US20070298071A1 - Bioactive scaffold for therapeutic and adhesion prevention applications - Google Patents

Bioactive scaffold for therapeutic and adhesion prevention applications Download PDF

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Publication number
US20070298071A1
US20070298071A1 US11/683,393 US68339307A US2007298071A1 US 20070298071 A1 US20070298071 A1 US 20070298071A1 US 68339307 A US68339307 A US 68339307A US 2007298071 A1 US2007298071 A1 US 2007298071A1
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scaffold
vivo
tissue layers
apposing
wound site
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US11/683,393
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Brendan Harley
Eric Soller
Eric Aiazian
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Axle International
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Axle International
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Assigned to AXLE INTERNATIONAL reassignment AXLE INTERNATIONAL ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: AIAZIAN, ERIC, HARLEY, BRENDAN A., SOLLER, ERIC C.
Publication of US20070298071A1 publication Critical patent/US20070298071A1/en
Priority to US12/725,656 priority patent/US8431146B2/en
Priority to US13/853,108 priority patent/US20130226313A1/en
Abandoned legal-status Critical Current

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/12—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
    • A61L31/125—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix
    • A61L31/129—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix containing macromolecular fillers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00—Medicinal preparations characterised by special physical form
    • A61K9/0012—Galenical forms characterised by the site of application
    • A61K9/0019—Injectable compositions; Intramuscular, intravenous, arterial, subcutaneous administration; Compositions to be administered through the skin in an invasive manner
    • A61K9/0024—Solid, semi-solid or solidifying implants, which are implanted or injected in body tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/14—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L31/146—Porous materials, e.g. foams or sponges
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P41/00—Drugs used in surgical methods, e.g. surgery adjuvants for preventing adhesion or for vitreum substitution

Definitions

  • the present invention relates to the prevention of undesired tissue adhesion generally, and more particularly to devices for inhibiting tissue adhesion through diversion of fibroblast activities.
  • the present invention further relates to methods and devices for therapeutic agent delivery, diagnostic agent delivery, and for promotion of tissue regeneration.
  • the serosa comprises the outermost layer of the visceral structures that lie in the pleural and peritoneal cavities of the human body; it consists of a surface epithelial layer called mesothelium and is typically reinforced by irregular fibroelastic tissue or stroma.
  • the serous cavities of the body are also lined by a single mesothelial layer of flattened cells (e.g. peritoneum, pleura, and pericardium).
  • fibrinolysis a component of the repair process that dissolves the fibrin matrix through the enzymatic action of plasmin. Both an inadequate blood supply and reduced tissue oxygenation are common in surgically traumatized tissue. Under these conditions, fibrinolytic activity is decreased and weak fibrinous bands, which often connect neighboring serosal surfaces, are allowed to persist under suppressed fibrinolysis. Over the 3 to 5 days following surgical injury, fibrinous bands gradually adopt and increase their cellularity, becoming organized by infiltrating fibroblasts via the deposition of collagen into strong fibrous bands, called adhesions.
  • Adhesions predominate in a wide variety of in vivo sites (including, but not limited to, the peritoneal, pleural, and pelvic cavities) with similar mechanisms.
  • ischemia from surgical repair grafting, suturing
  • the mechanical effects of handling grafting, suturing
  • the presence of foreign materials i.e. starch
  • Adhesion formation is a major complication of serosal repair following surgery, ischemia, or infection, and leads to conditions such as intestinal obstruction, severe abdominal pain, and infertility.
  • Intraperitoneal adhesions for example, occur in 67 to 93% of general abdominal surgeries and at an even higher rate following open gynecological pelvic surgeries.
  • adhesions present a significant burden to the health care system.
  • Postoperative adhesions often require additional surgical procedures to remove obstructions and may increase the risk, cost, and complexity of future operations.
  • pelvic-abdominal adhesiolysis operations are performed in US each year. When adhesiolysis is performed to remove an intestinal obstruction, adhesions form again and create a new obstruction in 11 percent to 21 percent of cases.
  • the annual cost of care for complications of post operative adhesions has been estimated to be $1.3 billion.
  • the fine threads of fibrin are invaded by fibroblasts and organized through the deposition of collagen into mature, strong, fibrous adhesions. It is clear that neighboring tissue structures will not form permanent adhesions unless they can achieve continuous, close apposition. In addition, the cellularity of the fragile fibrin matrix connecting two such structures seems to represent a critical factor in adhesion maturation. The extent of fibroblast invasion ultimately determines whether the fibrin bridge is absorbed or persists and is organized, forming an adhesion.
  • infection may be an important complication of the wound or injury healing.
  • antibiotics and other agents are widely used for the treatment or prophylactics of infection, mostly as a powder or a spray applied over the surgical wound area before the closure.
  • These methods of drug delivery are simple but have a disadvantage of very fast clearance of the drug from the treatment area to other areas and therefore suboptimal spatial and temporary drug concentration and distribution patterns in the cavity.
  • drug delivery formulations and devices suggested for the local drug delivery into the wound area are also is a wide variety of drug delivery formulations and devices suggested for the local drug delivery into the wound area.
  • a successful barrier temporarily prevents apposition of serosal tissue surfaces by separating the adhesiogenic tissue while the normal tissue repair process occurs. Subsequent degradation and clearance of the substance from the body prevents a foreign body response involving fibrosis of the implant or local toxicity.
  • An ideal barrier should be safe, effective, nonimmunogenic, noninflammatory, separate adhesiogenic tissue for the duration of the remesothelialization process, biodegrade, and remain functional in the presence of blood products. Further, the material should not interfere with the healing process, nor should it promote infection or abscess formation.
  • a number of adhesion prevention products have been approved by the U.S. Food and Drug Administration (FDA) for demonstrating an ability to reduce the incidence of scarring and adhesion formation following surgery (one example, approved in 1997, is SepraFilm®, which is a synthetic biodegradable membrane).
  • FDA U.S. Food and Drug Administration
  • SepraFilm® which is a synthetic biodegradable membrane
  • Anti-adhesion mechanical barriers that are commercially available are mostly synthetic polymeric membranes or films. Many of these products have demonstrated a degree of effectiveness but have several common drawbacks with regard to surgical use or clinical complications.
  • SepraFilm® carboxymethylcellulose/hyaluronic acid
  • Interceed® oxidized regenerated cellulose
  • Gore-tex Surgical Membrane® requires meticulous hemostasis in order to function properly and the material is prone to retention at the tissue surface.
  • Scaffolds are a relatively new class of biomaterials that are utilized widely in applications of regenerative medicine. They are highly porous, degradable macromolecular solids with specific microstructural characteristics. Following irreversible injury (injury of a severe enough nature that under normal spontaneous repair processes would result in scar, or non-physiological, tissue formation), scaffolds of highly specific structure and chemical composition have been shown to induce partial regeneration in several organs, notably skin and the peripheral nerves.
  • Induced organ regeneration or the recovery of physiological structure and function of non-regenerative tissues at the original site of injury (de novo synthesis) was accomplished using scaffolds that simultaneously blocked myofibroblast-generated contraction (the dominant method of spontaneous wound closure in adults) while mimicking the in vivo extracellular matrix environment (particularly the stroma) of the organ of interest.
  • Graft co-polymers of type I collagen and a glycosaminoglycan that were shown to actively block contraction in skin wounds (and induce regeneration) have structural properties that accomplish three main processes: 1) reduction of TGF- ⁇ in the wound site, leading to downregulation of fibroblast (and contractile myofibroblast) recruitment following severe injury; 2) blocking orientation of myofibroblast axes in the plane of the defect where macroscopic contraction is observed; and 3) ensuring that the scaffold's contraction blocking properties persist for the duration of the interim myofibroblast contractile response but not so long as to interfere with key regenerative processes.
  • chondroitin-6-sulfate chondroitin-6-sulfate
  • collagen-GAG copolymers are effective templates for regeneration of the dermis, peripheral nerve, and conjunctiva and show promise in cartilage repair studies.
  • the use of these analogs of the extracellular matrix has been linked to partial regeneration of the above organs, elimination of scar tissue, and a clear ability to block the contraction of fibroblasts in the wound site.
  • these matrices are widely used as substrates to probe the local environment of connective tissue cell-mediated contraction and specifically, myofibroblast-mediated contraction.
  • These scaffolds successfully induce tissue regeneration and impart contraction-blocking activity by altering the local environment of the contractile cells (fibroblasts) responsible for tissue contraction and scar formation.
  • a device for inhibiting such adhesion of apposing human body tissue layers, wherein the device includes a scaffold that is prepared by co-precipitation of collagen and a glycosaminoglycan, followed by lyophilization.
  • the device for inhibiting adhesion of apposing human body tissue layers may include a scaffold having a mean pore size of between about 5 and about 200 ⁇ m, a relative density of between about 0.5 and about 10%, and a degradation half-life of 1-6 weeks when disposed in vivo.
  • a device for the promotion of tissue regeneration, and particularly the regeneration of internal organ tissue.
  • the scaffold device of the invention may include a dispensable therapeutic agent for dispensation within the body.
  • a dispensable therapeutic agent for dispensation within the body.
  • Such dispensation may, for example, be directed over time to an injured body tissue so as to promote efficient regeneration thereof.
  • the device of the invention may be utilized by being operably positioned between the apposing tissue layers, and acts to inhibit formation of fibrous adhesions by promoting contractile cell migration away from the wound site for a predetermined period of time.
  • the scaffold device of the invention may include a diagnostic agent that may or may not be dispensed from the scaffold.
  • a diagnostic agent may be, for example, a radioactive marker material, an ultrasonic marker material, a magnetic marker material, and the like.
  • FIG. 1 is a perspective view of a scaffold device of the present invention
  • FIG. 2 is a magnified view of a scaffold device of the present invention.
  • FIG. 3 is a magnified view of a scaffold device of the present invention.
  • scaffolds that, by virtue of possessing novel, specific features, are capable of reducing the formation of fibrous adhesions after any type of internal injury by serving as a degradable, bioactive barrier (substances that physically prevent apposition of adjacent adhesiogenic and serosal surfaces while remesothelialization occurs).
  • the bioactive nature of the scaffold additionally modifies the local environment and behavior of the contractile cells responsible for fibrous adhesion maturation and scar formation, mediating the organized wound contraction and aiding in the wound healing process in a manner which previously described barrier products and membranes do not.
  • the therapeutic anti adhesive scaffold (TAS) of the invention significantly reduces adhesion formation by actively promoting fibroblast migration away from the wound site (adhesiogenic surfaces, e.g. suture lines) and into the TAS.
  • a TAS scaffold 1 has an upper portion 3 including an upper surface 5 and a lower portion 4 including a lower surface 6 .
  • lower surface 6 is placed into contact with the target tissue surface (such as the injured tissue).
  • the target tissue surface such as the injured tissue
  • exudate and cell flow from the injured tissue flows into TAS scaffold 1 generally in the direction illustrated by arrow 8 .
  • TAS scaffold 1 may be provided with a releasable therapeutic agent, wherein such therapeutic agent may be released in a predetermined manner from TAS scaffold 1 .
  • Such therapeutic agent release may, for example, include release in the direction of arrow 9 to an injured tissue surface.
  • the structure of the scaffold allows it to serve as a depot for one or more therapeutic agents, for example by immersing the scaffold into the therapeutic agent instead of pure saline solution before implantation.
  • the therapeutic agent may also be incorporated with the scaffold through chemical bonding or other techniques which provide at least temporary adherence of the therapeutic agent to or within the scaffold structure.
  • the structure of the TAS may be modified in such a way that the lower part of the TAS that comes into contact with the injured surface has higher permeability than the upper part and thus allows preferential optional therapeutic agent outflow from the TAS into the underlying wound area and inflow of exudate and cells through the lower part of TAS into the scaffold structure.
  • the TAS scaffold of the present invention may additionally or instead at least temporarily retain a diagnostic agent thereat.
  • Diagnostic agents may include, for example, materials that aid in remotely diagnosing conditions within the body. Such materials may include, for example, radioactive marker materials, magnetic marker materials, ultrasonic marker materials, and the like.
  • the diagnostic materials contemplated for use in connection with the scaffold structure of the invention may optionally be dispensable from the structure, but may instead be retained at the scaffold for a predetermined period of time, including for example, the duration of the lifespan of the scaffold.
  • Such diagnostic materials may aid in the monitoring of the physical condition of the scaffold, the extent of degradation of the scaffold, the extent of healing of damaged tissue, or other conditions throughout the body.
  • TAS scaffold 1 involving a dispensable agent whether therapeutic, diagnostic, or both, such dispensation may be accomplished in a predetermined manner.
  • the dispensation of the respective agent or agents may be accomplished over a predetermined period of time at homogeneous or heterogeneous rates.
  • modifications to the scaffold structure and/or the use of various binding agents, suspensions, solvents, or other materials can customize the rates of agent dispensation.
  • dispensation may be controlled as a function of the rate of scaffold biodegradation. It is to be further understood that various modifications may be made to TAS scaffold 1 in order to alter the degradation rate of the scaffold structure as a whole, or for only a portion of the scaffold structure.
  • the therapeutic and/or diagnostic agent release may be coordinated with the biodegradation of part or all of the scaffold structure.
  • TAS scaffold 1 may be constructed in a variety of shapes and dimensions, one useful embodiment of TAS scaffold 1 may have a thickness dimension “T” of between about 0.1 and 10 mm. TAS scaffold 1 may also be dimensioned to superimpose the region of injured tissue. In addition, some embodiments of TAS scaffold 1 may have a Young's modulus value in a dry condition of between about 25-35 KPa. In hydrated form, one embodiment of TAS scaffold 1 may have a Young's modulus value of between about 0.1-0.5 KPa. While the above values for elasticity of the scaffold structure have been demonstrated to be useful, it should be understood that such values are not limiting to the structure of the present invention.
  • the mechanism for adhesion prevention is as follows.
  • the TAS constitutes a barrier to adhesion formation by preventing the close, continuous contact of adhesiogenic surfaces through its placement over the area of surgical repair, thereby preventing the fibrin gel matrix from connecting neighboring structures.
  • the TAS persists in its active state for a pre-determined time period that matches the remesothelialization phase and the duration of the fibroblast response during adhesion maturation before degrading completely through the body's normal enzymatic activity.
  • the TAS prevents adhesion formation by modifying the native behavior of fibroblasts at the wound site, the protagonist cell in the crucial step of fibrous adhesion maturation and scar formation.
  • the material is highly porous and possesses an interconnected open pore microarchitecture that is well-suited for fibroblast migration and remodeling. Fibroblasts, originally recruited to the site of surgical repair through the spontaneous healing response (cytokines and the inflow of inflammatory exudate) recognize and bind avidly to the collagen ligands of the TAS, eventually migrating into and remodeling the TAS.
  • Inflammatory exudate and blood products infiltrate the scaffold without compromising its function, bringing additional oxygen and nutrients into the porous structure, and further driving migration and persistence of fibroblasts in the scaffold for the period of time that the scaffold is active in the wound site prior to degradation.
  • the pore volume fraction of the TAS is such that a very large number of ligands, or areas for fibroblast attachment, are present. Duration of the TAS in an undegraded state for the first 14 days after injury prevents apposition of the serosal tissues until such time that normal repair has occurred and the fibroblast response has been blocked.
  • the TAS has the potential to improve the quality of regeneration at the site of the surgically repaired defect and reduce macroscopically-observed post-surgical organ deformation.
  • the net migration of contractile fibroblasts out of the plane of the defect and into the TAS reduces the incidence of contraction and scar synthesis at the wound site.
  • the observed migration of myofibroblasts out of the wound plane and into a collagen-GAG copolymer scaffold has corresponded to an increase in the quality of regeneration of several organs.
  • the TAS is a highly porous, three-dimensional thin sheet or “scaffold” that is prepared by co-precipitation of collagen and a glycosaminoglycan (e.g. chondroitin-6-sulfate), followed by lyophilization.
  • a glycosaminoglycan e.g. chondroitin-6-sulfate
  • the relevant properties of the TAS can be modified by adjusting the chemical composition, pore size, pore volume fraction, degree of cross-linking, and TAS thickness to yield a scaffold variant that is designed to suit the specific needs of a wide array of wound sites.
  • the initial incarnation of the TAS scaffold is a collagen-glycosaminoglycan (GAG) scaffold with a mean pore size between 5 and 200 ⁇ m, preferably between 20 and 150 ⁇ m; relative density of 0.5-10%, preferably 0.5-5%; and a degradation half life of 1-6 weeks, preferably 1-4 weeks.
  • GAG collagen-glycosaminoglycan
  • Collagen-GAG scaffolds can be crosslinked using a variety of methods that impart sterility and control over the in vivo degradation rate of the scaffolds, or alternatively can be sterilized by any number of processes including, but not limited to, ethylene oxide treatment, or gamma radiation.
  • the TAS can be stored in a desiccated environment for extended periods of time without a decrease in bioactivity, making the TAS appropriate for large-scale fabrication and distribution. Processing conditions readily allow additional modification of micro-structural, compositional, and mechanical properties of the TAS.
  • the TAS scaffold can be readily cut in the operating theater so that the surgeon can fit the scaffold to a particular wound or surgical site.
  • TAS therapeutic anti adhesive scaffold
  • Sterile, hydrated sections of scaffold (hydrated in phosphate buffered saline solution, 30 minutes; a drug may be added to the solution at the discretion of the physician for the delivery to the wound site) that have been cut to the required size and shape are applied by the surgeon on the cecal suture line and under the laparatomy incision prior to surgical closure of the abdomen and sutured in place, ensuring close contact with the underlying adhesiogenic surface.
  • the physical properties of the TAS are such that it may be simply applied to the site or if necessary fixed in place using variety of methods including, but not limited to, suturing, stapling, or gluing without detriment to its structural integrity or adhesion-prevention function.
  • the porous TAS becomes bathed in residual inflammatory exudates from the surgical repair and the peritoneal closure and become invaded with fibroblasts which recognize and bind avidly to the collagen ligands of the scaffold.
  • Fibroblasts remodel the TAS for a period of 5-7 days, approximately matching the duration of the remesothelialization process.
  • the TAS remains intact, providing a mechanical barrier and preventing continuous, close apposition between the colonic wound site and the regenerating mesothelium of the peritoneal wall.
  • the half life of the TAS is such that it accomplishes regeneration of mesothelial layers without formation of fibrous adhesions or a chronic foreign body response (e.g.
  • the degradation characteristics of the TAS can be modified by variable cross-linking without significantly modifying the microarchitecture or mechanical characteristics of the scaffold, such that complete degradation times of substantially less than one week, or up to one year or more, may be obtained.
  • the degradation of the TAS may be optionally homogeneous or heterogeneous, wherein one or more portions of the TAS may degrade at respectively different rates, and/or may respectively degrade to various extents.
  • the TAS may be modified to have an area with properties that differ from the rest of the TAS. These modifications include but are not limited to increased thickness and increased density. These may be particularly used for fixing the scaffold in place as well as maintaining the shape of the scaffold and modifying its depot qualities.
  • TAS When required by the surgeon (such as in the case of severe injury to both apposing tissue layers), multiple pieces of TAS may be used simultaneously (e.g. one TAS may be applied to each of two apposing tissue surfaces).
  • the TAS microarchitecture may be modified such that one side of the TAS is more bioadhesive than the other side. This ensures the TAS will prevent adhesion formation and decreases the likelihood of two apposing pieces of TAS from adhering to each other.
  • the TAS may be provided with any number of a wide range of therapeutic agents, including, but not limited to, antibiotics, cytokines, cytostatic agents, fibrinolytic agents, corticosteroids, and non-steroidal anti-inflammatory drugs, prior to implantation.
  • therapeutic agents including, but not limited to, antibiotics, cytokines, cytostatic agents, fibrinolytic agents, corticosteroids, and non-steroidal anti-inflammatory drugs, prior to implantation.
  • the porous nature of the TAS allows it to hold liquid agents much in the way a traditional sponge holds water and deliver them to the area of injury over time.
  • the TAS comprises a biodegradable implant that, when placed or grafted between apposing serosal layers of adhesiogenic tissue, reduces the incidence and severity of fibrous adhesion formation between these tissues
  • these therapeutic anti adhesive scaffolds possess the following features:
  • the TAS represents a barrier to adhesion formation with an inherent capacity to prevent the close, continuous contact of adhesiogenic tissue and other serosal layers.
  • the bioactive nature of the TAS reduces irreversible components of the normal healing response (fibrous adhesion and scar formation) while promoting regeneration of mesothelial layers and reducing macroscopically observed organ deformation.
  • the structural and chemical properties of the TAS modify the local extracellular environment and influence behavior of the contractile cells responsible for fibrous adhesion maturation and scar formation in a specific manner which previously described barrier membranes do not.
  • the TAS significantly reduces adhesion formation by actively promoting fibroblast migration away from the wound site (adhesiogenic surfaces, e.g. suture lines) and into the porous TAS.
  • the TAS is a generic adhesive barrier scaffold with therapeutic properties that can be applied in response to injury in the human body resulting from processes including, but not limited to, surgical or traumatic injury, inflammation, and infection.
  • the TAS may be applied at multiple sites including, but not limited to: organs of the peritoneal cavity, pericardium, pleural cavity, pelvic cavity, tendons, and nerves.
  • the TAS has a three-dimensional shape and mechanical properties such that it is an optimal type of implant for surgical application (e.g. pliable, sheet form, elastic properties). These properties allow the TAS to be modified easily in the operating room theater (e.g. trimmed to fit specific shapes and sizes).
  • the structure of the implant is a highly porous scaffold fabricated through, for example, a co-precipitation reaction of collagen and possibly a glycosaminoglycan followed by lyophilization.
  • Other fabrication techniques may be employed for the development of a scaffold structure.
  • a porous scaffold structure may be fabricated from collagen alone, or from collagen-GAG with various cross-linking agents.
  • TAS All components of the TAS are naturally occurring structural materials of the human body that are degraded and cleared from the site of implantation through normal enzymatic action (collagenases).
  • the chemical composition, pore structure, pore size, pore volume fraction, degradation rate, degradation homogeneity, thickness, and elasticity of the scaffold can be readily modified to yield an implant with a geometric structure that can be individually tailored to one of many physiological wound sites.
  • the initial incarnation of the TAS scaffold is a collagen-glycosaminoglycan (GAG) copolymer scaffold with a mean pore size between 5 and 200 ⁇ m, preferably between 20 and 150 ⁇ m; relative density of 0.5-10%, preferably 0.5-5%; and a degradation half life of 1-6 weeks, preferably 1-4 weeks.
  • GAG collagen-glycosaminoglycan
  • the TAS may be uniform in structure or developed in such a way that the sides or certain areas of it have different properties including, but not limited to, local areas of modified density, pore size, degradation rates, elasticity, and thickness. These may be particularly used for fixing the scaffold in place as well as maintaining the shape of the scaffold.
  • the TAS may be provided with therapeutic and/or diagnostic agents, including, but not limited to, antibiotics, cytokines, non-steroidal anti-inflammatory drugs, fibrinolytic agents, and corticosteroids, prior to implantation.
  • therapeutic and/or diagnostic agents including, but not limited to, antibiotics, cytokines, non-steroidal anti-inflammatory drugs, fibrinolytic agents, and corticosteroids.
  • the porous nature of the TAS allows it to hold liquid agents much in the way (but not limited to) a traditional sponge holds water and deliver them to various areas of the body, such as to the area of injury.
  • the structure of the TAS may be modified in such a way that the lower part of the TAS that comes in a contact with the injured surface has higher permeability than the upper part and thus allows preferential optional therapeutic agent outflow from the TAS into the underlying wound area and inflow of exudate and cells through the lower part of TAS into the scaffold structure ( FIG. 1 ).
  • the TAS is constructed from components and subjected to processing conditions that render it both nonimmunogenic and nonantigenic.
US11/683,393 2006-03-07 2007-03-07 Bioactive scaffold for therapeutic and adhesion prevention applications Abandoned US20070298071A1 (en)

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US11/683,393 US20070298071A1 (en) 2006-03-07 2007-03-07 Bioactive scaffold for therapeutic and adhesion prevention applications
US12/725,656 US8431146B2 (en) 2006-03-07 2010-03-17 Scaffold comprising co-precipitated Collgen and glycosaminoglycan for inhibiting adhesion of body tissue layers
US13/853,108 US20130226313A1 (en) 2006-03-07 2013-03-29 Bioactive Scaffold for Therapeutic and Adhesion Prevention Applications

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US9512192B2 (en) 2008-03-27 2016-12-06 Purdue Research Foundation Collagen-binding synthetic peptidoglycans, preparation, and methods of use
US10772931B2 (en) 2014-04-25 2020-09-15 Purdue Research Foundation Collagen binding synthetic peptidoglycans for treatment of endothelial dysfunction
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ITRM20130674A1 (it) * 2013-12-06 2015-06-07 Giada Maria Manti Utilizzo di sostituti dermici per la prevenzione della sindrome aderenziale

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