traverse the blockade and come in contact with each other—thereby reducing the incidence of unwanted intrauterine pregnancy or tubal pregnancy.
  • Fallopian tube implants may be adapted to have a fibrosis-inducing agent incorporated into their structure, adapted to have a surface coating of a fibrosis-inducing agent and/or adapted to release a fibrosis-inducing agent.
  • fibrosing agents for use in fallopian tube implants and devices include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, and CTGF, as well as analogues and derivatives of the aforementioned.
  • the device may alone or additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone) or a bone morphogenic protein (BMP) (e.g., BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, OR BMP-7 or an analogue or derivative thereof).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone
  • BMP bone morphogenic protein
  • the device may alone or additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • Another preferred embodiment of the present invention involves delivering a fibrosis-inducing agent in combination with a biomaterial designed for injection into the fallopian tubes to “plug” or obstruct the tube.
  • a transvaginal route of administration i.e., the delivery device is inserted into the vagina, through the uterus, placed into the interior lumen of the fallopian tube, and the biomaterial containing a fibrosis-inducing agent is injected into the lumen of the fallopian tube), thus eliminating the need for surgical access to the external (intra-abdominal/pelvic) surface of the fallopian tube via the abdomen.
  • these implants obstruct the fallopian tube from the inside (luminal surface) and can be performed in a conscious patient in much the same manner as a gynecological exam.
  • the biomaterial can obstruct the lumen of the tube, while the fibrosis-inducing agent encourages the formation of scar tissue between the walls of the fallopian tube to permanently obstruct the lumen, prevent the movement of the gametes through the tract, and lower the failure rate of the procedure (measured as the prevention of unwanted pregnancies).
  • the injectable material may be composed of a hydrogel for use in the sterilization of a mammalian female.
  • the hydrogel can be composed of a non-degradable or a degradable material.
  • Non-degradable materials can include crosslinked compositions that comprise PVA, PVP, polyacrylamide, pHEMA, poly(vinyl PEG), poly(styrene sulfonate), poly(acrylic acid), poly(methacrylic acid), as well as other polymers that are known to form hydrogels. Additional compositions include blends and copolymers of the agents listed above.
  • Degradable materials include, but are not limited to, crosslinked materials of PEG, gelatin, collagen, hyaluronic acid, hyaluronic acid derivatives, polysaccharides, carbohydrates, proteins (e.g., albumin, casein, whey proteins, plant proteins, and fish proteins), cellulose derivatives (e.g., HPC), chitosan, chitosan derivatives, polyester-polyalkylene oxide block copolymers (e.g., PLGA-PEG-PLGA and MePEG-PLGA) and other low molecular weight polymers that can be excreted.
  • PEG polysaccharides
  • carbohydrates e.g., albumin, casein, whey proteins, plant proteins, and fish proteins
  • proteins e.g., HPC
  • chitosan chitosan derivatives
  • polyester-polyalkylene oxide block copolymers e.g., PLGA-PEG-PLGA and MePEG-PLGA
  • the hydrogel also contains a biologically active agent capable of inducing fibrosis in the fallopian tube.
  • a biologically active agent capable of inducing fibrosis in the fallopian tube.
  • Preferred, biologically active, fibrosis-inducing, agents, their dosages and their release kinetics, are all described in detail in section (c) below.
  • the hydrogel can be utilized to deliver a sclerosant to the fallopian tube.
  • Sclerosants include compounds such as ethanol, DMSO, surfactants, sucrose, NaCl, dextrose, glycerin, minocycline, tetracycline, doxycycline, polidocanol, sodium tetradecyl sulfate, sodium morrhuate, sotradecol and others.
  • the hydrogel can further comprise agents such as glycerol, glycerin, PEG 200, triethyl citrate, and triacetin as plasticizers.
  • hydrogels described above can further modified to be comprised of, or contain, polymeric threads.
  • Polymeric threads have the ability to induce a fibroproliferative response from the surrounding tissue in the fallopian tube. These polymer threads can be degradable or non-degradable.
  • Degradable threads can be composed of degradable polyesters, polyanhydrides, poly(anhydride esters), poly(ester-amides), poly(ester-ureas), polyorthoesters, polyphosphoesters, polyphosphazines, cyanoacrylate polymers, collagen, chitosan, hyaluronic acid, chromic cat gut, alginates, starch, cellulose, cellulose esters, blends and copolymers thereof, as well as other known degradable polymers.
  • Non-degradable polymers that can be used include, but are not limited to, polyesters (e.g., PET), polyurethanes, silicones, PE, PP, PS, PAA, PMA, silk, blends, copolymers thereof as well as other known polymers.
  • the threads used can be composed of a single composition or composed of a blend of differing compositions.
  • the polymeric threads themselves can be further modified through the addition of a polymeric coating applied to the threads.
  • the polymer used for coating the thread can be similar to that described above for the threads themselves.
  • the polymer coating may further comprise a biologically active agent that has the ability to induce a fibroproliferative response.
  • the agents that can be used are further described in the section (c) below.
  • the hydrogels described above can be utilized to deliver a particulate material that has the ability to induce a fibroproliferative response in the fallopian tube.
  • These particles can be either degradable or non-degradable and are similar to those described above for threads.
  • particulate materials useful for the practice of this embodiment include talc, starch, glass, silicates, silica, silver nitrate, ceramic particles and other inorganic particles known in the art to induce a fibroproliferative response.
  • the particles used in this embodiment can be all of the same composition or a blend of differing compositions. These particles can also be used as a coating applied to the polymeric strands as described above.
  • the hydrogel can also be constructed such that it is comprised of both polymeric threads and particles.
  • the threads and particles used are similar to those described above and may be of uniform composition or blended composition. Virtually any combination of threads of differing compositions and particles of differing compositions can be utilized in this embodiment.
  • the hydrogel, the polymeric threads, and the particles can all be utilized to deliver one or more biologically active agents, as described below.
  • the hydrogel can be formed into a variety of shapes and sizes for implantation into the fallopian tubes.
  • the hydrogel can be shaped into a rod of the desired length or subsequently cut to the appropriate length.
  • the hydrogel can be made into another shape and then further processed to form a rod of the appropriate dimensions.
  • the rods can be cylindrical in shape or they can have a tapered shape or an hourglass shape.
  • the hydrogel can also be formed into a rectangular shape by adding the appropriate reagents to a mould and then curing the composition.
  • a cork-borer type device of the appropriate dimensions can be used to produce rods.
  • the thickness of the initial hydrogel can determine if these rods have to be further cut into the appropriate lengths.
  • the rods can be then dehydrated by freeze drying or by air drying.
  • the freeze-dried rods may have more of a foam structure while the air dried rods may be of a more solid nature.
  • the particles and/or biologically active agents can be incorporated into the hydrogel prior to the curing stage.
  • the particles can be applied to the surface by rolling the rods in the particles or by applying the particles to the surface by dipping, spraying or painting.
  • the particles can be applied in combination with a coating polymer that may dissolve or degrade.
  • This coating polymer may be gelatin, hydroxypropyl cellulose, MePEG-PLA, MePEG-polyester, polyester-PEG-polyester, or the like.
  • the polymer threads can be added prior to the curing stage or they can be added after the hydrogel has cured.
  • the polymer threads can be added before or after the drying stage of the rods.
  • the threads may be wrapped around the external surface of the rod.
  • the needle may be used to pass the threads through the rod in a vertical, horizontal, diagonal manner or a combination thereof.
  • the threads may be placed such that they form loops protruding from the surface of the rod.
  • One specific composition comprises rods prepared from a methylated collagen-crosslinked poly(ethylene glycol) composition such as described above which has powdered silk particles added to the composition prior to curing. Once deployed, the rod can absorb water and thereby occlude the fallopian tube. This expansion can prevent the rod from moving, while the powdered silk can initiate a fibroproliferative response. As the methylated collagen-crosslinked poly(ethylene glycol) composition starts to degrade, the material can support the fibrous tissue ingrowth that is initiated and potentiated by the silk particles. To further increase the rate of initiation of this fibroproliferative response, a sclerosant such as a surfactant (SDS), ethanolamine oleate or DMSO can be added.
  • SDS surfactant
  • DMSO ethanolamine oleate
  • the amino PEG can provide a gel that can take a longer time to degrade and can provide some positive charge to further attract cellular material.
  • a second specific embodiment consists of an implant composed of silk fibers or from a polymerized version of the fibrosing agent itself (i.e., repeating units of the fibrosing agent polymerized together).
  • this embodiment can be performed in several ways including: (a) topical application of the fibrosing agent onto the luminal surface of the fallopian tube (particularly useful for this embodiment is the use of polymeric carriers which release the fibrosing agent over a period ranging from several hours to several weeks—fluids, suspensions, emulsions, microemulsions, microspheres, pastes, gels, microparticulates, sprays, aerosols, solid implants and other formulations which release a fibrosing agent can be delivered into the fallopian tube via specialized delivery catheters or other applicators); (b) microparticulate silk and/or silk strands (linear, branched, and/or coiled), either alone, or loaded with an additional fibrosis-inducing
  • a radio-opaque material such as tantalum, technetium, gadolinium, barium, other metal, or contrast material
  • the contrast agent may be a water soluble or water insoluble radio-opaque material.
  • the gel or the coated implant can contain air bubbles (e.g., ECHO-COAT) or air can be injected into the tube such that visualization by ultrasound is enhanced.
  • fibrosing agents for use in fallopian tube implants and devices include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, and CTGF, as well as analogues and derivatives of the aforementioned.
  • the device may alone or additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone.
  • the device may alone or additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • Drug dose can be calculated as a function of dose per unit area (of the portion of the device being coated), total drug dose administered can be measured and appropriate surface concentrations of active drug can be determined.
  • the exemplary fibrosing agents used alone or in combination, should be administered under the following dosing guidelines:
  • the total dose of talc delivered from a sterilization device, or coated onto the surface of a sterilization device should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of talc released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of talc as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • talc should be applied to a sterilization device surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • talc is released from the surface of a sterilization device such that fibrosis in the tissue is promoted for a period ranging from several hours to several months. For example, talc may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of talc (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as talc is administered at half the above parameters, a compound half as potent as talc is administered at twice the above parameters, etc.).
  • the total dose of silk delivered from a sterilization device, or coated onto the surface of a sterilization device should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of silk released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of silk as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • silk should be applied to a sterilization device surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release silk at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the sterilization device such that a minimum concentration of 0.01 nM to 1000 ⁇ M of silk is delivered to the tissue.
  • silk is released from the surface of a sterilization device such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • silk may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of silk (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as silk is administered at half the above parameters, a compound half as potent as silk is administered at twice the above parameters, etc.).
  • the total dose of chitosan delivered from a sterilization device, or coated onto the surface of a sterilization device should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of chitosan released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of chitosan as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • chitosan should be applied to a sterilization device surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • chitosan is released from the surface of a sterilization device such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • chitosan may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of chitosan (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as chitosan is administered at half the above parameters, a compound half as potent as chitosan is administered at twice the above parameters, etc.).
  • the total dose of polylysine delivered from a sterilization device, or coated onto the surface of a sterilization device should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of polylysine released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of polylysine as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • the dose per unit area of the device should fall within the range of 0.05 ⁇ g-10 ⁇ g per mm 2 of surface area coated.
  • polylysine should be applied to a sterilization device surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • polylysine As specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release polylysine at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the sterilization device such that a minimum concentration of 0.01 nM to 1000 ⁇ M of polylysine is delivered to the tissue.
  • polylysine is released from the surface of a sterilization device such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • polylysine may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of polylysine with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as polylysine is administered at half the above parameters, a compound half as potent as polylysine is administered at twice the above parameters, etc.).
  • the total dose of fibronectin delivered from a sterilization device, or coated onto the surface of a sterilization device should not exceed 100 mg (range of 1 ⁇ g to 100 mg). In one embodiment, the total amount of fibronectin released from the prosthesis should be in the range of 10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of fibronectin as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • fibronectin should be applied to a sterilization device surface at a dose of 0.05 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • fibronectin is released from the surface of a sterilization device such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • fibronectin may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of fibronectin (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as fibronectin is administered at half the above parameters, a compound half as potent as fibronectin is administered at twice the above parameters, etc.).
  • the total dose of bleomycin delivered from a sterilization device, or coated onto the surface of a sterilization device should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg). In one embodiment, the total amount of bleomycin released from the prosthesis should be in the range of 0.10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of bleomycin as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • bleomycin should be applied to a sterilization device surface at a dose of 0.005 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • bleomycin is released from the surface of a sterilization device such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • bleomycin may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of bleomycin with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as bleomycin is administered at half the above parameters, a compound half as potent as bleomycin is administered at twice the above parameters, etc.).
  • the total dose of CTGF delivered from a sterilization device, or coated onto the surface of a sterilization device should not exceed 100 mg (range of 0.01 ⁇ g to 100 mg). In one embodiment, the total amount of CTGF released from the prosthesis should be in the range of 0.10 ⁇ g to 50 mg.
  • the dose per unit area of the device i.e., the dosage of CTGF as a function of the surface area of the portion of the device to which drug is applied and/or incorporated
  • CTGF should be applied to a sterilization device surface at a dose of 0.005 ⁇ g/mm 2 -10 ⁇ g/mm 2 of surface area coated.
  • CTGF As specific (polymeric and non-polymeric) drug delivery vehicles and specific medical devices can release CTGF at differing rates, the above dosing parameters should be utilized in combination with the release rate of the drug from the a sterilization device such that a minimum concentration of 0.001 nM to 1000 ⁇ M of CTGF is delivered to the tissue.
  • CTGF is released from the surface of a sterilization device such that fibrosis in the tissue is promoted for a period ranging from several hours to several months.
  • CTGF may be released in effective concentrations for a period ranging from 1 hour-30 days.
  • analogues and derivatives of CTGF (as described previously) with similar functional activity can be utilized for the purposes of this invention; the above dosing parameters are then adjusted according to the relative potency of the analogue or derivative as compared to the parent compound (e.g., a compound twice as potent as CTGF is administered at half the above parameters, a compound half as potent as CTGF is administered at twice the above parameters, etc.).
  • the device may alone or additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone).
  • inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone.
  • Inflammatory cytokines are to be used in formulations at concentrations that range from 0.0001 ⁇ g/ml to approximately 20 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • the inflammatory cytokine is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 100 mg); preferred 0.001 ⁇ g to 50 mg.
  • the dose is per unit area of 0.0001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 10 -10 4 g/ml of inflammatory cytokine is to be maintained on the device surface.
  • the device may alone or additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • Doses used are those concentrations which are demonstrated to stimulate cell proliferation (Example 16).
  • the proliferative agents are to be used in formulations at concentrations that range from 0.01 ng/ml to 25 mg/ml depending on the specific clinical application, formulation type (e.g., gel, liquid, solid, semi-solid), formulation chemistry, duration of required application, type of medical device interface and formulation volume and or surface area coverage required.
  • formulation type e.g., gel, liquid, solid, semi-solid
  • formulation chemistry e.g., duration of required application
  • type of medical device interface e.g., aqueous containing formulation volume
  • formulation volume e.g., a coating thickness
  • the proliferative agent is released in effective concentrations for a period ranging from 1-180 days.
  • the total dose for a single application is typically not to exceed 500 mg (range of 0.0001 ⁇ g to 200 mg); preferred 0.001 ⁇ g to 100 mg.
  • the dose is per unit area of 0.00001 ⁇ g-500 ⁇ g per mm 2 ; with a preferred dose of 0.0001 ⁇ g/mm 2 -200 ⁇ g/mm 2 .
  • Minimum concentration of 10 ⁇ 11 -10 ⁇ 6 M of proliferative agent is to be maintained on the device surface.
  • any of the previously described fibrosis inducing agents, or derivatives and analogues thereof, can be utilized to create variations of the above compositions without deviating from the spirit and scope of the invention. It should also be apparent that the agent can be utilized in a composition with or without polymer carrier and that altering the carrier does not deviate from the scope of this invention.
  • vasectomy is a commonly used, highly effective method for the control of fertility.
  • a common vasectomy procedure involves injecting local anesthetic alongside the vas deferens, opening the scrotum with pointed dissecting forceps, pulling the vas through the puncture, and occluding or cutting the vas deferens (e.g., using a ligation technique in which the vas is ligatured at one or both ends with a suture, application of an implantable clip, or by cutting and/or cauterizing the vas).
  • vasectomy clips include those produced by Advanced Meditech International, Inc.
  • the incorporation of a fibrosis-inducing agent onto or into vasectomy sutures, clips, or implantable devices can promote fibrosis of the vas deferens, produce a more complete occlusion, and increase the success rate of the procedure.
  • the fibrosing agent can be mixed with the materials that are used to make the device such that the fibrosing agent is incorporated into the final structure of device itself.
  • a film or mesh that further comprises a fibrosis-inducing agent can be wrapped around the vas deferens or a cut portion of the vas deferens. This can promote fibrosis of the cut vas deferens and can increase the success rate of the procedure.
  • the fibrosis-inducing agent can be incorporated into an in situ forming gel composition. Following the application of a clip, ligation with a suture, or cutting of the vas deferens, the in situ forming composition can be applied to the treatment site (e.g., the cut end of the vas deferens) so as to promote fibrosis and increase the success rate of the procedure.
  • fibrosing agents for use in vas deferens implants and devices include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, and CTGF, as well as analogues and derivatives of the aforementioned.
  • the device may alone or additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone.
  • the device may additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • a particularly preferred embodiment of the present invention involves percutaneous delivery of a fibrosis-inducing agent in combination with a biomaterial designed for injection into the vas deferens to “plug” or obstruct the male reproductive tract.
  • the vas deferens is located by palpation (on both sides), a needle is inserted into the lumen, a guidewire is advanced into the lumen of the vas deferens, a dual lumen catheter (for many of the hydrogels described below such as materials prepared from a 4-armed thiol PEG (10K), a 4-armed NHS PEG(10K) and methylated collagen such as described above, COSEAL, COSTASIS, FLOSEAL, TISSEAL) or a single lumen catheter (for materials such as cyanoacrylate, hyaluronic acid, proteins, carbohydrates, sclerosing agents etc.) is advanced over the guidewire into the lumen of the vas deferens, the guidewire is removed, and a composition containing a fibro
  • Techniques can be used to enhance visualization of needle (or catheter) placement within the vas deferens including, but not limited to, the use of a needle coated with ECHO—COAT or the injection of air to enable localization by ultrasound, or the addition of contrast agents (e.g., barium, tantalum, technitium, gadolinium) for localization by x-ray or MRI.
  • the injectable implant can obstruct the vas deferens from the inside (luminal surface) and can be implanted in a conscious patient through a single (left and right) needle puncture-reducing the time required to perform the procedure, the invasiveness (a surgical incision is not required), and the risk of infection.
  • the biomaterial physically obstructs the lumen of the tube, while the fibrosis-inducing agent encourages the formation of scar tissue between adjacent walls of the vas deferens, leading to permanent obstruction of the lumen. This prevents the movement of sperm cells through the male reproductive tract, and can lower the failure rate of the procedure (measured as the prevention of unwanted pregnancies).
  • the injectable material may be composed of a hydrogel for use in the sterilization of a mammalian male.
  • the hydrogel can be composed of a non-degradable or a degradable material.
  • Non-degradable materials can include crosslinked compositions that comprise PVA, PVP, polyacrylamide, pHEMA, poly(vinyl PEG), poly(styrene sulfonate), poly(acrylic acid), poly(methacrylic acid), as well as other polymers that are known to form hydrogels. Additional compositions include blends and copolymers of the agents listed above.
  • Degradable materials include, but are not limited to, crosslinked materials of PEG, gelatin, collagen, hyaluronic acid, hyaluronic acid derivatives, polysaccharides, carbohydrates, proteins (e.g., albumin, casein, whey proteins, plant proteins, and fish proteins), cellulose derivatives (e.g., HPC), chitosan, chitosan derivatives, polyester-polyalkylene oxide block copolymers (e.g., PLGA-PEG-PLGA and MePEG-PLGA, etc) and other low molecular weight polymers that can be excreted.
  • proteins e.g., albumin, casein, whey proteins, plant proteins, and fish proteins
  • cellulose derivatives e.g., HPC
  • chitosan chitosan derivatives
  • polyester-polyalkylene oxide block copolymers e.g., PLGA-PEG-PLGA and MePEG-PLGA, etc
  • One material that is of particular interest is prepared from a 4-armed thiol PEG (10K), a 4-armed NHS PEG(10K) and methylated collagen such as described above.
  • the hydrogel may also contain a biologically active agent capable of inducing fibrosis in the vas deferens.
  • a biologically active agent capable of inducing fibrosis in the vas deferens.
  • Preferred, biologically active, fibrosis-inducing, agents, their dosages and their release kinetics, are all described in detail in section (c) below.
  • the hydrogel can be utilized to deliver a sclerosant to the vas deferens.
  • Sclerosants include compounds such as ethanol, DMSO, surfactants, sucrose, NaCl, dextrose, glycerin, minocycline, tetracycline, doxycycline, polidocanol, sodium tetradecyl sulfate, sodium morrhuate, sotradecol and others.
  • the hydrogel can further comprise agents such as glycerol, glycerin, PEG 200, triethyl citrate, and triacetin as plasticizers.
  • hydrogels described above can further modified to be comprised of, or contain, polymeric threads.
  • Polymeric threads have the ability to induce a fibroproliferative response from the surrounding tissue in the vas deferens. These polymer threads can be degradable or non-degradable.
  • Degradable threads can be composed of degradable polyesters, polyanhydrides, poly(anhydride esters), poly(ester-amides), poly(ester-ureas), polyorthoesters, polyphosphoesters, polyphosphazines, cyanoacrylate polymers, collagen, chitosan, hyaluronic acid, chromic cat gut, alginates, starch, cellulose, cellulose esters, blends and copolymers thereof, as well as other known degradable polymers.
  • Non-degradable polymers that can be used include, but are not limited to, polyesters (e.g., PET), polyurethanes, silicones, PE, PP, PS, PAA, PMA, silk, blends, copolymers thereof as well as other known polymers.
  • the threads used can be composed of a single composition or composed of a blend of differing compositions.
  • the polymeric threads themselves can be further modified through the addition of a polymeric coating applied to the threads.
  • the polymer used for coating the thread can be similar to that described above for the threads themselves.
  • the polymer coating may further comprise a biologically active agent that has the ability to induce a fibroproliferative response.
  • the agents that can be used are further described in the section (c) below.
  • the hydrogels described above can be utilized to deliver a particulate material that has the ability to induce a fibroproliferative response in the vas deferens.
  • These particles can be either degradable or non-degradable and are similar to those described above for threads.
  • particulate materials useful for the practice of this embodiment include talc, starch, glass, silicates, silica, silver nitrate, ceramic particles and other inorganic particles known in the art to induce a fibroproliferative response.
  • the particles used in this embodiment can be all of the same composition or a blend of differing compositions. These particles can also be used as a coating applied to the polymeric strands as described above.
  • the hydrogel can also be constructed such that it is comprised of both polymeric threads and particles.
  • the threads and particles used are similar to those described above and may be of uniform composition or blended composition. Virtually any combination of threads of differing compositions and particles of differing compositions can be utilized in this embodiment.
  • the hydrogel, the polymeric threads, and the particles can all be utilized to deliver one or more biologically active agents, as described below.
  • One specific composition comprises rods prepared from a methylated collagen-crosslinked poly(ethylene glycol) composition such as described above which has powdered silk particles added to the composition prior to curing. Once deployed, the rod can absorb water and thereby occlude the vas deferens. This expansion can prevent the rod from moving, while the powdered silk can initiate a fibroproliferative response. As the methylated collagen-crosslinked poly(ethylene glycol) material starts to degrade, the material can support the fibrous tissue ingrowth that is initiated and potentiated by the silk particles. To further increase the rate of initiation of this fibroproliferative response, a sclerosant such as a surfactant (SDS), ethanolamine oleate or DMSO can be added.
  • SDS surfactant
  • DMSO ethanolamine oleate
  • the amino PEG can provide a gel that can take a longer time to degrade and can provide some positive charge to further attract cellular material.
  • Another embodiment consists of an injectable implant composed of silk fibers or from a polymerized version of the fibrosing agent itself (i.e., repeating units of the fibrosing agent polymerized together).
  • the practice of this embodiment can be performed in several ways including: (a) injection of the fibrosing agent onto the luminal surface of the vas deferens (particularly useful for this embodiment is the use of polymeric carriers which release the fibrosing agent over a period ranging from several hours to several weeks-fluids, suspensions, emulsions, microemulsions, microspheres, pastes, gels, microparticulates, sprays, aerosols, solid implants and other formulations which release a fibrosing agent can be delivered into the vas deferens via specialized delivery catheters or other applicators); (b) microparticulate silk and/or silk strands (linear, branched, and/or coiled) either alone, or loaded with an additional fibrosis-inducing agent are also useful for directed injection into the vas deferens; (c) injectable collagen-containing formulations such as COSTASIS or materials prepared from a 4-armed thiol PEG (10K), a 4-armed NHS PEG(
  • a radio-opaque material such as tantalum, barium, other metal, or contrast material
  • the contrast agent may be a water soluble or water insoluble radio-opaque material.
  • fibrosing agents for use in vas deferens implants and devices include talc, silk, wool, chitosan, polylysine, fibronectin, bleomycin, and CTGF, as well as analogues and derivatives of the aforementioned.
  • the device may alone or additionally comprise an inflammatory cytokine (e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone).
  • an inflammatory cytokine e.g., TGF ⁇ , PDGF, VEGF, bFGF, TNF ⁇ , NGF, GM-CSF, IGF-a, IL-1, IL-1- ⁇ , IL-8, IL-6, and growth hormone.
  • the device may additionally comprise an agent that stimulates cellular proliferation.
  • agents include: dexamethasone, isotretinoin (13-cis retinoic acid), 17- ⁇ -estradiol, estradiol, 1-a-25 dihydroxyvitamin D 3 , diethylstibesterol, cyclosporine A, L-NAME, all-trans retinoic acid (ATRA), and analogues and derivatives thereof.
  • the exact dose administered can vary with device size, surface area and design. However, certain principles can be applied in the application of this art. Drug dose can be calculated as a function of dose per unit area (of the portion of the device being coated), total drug dose administered can be measured and appropriate surface concentrations of active drug can be determined. Regardless of the method of application of the drug to the sterilization device, the exemplary fibrosing agents, used alone or in combination, should be administered under the following dosing guidelines:

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US10/986,230 2003-11-10 2004-11-10 Medical implants and fibrosis-inducing agents Abandoned US20050148512A1 (en)

Priority Applications (71)

Application Number Priority Date Filing Date Title
US10/986,230 US20050148512A1 (en) 2003-11-10 2004-11-10 Medical implants and fibrosis-inducing agents
US10/996,353 US20050152941A1 (en) 2003-11-20 2004-11-22 Soft tissue implants and anti-scarring agents
CA002536242A CA2536242A1 (en) 2003-11-20 2004-11-22 Implantable sensors and implantable pumps and anti-scarring agents
EP04812062A EP1687041A2 (en) 2003-11-20 2004-11-22 Soft tissue implants and anti-scarring agents
JP2006541669A JP2007513650A (ja) 2003-11-20 2004-11-22 移植可能なセンサーおよび移植可能なポンプならびに瘢痕化抑制剤
PCT/US2004/039346 WO2005051232A2 (en) 2003-11-20 2004-11-22 Soft tissue implants and anti-scarring agents
PCT/US2004/039465 WO2005051444A2 (en) 2003-11-20 2004-11-22 Soft tissue implants and anti-scarring agents
US10/996,352 US20050158356A1 (en) 2003-11-20 2004-11-22 Implantable sensors and implantable pumps and anti-scarring agents
AU2004293075A AU2004293075A1 (en) 2003-11-20 2004-11-22 Soft tissue implants and anti-scarring agents
EP04811760A EP1687043A2 (en) 2003-11-20 2004-11-22 Electrical devices and anti-scarring agents
PCT/US2004/039353 WO2006055008A2 (en) 2003-11-20 2004-11-22 Implantable sensors and implantable pumps and anti-scarring agents
AU2004293030A AU2004293030A1 (en) 2003-11-20 2004-11-22 Electrical devices and anti-scarring agents
US10/996,355 US20050149157A1 (en) 2003-11-20 2004-11-22 Electrical devices and anti-scarring agents
PCT/US2004/039183 WO2005051483A2 (en) 2003-11-20 2004-11-22 Electrical devices and anti-scarring agents
PCT/US2004/039099 WO2005051451A2 (en) 2003-11-20 2004-11-22 Electrical devices and anti-scarring agents
CA002536188A CA2536188A1 (en) 2003-11-20 2004-11-22 Electrical devices and anti-scarring agents
CA002536192A CA2536192A1 (en) 2003-11-20 2004-11-22 Soft tissue implants and anti-scarring agents
AU2004293463A AU2004293463A1 (en) 2003-11-20 2004-11-22 Implantable sensors and implantable pumps and anti-scarring agents
JP2006541689A JP2007514472A (ja) 2003-11-20 2004-11-22 軟組織移植片および瘢痕化抑制剤
PCT/US2004/039387 WO2005051871A2 (en) 2003-11-20 2004-11-22 Implantable sensors and implantable pumps and anti-scarring agents
EP04817879A EP1685085A2 (en) 2003-11-20 2004-11-22 Implantable sensors and implantable pumps and anti-scarring agents
JP2006541598A JP2007516742A (ja) 2003-11-20 2004-11-22 電気装置と瘢痕化抑制剤
US10/998,351 US20050209665A1 (en) 2003-11-20 2004-11-26 Electrical devices and anti-scarring agents
US10/998,349 US20050209664A1 (en) 2003-11-20 2004-11-26 Electrical devices and anti-scarring agents
US10/998,350 US20050187600A1 (en) 2003-11-20 2004-11-26 Electrical devices and anti-scarring agents
US11/001,415 US20050181007A1 (en) 2003-11-20 2004-11-30 Soft tissue implants and anti-scarring agents
US11/001,421 US20060240063A9 (en) 2003-11-10 2004-12-01 Medical implants and fibrosis-inducing agents
US11/001,789 US20050181010A1 (en) 2003-11-20 2004-12-01 Implantable sensors and implantable pumps and anti-scarring agents
US11/001,416 US20050142162A1 (en) 2003-11-20 2004-12-01 Soft tissue implants and anti-scarring agents
US11/001,422 US20060240064A9 (en) 2003-11-10 2004-12-01 Medical implants and fibrosis-inducing agents
US11/001,787 US20050181009A1 (en) 2003-11-20 2004-12-01 Implantable sensors and implantable pumps and anti-scarring agents
US11/001,420 US20050169958A1 (en) 2003-11-10 2004-12-01 Medical implants and fibrosis-inducing agents
US11/004,671 US20050169960A1 (en) 2003-11-20 2004-12-02 Implantable sensors and implantable pumps and anti-scarring agents
US11/004,675 US20050169961A1 (en) 2003-11-20 2004-12-02 Implantable sensors and implantable pumps and anti-scarring agents
US11/004,673 US20050175657A1 (en) 2003-11-10 2004-12-02 Medical implants and fibrosis-inducing agents
US11/004,672 US20050175664A1 (en) 2003-11-20 2004-12-02 Implantable sensors and implantable pumps and anti-scarring agents
US11/006,902 US20050158274A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,906 US20050182496A1 (en) 2003-11-20 2004-12-07 Soft tissue implants and anti-scarring agents
US11/006,880 US20050186245A1 (en) 2003-11-20 2004-12-07 Implantable sensors and implantable pumps and anti-scarring agents
US11/006,893 US7166570B2 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,892 US20050187639A1 (en) 2003-11-20 2004-12-07 Soft tissue implants and anti-scarring agents
US11/006,882 US20050154374A1 (en) 2003-11-20 2004-12-07 Implantable sensors and implantable pumps and anti-scarring agents
US11/006,886 US20050147562A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,901 US20050181005A1 (en) 2003-11-20 2004-12-07 Implantable sensors and implantable pumps and anti-scarring agents
US11/006,898 US20050192647A1 (en) 2003-11-20 2004-12-07 Electrical devices and anti-scarring agents
US11/007,838 US20050152948A1 (en) 2003-11-20 2004-12-07 Soft tissue implants and anti-scarring agents
US11/006,884 US20050182467A1 (en) 2003-11-20 2004-12-07 Electrical devices and anti-scarring agents
US11/006,909 US20050203635A1 (en) 2003-11-20 2004-12-07 Soft tissue implants and anti-scarring agents
US11/006,910 US20060282123A1 (en) 2003-11-20 2004-12-07 Electrical devices and anti-scarring agents
US11/006,897 US20050186239A1 (en) 2003-11-20 2004-12-07 Implantable sensors and implantable pumps and anti-scarring agents
US11/006,883 US20050186246A1 (en) 2003-11-20 2004-12-07 Soft tissue implants and anti-scarring agents
US11/006,891 US20050182468A1 (en) 2003-11-20 2004-12-07 Electrical devices and anti-scarring agents
US11/006,894 US20050152946A1 (en) 2003-11-20 2004-12-07 Implantable sensors and implantable pumps and anti-scarring agents
US11/006,885 US20050209666A1 (en) 2003-11-20 2004-12-07 Electrical devices and anti-scarring agents
US11/006,907 US20050191248A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,881 US20050152944A1 (en) 2003-11-20 2004-12-07 Soft tissue implants and anti-scarring agents
US11/006,890 US20050182450A1 (en) 2003-11-20 2004-12-07 Electrical devices and anti-scarring agents
US11/006,887 US20050152945A1 (en) 2003-11-20 2004-12-07 Soft tissue implants and anti-scarring agents
US11/006,903 US20050152947A1 (en) 2003-11-20 2004-12-07 Soft tissue implants and anti-scarring agents
US11/006,904 US20050186247A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/007,837 US20050182469A1 (en) 2003-11-20 2004-12-07 Electrical devices and anti-scarring agents
US11/006,889 US20050147599A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/129,763 US7241736B2 (en) 2003-11-10 2005-05-12 Compositions and methods for treating diverticular disease
IL174640A IL174640A0 (en) 2003-11-20 2006-03-30 Compositions containing anti-scarring agents and soft tissue implants incorporating the same
IL174638A IL174638A0 (en) 2003-11-20 2006-03-30 Compositions containing anti-scarring agents and electrical devices incorporating the same
IL174639A IL174639A0 (en) 2003-11-20 2006-03-30 Compositions containing anti-scarring agents and implantable pumps and sensors incorporating the same
US11/431,427 US20070026043A1 (en) 2003-11-20 2006-05-09 Medical devices combined with diblock copolymer compositions
US11/775,816 US20070254833A1 (en) 2003-11-10 2007-07-10 Compositions and methods for treating diverticular disease
US12/425,316 US20090214652A1 (en) 2003-11-20 2009-04-16 Soft tissue implants and anti-scarring agents
US12/464,012 US20100092536A1 (en) 2003-11-20 2009-05-11 Implantable sensors and implantable pumps and anti-scarring agents
US12/703,679 US20100268288A1 (en) 2003-11-20 2010-02-10 Electrical devices and anti-scarring agents

Applications Claiming Priority (6)

Application Number Priority Date Filing Date Title
US51878503P 2003-11-10 2003-11-10
US52402303P 2003-11-20 2003-11-20
US52390803P 2003-11-20 2003-11-20
US57847104P 2004-06-09 2004-06-09
US58686104P 2004-07-09 2004-07-09
US10/986,230 US20050148512A1 (en) 2003-11-10 2004-11-10 Medical implants and fibrosis-inducing agents

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US10/986,231 Continuation-In-Part US20050181977A1 (en) 2003-11-10 2004-11-10 Medical implants and anti-scarring agents

Related Child Applications (16)

Application Number Title Priority Date Filing Date
US10/986,231 Continuation-In-Part US20050181977A1 (en) 2003-11-10 2004-11-10 Medical implants and anti-scarring agents
US10/996,352 Continuation-In-Part US20050158356A1 (en) 2003-11-20 2004-11-22 Implantable sensors and implantable pumps and anti-scarring agents
US10/996,355 Continuation-In-Part US20050149157A1 (en) 2003-11-20 2004-11-22 Electrical devices and anti-scarring agents
US10/996,353 Continuation-In-Part US20050152941A1 (en) 2003-11-20 2004-11-22 Soft tissue implants and anti-scarring agents
US11/001,420 Continuation US20050169958A1 (en) 2003-11-10 2004-12-01 Medical implants and fibrosis-inducing agents
US11/001,422 Continuation US20060240064A9 (en) 2003-11-10 2004-12-01 Medical implants and fibrosis-inducing agents
US11/001,421 Continuation US20060240063A9 (en) 2003-11-10 2004-12-01 Medical implants and fibrosis-inducing agents
US11/004,673 Continuation US20050175657A1 (en) 2003-11-10 2004-12-02 Medical implants and fibrosis-inducing agents
US11/006,902 Continuation US20050158274A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,907 Continuation US20050191248A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,889 Continuation US20050147599A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,904 Continuation US20050186247A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,886 Continuation US20050147562A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,893 Continuation US7166570B2 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/129,763 Continuation-In-Part US7241736B2 (en) 2003-11-10 2005-05-12 Compositions and methods for treating diverticular disease
US11/431,427 Continuation-In-Part US20070026043A1 (en) 2003-11-20 2006-05-09 Medical devices combined with diblock copolymer compositions

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US10/986,230 Abandoned US20050148512A1 (en) 2003-11-10 2004-11-10 Medical implants and fibrosis-inducing agents
US11/001,420 Abandoned US20050169958A1 (en) 2003-11-10 2004-12-01 Medical implants and fibrosis-inducing agents
US11/001,422 Abandoned US20060240064A9 (en) 2003-11-10 2004-12-01 Medical implants and fibrosis-inducing agents
US11/001,421 Abandoned US20060240063A9 (en) 2003-11-10 2004-12-01 Medical implants and fibrosis-inducing agents
US11/004,673 Abandoned US20050175657A1 (en) 2003-11-10 2004-12-02 Medical implants and fibrosis-inducing agents
US11/006,889 Abandoned US20050147599A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,902 Abandoned US20050158274A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,893 Expired - Fee Related US7166570B2 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,886 Abandoned US20050147562A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,907 Abandoned US20050191248A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,904 Abandoned US20050186247A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/129,763 Expired - Fee Related US7241736B2 (en) 2003-11-10 2005-05-12 Compositions and methods for treating diverticular disease
US11/775,816 Abandoned US20070254833A1 (en) 2003-11-10 2007-07-10 Compositions and methods for treating diverticular disease

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US11/001,420 Abandoned US20050169958A1 (en) 2003-11-10 2004-12-01 Medical implants and fibrosis-inducing agents
US11/001,422 Abandoned US20060240064A9 (en) 2003-11-10 2004-12-01 Medical implants and fibrosis-inducing agents
US11/001,421 Abandoned US20060240063A9 (en) 2003-11-10 2004-12-01 Medical implants and fibrosis-inducing agents
US11/004,673 Abandoned US20050175657A1 (en) 2003-11-10 2004-12-02 Medical implants and fibrosis-inducing agents
US11/006,889 Abandoned US20050147599A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,902 Abandoned US20050158274A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,893 Expired - Fee Related US7166570B2 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,886 Abandoned US20050147562A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,907 Abandoned US20050191248A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/006,904 Abandoned US20050186247A1 (en) 2003-11-10 2004-12-07 Medical implants and fibrosis-inducing agents
US11/129,763 Expired - Fee Related US7241736B2 (en) 2003-11-10 2005-05-12 Compositions and methods for treating diverticular disease
US11/775,816 Abandoned US20070254833A1 (en) 2003-11-10 2007-07-10 Compositions and methods for treating diverticular disease

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