US20180193537A1 - Elastic antimicrobial film and socket made therefrom - Google Patents

Elastic antimicrobial film and socket made therefrom Download PDF

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Publication number
US20180193537A1
US20180193537A1 US15/563,527 US201615563527A US2018193537A1 US 20180193537 A1 US20180193537 A1 US 20180193537A1 US 201615563527 A US201615563527 A US 201615563527A US 2018193537 A1 US2018193537 A1 US 2018193537A1
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Prior art keywords
antibiotic
minocycline
rifampicin
layers
film
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US15/563,527
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English (en)
Inventor
Wang Honglei
Luo Jingnan
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Foundry Therapeutics Inc
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Orchid Medical Pte Ltd
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Assigned to ORCHID MEDICAL PTE LTD reassignment ORCHID MEDICAL PTE LTD ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: HONGLEI, WANG, JINGNAN, LUO
Assigned to ORCHID MEDICAL PTE LTD reassignment ORCHID MEDICAL PTE LTD ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: LUO, Jingnan, WANG, Honglei
Publication of US20180193537A1 publication Critical patent/US20180193537A1/en
Assigned to FOUNDRY THERAPEUTICS, INC. reassignment FOUNDRY THERAPEUTICS, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: ORCHID MEDICAL PTE LTD
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
    • A61L31/14—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L31/16—Biologically active materials, e.g. therapeutic substances
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K31/00—Medicinal preparations containing organic active ingredients
    • A61K31/33—Heterocyclic compounds
    • A61K31/395—Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins
    • A61K31/495—Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins having six-membered rings with two or more nitrogen atoms as the only ring heteroatoms, e.g. piperazine or tetrazines
    • A61K31/496—Non-condensed piperazines containing further heterocyclic rings, e.g. rifampin, thiothixene or sparfloxacin
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K31/00—Medicinal preparations containing organic active ingredients
    • A61K31/65—Tetracyclines
    • 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
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/54—Biologically active materials, e.g. therapeutic substances
    • 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
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/58—Materials at least partially resorbable by the body
    • 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
    • A61L31/04—Macromolecular materials
    • A61L31/041—Mixtures of macromolecular compounds
    • 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
    • A61L31/04—Macromolecular materials
    • A61L31/06—Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
    • 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
    • A61L31/148—Materials at least partially resorbable by the body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372—Arrangements in connection with the implantation of stimulators
    • A61N1/375—Constructional arrangements, e.g. casings
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P31/00—Antiinfectives, i.e. antibiotics, antiseptics, chemotherapeutics
    • 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
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/40—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
    • A61L2300/402—Anaestetics, analgesics, e.g. lidocaine
    • 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
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/40—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
    • A61L2300/404—Biocides, antimicrobial agents, antiseptic agents
    • 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
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/40—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
    • A61L2300/404—Biocides, antimicrobial agents, antiseptic agents
    • A61L2300/406—Antibiotics
    • 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
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/60—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special physical form
    • A61L2300/602—Type of release, e.g. controlled, sustained, slow
    • 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
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/60—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special physical form
    • A61L2300/602—Type of release, e.g. controlled, sustained, slow
    • A61L2300/604—Biodegradation

Definitions

  • the present invention relates to an antibiotic article that prevents infection associated with the implantation of medical devices.
  • CIEDs cardiovascular implantable electronic devices
  • a pouch to contain the CIED has been developed with the aim to create a stable environment when implanted in the body.
  • a typical pouch used for this role is sealed at three sides and has a single opening for placing the device into said pouch.
  • CMS Centers for Medicare & Medicaid Services
  • An antimicrobial article that can be attached to, or wraps around the surface of, an implantable medical device may help to reduce, prevent, or mitigate infection by eluting antimicrobial agents over time into the surrounding environment of the medical device.
  • the TYRX Absorbable Antibacterial Envelope is a mesh with large pores that is knitted from absorbable filaments (a polymer made of glycolide, caprolactone, and trimethylene carbonate) and is coated with an absorbable polyarylate polymer.
  • absorbable filaments a polymer made of glycolide, caprolactone, and trimethylene carbonate
  • the absorbable polymer coating contains two antimicrobial agents: minocycline and rifampicin.
  • the envelope/pouch used in said devices has an opening that is usually bigger than the CIED to be inserted, which results in the potential risk of the CIED falling out.
  • these devices are designed to cater to numerous sizes of CIED, which increases the risk of smaller CIEDs falling out due to the relative rigidity and inelasticity of the material. Hence, there is a need for a new and improved design and structure that can securely hold CIEDs of various sizes.
  • the articles described above go some way to dealing with infections, there are issues with the use of these antimicrobial articles.
  • the articles described above often coat both agents together on the surface, or impregnate both agents within a material, and cannot control the release of both agents together, especially when both agents have differing hydrophilicity values, as is the case with Rifampin and Minocycline.
  • it is important to control the release of both agents so that they provide the required concentration of active agent over the required period of time.
  • antimicrobial agents coated on the surface tend to be released easily, and thus there is minimal control on the rate of release of the antimicrobial agent over an extended period of time. Therefore, there is a need for an improved antibiotic article.
  • a soft and elastic biodegradable controlled-release antibiotic socket e.g. a sleeve or band
  • a socket i.e. a sleeve, band or pocket
  • the socket and its openings can be stretched to a size larger than the object to be inserted to enable ease of insertion of said device.
  • the elastic biodegradable controlled-release antibiotic socket is intended to hold a cardiac implantable electronic device (CIED) securely in order to provide a stable environment when implanted in the body; and reduce, prevent, or mitigate infection by releasing at least one antimicrobial agent during and/or after implantation in a controlled manner.
  • the drug release is controlled by the choice of polymer, the addition of layers, tuning of the thickness of various layers, and the use of releasing agents.
  • controlled-release antibiotic socket for securely holding an implantable medical device, comprising:
  • At least one film made from at least one polymer layer, where the at least one film is formed into the socket; at least one antibiotic agent; and at least one opening in the socket, wherein
  • the socket may be in the form of a pocket with at least one opening or a sleeve/band with at least two openings. It will be further appreciated that for the socket to securely hold an implantable medical device, the socket made from the elastomeric material is smaller than the medical device to be inserted into it. This may result in the socket securely holding the medical device (e.g. a CIED device) by a resilient holding force generated from the elastomeric polymeric material that makes up the film.
  • the medical device e.g. a CIED device
  • a controlled-release antibiotic film made from at least one polymer layer for securely holding an implantable medical device, the film comprising at least one polymer layer that is made from a biodegradable elastomeric polymeric material; and at least one antibiotic agent is dispersed within at least one of the at least one polymer layers and/or, when the film comprises at least two polymer layers, the at least one antibiotic agent is disposed as a separate layer between two polymer layers.
  • the socket (and hence the openings) are stretchable to at least 1.1 times (e.g. from 1.2 times to 10 times) to allow for insertion of the CIED into the socket, and can recover to more than 80% to securely hold the CIED within the socket and prevent fall off.
  • a construction of the article that may be mentioned herein comprises at least one film, which itself comprises at least one polymer layer and at least one antimicrobial agent; and at least one opening and numerous holes on the surface.
  • the film has seven layers, such that there is a top, top-intermediate, top-middle-intermediate, middle, bottom-middle-intermediate, bottom-intermediate and bottom polymer layer, where the middle layer consists only of polymeric material, the top-middle-intermediate and bottom-middle-intermediate layers consist of at least one antibiotic (e.g. the at least one antibiotic is minocycline and/or rifampicin), the top-intermediate and bottom-intermediate layers comprise a polymeric material and a releasing agent, and the top and bottom layers each comprise a polymeric material and at least one further antibiotic (e.g.
  • the at least one antibiotic is minocycline and/or rifampicin) dispersed therein, optionally wherein, when the top-middle-intermediate and bottom-middle-intermediate polymer layers contain rifampicin, the top and bottom polymer layers contain minocycline dispersed therein or vice versa; or
  • the term “at least one antibiotic” in relation to a film or socket made therefrom having more than one layer, it may refer to the use of the same (or same mixture of) antibiotic in all layers that contain an antibiotic, and/or to different antibiotics (and/or to different mixtures of antibiotics) in layers of the film or socket made therefrom.
  • the implantable medical device may be a cardiovascular implantable electronic device (CIED).
  • CIED cardiovascular implantable electronic device
  • the film may be used to cover at least part of the surface of a medical device that is then implanted into a subject.
  • an implantable medical device comprising a medical device and socket as set out in the first aspect of the invention (and its various embodiments, whether alone or in any suitable combination), wherein the film covers a part or the whole of the medical device and is suitable for reducing or preventing migration of the medical device within the body following implantation.
  • the film may be provided in the shape of an envelope or pouch to surround part or whole of the medical device.
  • the device may further comprise an additional active agent (e.g. a growth factor, an anti-inflammatory, or anaesthetic agent) coated onto whole or part of an exposed surface of the film.
  • a process for making a socket or film as set out in the first and second aspects of the invention wherein when the socket is made from a film having two or more polymer layers or the film has two or more polymer layers, the film is prepared by the use of one or more of heat-melting, heat-compression, spray coating, dip coating, chemical grafting, electrostatic adsorption, chemical crosslinking to join the polymer layers together.
  • FIGS. 1 to 3 depict schematic illustrations of an article designed according to an embodiment of the invention (a socket to surround a medical device) with holes.
  • FIGS. 4-1 to 4-7 depict examples of layered designs according to embodiments of the current invention.
  • FIG. 5 depicts the cumulative release profile of minocycline (5-1) and rifampin (5-2) in the exemplified embodiments of the invention.
  • FIG. 6 depicts the cumulative release profile of minocycline and rifampin in a single film according to an embodiment of the current invention.
  • FIG. 7 depicts a tensile curve of an article.
  • the antibiotic socket of the current invention relates to a socket made from an elastic film material (comprising one or more elastomeric polymer layers), with at least one opening in the socket.
  • the socket is smaller than the objects it is intended to hold and so it is stretched to a size to permit the object to be inserted and then recovers towards its original size (due to the elastic material that is made from), such that it securely holds the object inserted thereto (e.g. resiliently engages, holds or secures the object).
  • the secure/resilient securing of the object inserted significantly reduces the possibility of the CIED falling out.
  • the socket (or the film the socket is made from) may also have a rough surface, which aids in securing the object to the socket and may also help the socket secure the object following implantation into the body.
  • the rough surface may also prevent the film/socket made therefrom from becoming adhered to a surface (i.e. sticking to a surface), for example the roughness may ensure that the inner surfaces of the socket do not stick to each other and thereby enables easy opening of the socket to insert a device.
  • the socket (or the film the socket is made from) may also contain numerous holes that may help to increase friction and reduce migration of the implant as well as allow outflow of exudates. The design of the socket is thus able to securely hold various sizes of medical devices (e.g. CIEDs) and prevent or reduce migration of the device during implantation, without risk of the device falling out of the socket.
  • medical devices e.g. CIEDs
  • the antibiotic socket of the current invention may comprise a single layer or multiple layers of a biodegradable/bioresorbable polymer film with at least one antibiotic agent contained within at least one of the polymer layers, or the antibiotic may be disposed as a separate layer encapsulated by at least two polymer layers to form a control-release matrix to provide a required eluting profile for the at least one antibiotic agent for a desired time period.
  • the single layer or multilayer structure also can be incorporated with other functional agents, such as anti-inflammatory, or anaesthetic agents or a growth factor agent.
  • a controlled-release antibiotic socket for securely holding an implantable medical device, comprising:
  • At least one film made from at least one polymer layer, where the at least one film is formed into the socket; at least one antibiotic agent; and at least one opening in the socket, wherein
  • the term “socket” is intended to mean a device that is intended to securely hold a separate object by surrounding the whole or part of said separate object (e.g. the socket may leave parts of the object uncovered to enable further connectivity of the object).
  • the socket is intended to be smaller than the object it is intended to hold and accomplishes the secure holding by its elastic nature, such that it may be stretched to a size larger than the object to be held and then recovers towards its original size once the object to be held has been placed within the socket.
  • the socket requires at least one opening to permit an object to be inserted within it and so the socket may also be described as a pocket when it has a single opening.
  • the socket may have two openings and so may also be called a sleeve or band. It will be appreciated that the socket may contain more than two openings too.
  • the socket is made from at least one film.
  • a film made from at least one polymer layer for securely holding an implantable medical device comprising:
  • both the socket and film are elastic, in that they can be stretched/deformed in any direction and recover towards their original size and shape. This property enables the socket to securely hold an object placed therein. This may be accomplished by the resilient force applied to the object inserted into the socket by the elastomeric polymeric material that comprises the film.
  • the socket or film can resiliently engage or resiliently hold a device inserted into a socket formed from the film after stretching.
  • the socket or film can stretch from its original size to an expanded size and return to its original size or to a size no greater than the expanded size minus (80% of the difference between expanded size and original size), optionally wherein the socket or film can stretch from its original size to an expanded size and return to its original size or to a size no greater than the expanded size minus (90% of the difference between expanded size and original size).
  • the controlled release antibiotic socket of the current invention provides enhanced stability of the object (i.e. the CIED) within the socket, reducing the possibility of the object falling out of the socket, and is able to effectively achieve that for a wide range of objects (i.e. CIEDs of different sizes) with one size of socket.
  • the selection of an elastic polymeric material is an intricate balance of elastic modulus and strain recovery. Certain polymers with high elasticity (low elastic modulus) have poor strain recovery, and would not be able to hold an object well. Other polymers that have relatively low elasticity (high elastic modulus) are not suitable for the construction of a sleeve that can securely hold different sizes of object.
  • the design of the sleeve aids in enhancing the stability of the object (i.e. CIED) within. Thus care need to be exercised in selecting the materials used to form the polymer film.
  • the controlled-release elastic biodegradable antibiotic film that makes up the socket in the first embodiment of the invention may comprise a single layer or multiple layers with at least one antibiotic agent contained within at least one of the layers to form a controlled-release matrix to provide a required eluting profile for the at least one antibiotic agent for a desired time period.
  • One or more of the layers may contain a releasing agent to enhance control of release of at least one antibiotic agent within the same layer or at other layers of the film.
  • the single layer or multilayer structure also can be incorporated with other functional agents, such as anti-inflammatory, or anaesthetic agents or a growth factor agent.
  • a controlled-release antibiotic film made from at least one polymer layer for securely holding an implantable medical device, the film comprising at least one polymer layer that is made from a biodegradable elastomeric polymeric material; and at least one antibiotic agent is dispersed within at least one of the at least one polymer layers and/or, when the film comprises at least two polymer layers, the at least one antibiotic agent is disposed as a separate layer between two polymer layers.
  • the controlled release antibiotic socket and films of the current invention provide enhanced control of drug eluting characteristics compared with previous drug eluting articles. This is achieved tuning of various factors, for example using additional layers (polymer layers or a layer of drug), where the active agent(s) are incorporated into different layer(s) (whether dispersed within a polymer layer, or forming a separate layer sandwiched between polymer layers), controlling the polymers used, controlling the thickness of the layers, the drug-polymer composite ratio, addition of releasing agent(s), and a layered structure designed to control the release rate of the active agent(s).
  • antibiotic film and “antibiotic agent” may refer to an antimicrobial, an antifungal, an antiseptic or a disinfecting film and/or agent.
  • antibiotic film and “antibiotic agent” may refer to an antimicrobial or antifungal agent.
  • antimicrobial agents examples include tetracycline and its derivatives (such as minocycline, tigecycline and doxycycline), rifampin, triclosan, chlorhexidine, penicillins, aminoglycides, quinolones, vancomycin, gentamycine, a cephalosporins (e.g. cephalosporin), carbapenems, imipenem, ertapenem, an antimicrobial peptide, cecropin-mellitin, magainin, dermaseptin, cathelicidin, ⁇ -defensins, ⁇ -protegrins, pharmaceutically acceptable salts thereof and combinations thereof.
  • tetracycline and its derivatives such as minocycline, tigecycline and doxycycline
  • rifampin such as minocycline, tigecycline and doxycycline
  • triclosan chlorhexidine
  • penicillins aminoglycides
  • quinolones vancomycin
  • antimicrobial agents include a combination of rifampin and another antimicrobial agent, such as a combination of rifampin and a tetracycline derivative (e.g. minocycline, doxycycline, and tigecycline, such combinations including rifampin and doxycycline, rifampin and tigecycline or, more particularly, rifampin and minocycline).
  • a combination of rifampin and another antimicrobial agent such as a combination of rifampin and a tetracycline derivative (e.g. minocycline, doxycycline, and tigecycline, such combinations including rifampin and doxycycline, rifampin and tigecycline or, more particularly, rifampin and minocycline).
  • the antimicrobial agent is a combination of rifampin and minocycline
  • the ratio of rifampin to minocycline is from 1:10 to 10:1 (wt/wt) (e.g. from 2:5 to 5:2 (wt/wt)).
  • rifampicin and “rifampin” are used interchangeably herein to refer to the active agent having CAS number 13292-46-1, or salts and/or solvates thereof.
  • antifungal agents examples include azoles (such as ketoconazole, clotrimazole, miconazole, econazole, itraconazole, fluconazole, bifoconazole, terconazole, butaconazole, tioconazole, oxiconazole, sulconazole, saperconazole, clotrimazole, voriconazole, clotrimazole), allylamines (such as terbinafine), morpholines (such as amorolfine and naftifine), griseofulvin, haloprogin, butenafine, tolnaftate, nystatin, cyclohexamide, ciclopirox, flucytosine, terbinafin, amphotericin B and pharmaceutically acceptable salts thereof.
  • azoles such as ketoconazole, clotrimazole, miconazole, econazole, itraconazole, fluconazole,
  • releasing agent or “hydrophilic small molecules” may refer to natural or synthetic chemical compounds with a molecular weight of less than 2000 Daltons, which are able to dissolve or dislodge from a matrix when in contact with water or in physiological conditions.
  • releasing agents include sorbitol, xylitol, glycerin, mannitol, polyethylene glycol (PEG) having a number average molecular weight of from 200 to 2000 Daltons, polysorbate and urea or any molecule (e.g. one that has a molecular weight of less than 2000 Daltons) with a hydrophobic-lipophilic balance of greater than 6.
  • the term “polymer layer” may refer to a formulated composition which forms a solid or semi-solid film, with/without an antibiotic agent (as defined herein), with a controlled thickness.
  • the combination of polymer layers may serve as a drug reservoir exhibiting drug control-release behaviour.
  • the polymeric material when an antibiotic agent is present in the polymeric layer, may comprise at least 1 wt % (e.g. at least 2 wt %, such as at least 5 wt %) of the polymer layer.
  • antibiotic layer may refer to a defined layer of an antibiotic layer laid on the surface of a polymer layer and comprising at least one or more antibiotic materials, but which is substantially free of a polymeric material (i.e. there may be less than 0.5 wt % of a polymeric material as a minor impurity in said layer), or more particularly, there is an absence of polymeric material in the antibiotic layer.
  • the antibiotic layer cannot be on a surface of a polymer layer that is directly in contact with the environment in a completed film, that is, each antibiotic layer is ultimately encapsulated between two polymer layers. This encapsulation may be direct (e.g. an antibiotic layer is sandwiched between two polymer layers) or indirect (e.g.
  • the antibiotic layers may be continuous or discontinuous, such that the antibiotic layer can be encapsulated within the polymer layers (e.g. the footprint of the antibiotic layer is adjusted so that it is smaller than the footprint of the polymer layers that encapsulate it).
  • the antibiotic layer may take the form of a particulate layer on the surface of a polymeric substrate layer.
  • the film of the current invention may provide beneficial effects as a single layer of film
  • particular embodiments of the invention relate to a film has at least two polymer layers.
  • the film may have from two to nine layers, such as from three to seven layers (e.g. from three to five layers), whether polymer layers only or a combination of polymer layers and antibiotic layers, provided that the antibiotic layers are not the outer layers of the film.
  • the film may have from two to nine polymer layers, such as from three to seven polymer layers (e.g. from three to five polymer layers).
  • bioresorbable polymer and “biodegradable polymer” refers to a material that can be at least partially broken down or, more particularly, fully degraded by contact with a bodily fluid, with the breakdown products being either eliminated from the body as waste or used by the body in further metabolic processes (e.g. anabolic processes).
  • bioresorbable polymers include poly(DL-lactide-co-caprolactone) (DL-PLCL), or more particularly, poly(lactide-co-caprolactone) (PLCL), polycaprolactone (PCL), polyglycolide (PGA), poly(L-lactic acid) (PLA), poly(trimethylene carbonate) (PTMC), polydioxanone (PDO), poly(4-hydroxy butyrate) (PHB), polyhydroxyalkanoates (PHA), poly(phosphazene), poly(phosphate ester), poly(amino acid), polydepsipeptides, poly(butylene succinate) (PBS), polyethylene oxide, polypropylene fumarate, polyiminocarbonates, poly(D,L-lactic acid), polyglycolic acid, poly(L-lactide-co-D,L-lactide), poly(L-lactide-co-glycolide) (PLGL), poly(D,L-lactide-co-glycoli
  • Particular bioresorbable polymers include poly(DL-lactide-co-caprolactone) (DL-PLCL), or more particularly, polycaprolactone (PCL), polyglycolide (PGA), poly(L-lactic acid) (PLA), polydioxanone (PDO), poly(4-hydroxy butyrate) (PHB), polyhydroxyalkanoates (PHA), PEG and its derivatives, and their copolymers (e.g. selected from one or more of the group consisting of poly(DL-lactide-co-caprolactone) (DL-PLCL), polycaprolactone (PCL), polyglycolide (PGA), poly(L-lactic acid) (PLA), PEG and its derivatives and their copolymers).
  • PCL poly(DL-lactide-co-caprolactone)
  • PGA polyglycolide
  • PLA poly(L-lactic acid)
  • PDO polydioxanone
  • PDO poly(4-hydroxy butyrate)
  • PHA polyhydroxy
  • poly(ester-urethane)s include, poly(diol citrates), poly(4-hydroxybutyrate)s, poly(glycerol sebacate), and star-poly( ⁇ -caprolactone-co-D,L-lactide), poly(lactide-co-caprolactone) (PLCL), poly(glycolide-co-caprolactone) (PGCL) and other biodegradable elastomer prepared through synthesis of di-, tri-, or multi-polymers, architecturally arranged in block, star, or linear structures, and prepared as thermoplastics or thermosets, their co-polymers, and mixtures or blends.
  • Particular polymers that may be mentioned herein include DL-PLCL, PGCL and PLCL, their copolymers, and mixtures or blends thereof.
  • the term “elastic polymer” refers to a material that can resist a distorting influence or stress and can return to towards its original size and shape when the stress is removed.
  • the elastic polymer may be stretched up to 10 times its original size in any direction (e.g. from 1.1 times to 4 times its original size) and may then recover at least to 80%, such as at least 90% of its original size following release of the stretch.
  • a film to size B a difference of size C
  • C is B ⁇ A, such as a maximum size of B ⁇ (0.9 ⁇ C).
  • the antibiotic film can be prepared as a single polymer, a polymer blend or copolymer, with one or more layers.
  • Particular polymers that may be mentioned herein include PLCL, DL-PLCL and PGCL.
  • polymer layers described above may be combined to form a single multilayer film.
  • This film may only have polymer layers, or may also have antibiotic layers interspersed between the polymer layers, provided that the antibiotic layers are ultimately encapsulated between two polymer layers.
  • the number average molecular weight of the polymer may be greater than or equal to 5,000 Daltons, such as greater than 5000 Daltons (e.g. from 5,000 to 500,000 Daltons).
  • the antibiotic film include may include a releasing agent in at least one layer of the film or the film that comprises a component part of the socket.
  • the releasing agent may be present in at least one of the at least one layers of the film, whether the layer is a polymer layer or an antibiotic layer, or may be present in more than one of the layers that make up the film, up to the total number of layers in the film. It will be appreciated, that when present, the releasing agent may be a single releasing agent or may be more than one releasing agent. When there is more than one releasing agent (e.g. 2 to 10 releasing agents), the releasing agents may be mixed together to form a blend that may be applied to one or more of the layers of the film as described above.
  • each releasing agent may be applied to separate layers of the film, provided that more than two layers of the film are intended to contain a releasing agent.
  • at least three releasing agents e.g. 4 to 10 releasing agents
  • at least two blends e.g. 3 to 9 blends
  • the releasing agent may be present in an amount from 0.1 wt % to 50 wt % of said layer.
  • the antibiotic film includes at least one antibiotic agent which is distributed in at least one layer of polymer.
  • the antibiotic agent may be distributed within one or more polymer layers of the antibiotic film (e.g. heterogeneously or, more particularly homogeneously distributed). Therefore, while not necessary, in particular embodiments of the current invention the at least one antibiotic agent is miscible with the bioresorbable polymer of each polymer layer in which it is present. For example:
  • the at least one antibiotic agent may be present in an amount of from 0.1 wt % to 99 wt %, such as from 0.1 wt % to 95 wt % of said polymer layer (e.g.
  • the at least one antibiotic agent may be present in an amount of from 0.1 wt % to 30 wt % of said polymer layer, optionally wherein said polymer layer is solvent cast and/or in the at least one layer of the polymer film, the at least one antibiotic agent may be present in an amount of from 10 wt % to 95 wt % (e.g.
  • the antibiotic film can be formed as a single layer film or a multilayer film composite.
  • the composite consists of at least one type of biodegradable polymer and at least one antibiotic agent.
  • Each polymer layer can be formed from one biodegradable polymer or polymer blends.
  • the outer layer of biodegradable polymer film incorporated with or without an agent to encourage tissue growth on the surface, such as collagen, a middle layer of biodegradable polymer incorporated with an antibiotic agent, and a third layer of biodegradable polymer, with no active agent.
  • Another multilayer film composite can be a layer of biodegradable polymer with or without a growth factor agent, three layers of a biodegradable polymer composite comprising an antibiotic agent, and followed by a layer of biodegradable polymer film with or without a growth factor agent.
  • the antibiotic agents in the three layers can be the same or different in content and concentration distribution.
  • antibiotic film examples include:
  • the at least one antibiotic agent is present in an amount of from 0.1 wt % to 99 wt %, such as from 0.1 wt % to 95 wt % of said polymer layer (e.g. from 0.1 wt % to 90 wt % or from 0.1 wt % to 80 wt %, from 0.1 wt % to 60 wt %, such as from 0.1 wt % to 30 wt % or from 10 wt % to 60 wt %).
  • the actual amount present within each polymer layer may vary depending on the way that the layer of film was prepared.
  • the at least one antibiotic agent when the polymer layer is solvent cast the at least one antibiotic agent may be present in an amount of from 0.1 wt % to 30 wt % of said polymer layer, and when the polymer layer was formed by spray coating it onto a substrate, the at least one antibiotic agent may be present in an amount of from 10 wt % to 95 wt % (e.g. from 10 wt % to 60 wt %, or from 30 wt % to 95 wt %, such as from 40 wt % to 80 wt %).
  • 10 wt % to 95 wt % e.g. from 10 wt % to 60 wt %, or from 30 wt % to 95 wt %, such as from 40 wt % to 80 wt %.
  • the film and sockets made therefrom may contain one or more layers of the one or more antibiotic agent that are ultimately encapsulated between two polymer layers.
  • the at least one antibiotic agent may be present in an amount of from 10 wt % to 100 wt % of said layer.
  • Said layer may further comprise releasing agent or other pharmaceutically acceptable adjuvants, diluents or disperants.
  • the at least one antibiotic agent may make up from 0.001 wt % to 30 wt %, or more particularly 0.001 wt % to 20 wt %, such as 0.001 wt % to 20 wt % (e.g. from 0.01 wt % to 5 wt %, or from 0.5 wt % to 5 wt %) of the weight of the entire film (i.e. all layers of the film).
  • the film/socket has to release the one or more antibiotic agents over an extended period of time in a controlled manner.
  • the at least one antibiotic agent is released from the antibiotic film over a period of from 1 to 30 days following implantation or, more particularly, over a period of from 3 to 14 days following implantation.
  • Particular films and sockets made therefrom that may be mentioned herein include an antibiotic film/socket where more than 10 wt % of the at least one antibiotic agent is released within 24 hours of implantation, with the entirety of the at least one antibiotic agent being released from the antibiotic film over a period of from 3 to 14 days following implantation.
  • the antibiotic films and the sockets made therefrom of the current invention can be used in medicine.
  • the antibiotic films mentioned herein can be used in treating or preventing infection and associated diseases and disorders.
  • the films mentioned herein may be used in:
  • the antibiotic films and sockets made therefrom mentioned herein may be used to cover at least part of the surface of a medical device that is then implanted into a subject, as described in more detail below.
  • the films and the sockets made therefrom may be applied to an implantable medical device, where the resulting device comprises a medical device and an antibiotic film in the form of a socket as described herein, wherein the socket covers a part or the whole of the medical device and is suitable for reducing or preventing migration of the medical device within the body following implantation.
  • the sockets made from the film may be provided in the shape of an envelope, pouch, pocket, sleeve or band to surround part or whole of the medical device.
  • the device may further comprise an additional active agent (e.g. a growth factor) coated onto whole or part of an exposed surface of the film. An embodiment of the device is described below in relation to FIG. 1 .
  • implantable medical device refers to a medical device that can be implanted transdermally, or to any indwelling medical device that includes a transdermal component.
  • implantable medical device examples include arteriovenous shunts, left ventricular assist devices, cardiovascular implantable electronic devices (CIEDs), tissue expanders, gastric lap bands, spinal cord stimulators, intrathecal infusion pumps, deep brain stimulators, gastric electrical stimulators, sacral nerve stimulators, and vagus nerve stimulators, amongst others.
  • FIG. 1 is a schematic illustration of an antibiotic film shaped into an article substrate that can be coupled to an implantable medical device for implantation into a site of subject's body.
  • the article may be used to secure an implantable device at the desired site within the subject's body, by helping to anchor the device into the surrounding tissue or part of the tissue.
  • the article is also able to inhibit bacterial growth due to the presence of the antibiotic agent within the film.
  • the socket 100 comprising a controlled-release antimicrobial film 110 as hereinbefore defined, has two openings 120 and 130 that may be fully or partially open, and so may be described as a band or sleeve, as well as a socket.
  • the socket itself and hence the openings 120 / 130 are smaller than the object to be inserted into and held by the socket.
  • the socket may also, as illustrated, contain a plurality of holes 140 in the film 110 .
  • the socket is made from a single film and so only requires a single side-seal 150 and may also comprise curved seal corners 160 . It will be appreciated that the socket may be manufactured using more than one film, which may then result in additional side-seals being required.
  • the openings 120 / 130 may be of the same size. However, it is specifically contemplated that the openings may also be of different sizes. In certain embodiments, the holes may be from 0.1 mm to 5 mm (e.g. from 0.3 mm to 2 mm or from 0.3 mm to 1 mm). As shown in FIG. 1 , the holes may have a uniform shape and size (e.g. all are circular in shape of the same size). However, it is specifically contemplated that the holes may be irregular in shape (each hole being of an undefined shape) or be of any shape (e.g. random defined shapes) and that the size of the holes may not be uniform. The holes may be focused in the middle (avoiding seals and openings) as shown in FIGS.
  • the sleeve may be formed by sealing at one end, as shown in FIG. 1 , or sealed at multiple ends.
  • the corner seals may be curved, as shown in FIG. 1 , angled or squared.
  • the socket 200 is made from a controlled-release antimicrobial film 210 (i.e. any film as defined hereinbefore), with two openings 220 and 230 , a plurality of holes (e.g. one or more holes) 240 , two-side seals 250 and angled sealed corners 260 .
  • the socket is smaller than the object to be inserted therein (i.e. a CIED) and may be capable of housing a range of different sizes of CIED.
  • the openings may be of different sizes; however it is specifically contemplated that the openings may also be of the same size.
  • the holes may be from 0.1 mm to 5 mm (e.g.
  • the socket of FIG. 2 may be formed by sealing two films together at two ends, as shown in FIG. 2 to form a sleeve or band-like structure.
  • the corner seals may be angled, as shown in FIG. 2 , or curved or squared. It is also contemplated that the corner seals may be angled in any technically suitable manner.
  • a socket in the form of a pocket 300 comprising a controlled-release antimicrobial film 310 (i.e. any film described hereinbefore), with one opening 320 , a plurality of holes (e.g. one or more holes) 330 , a three-side seal 340 , curved sealed corners 350 and angled sealed corners 360 .
  • the pocket may be formed by sealing at least two films together at three ends, leaving a single end open to act as an opening. It will be appreciated that all of the ends may be sealed together and a new opening created by cutting an opening of suitable dimensions into the sealed film (this may apply using a single film as well as more than two films).
  • the term “article” may refer to the overall medical device unit, that is the film and implantable medical device, or it may refer to the film shaped as a socket (i.e. a mesh, pouch, bag, envelope, sleeve, band, pocket or receptacle (all of which may be with or without holes)), that can fully or partially cover an implantable medical device.
  • a socket i.e. a mesh, pouch, bag, envelope, sleeve, band, pocket or receptacle (all of which may be with or without holes)
  • the socket (e.g. 300 of FIG. 3 ) may be in the form of an envelope with an opening 320 to allow insertion of an implantable device into the film and to permit insertion of accessories, such as leads or wires.
  • the surface of the article 300 may also contain holes 330 within the film 310 , with all possible shapes and dimensions to reduce mass of pouch and to enhance the release of the active agent into the surrounding tissue efficiently. It will be appreciated that this is generically applicable to other forms of sockets described or contemplated herein.
  • the size, shape and weight of the article can vary according to the implantation requirement.
  • the film may be cut into strips an applied piece-meal so as to cover whole or part of the medical device.
  • the film may be applied by any method of bonding, such as by the use of an adhesive, heat bonding or adhesion caused by the nature of the film itself (e.g. in the manner of attaching a plastic paraffin film to an object).
  • the sockets of FIGS. 1-3 are configured to (1) reduce device migration or erosion; (2) securely hold the implanted medical device within the article to reduce the risk of it falling out; (3) securely hold various sizes of medical device to reduce the risk of it falling out; (4) eliminate direct contact between the implanted medical device and the tissue layer; and (5) release antibiotic agent within a desired period at the required eluting rate. This is achieved by the properties of the socket and the antibiotic film(s) that form the socket of the current invention.
  • the antibiotic article is a versatile platform, which can be capable of different functions.
  • the controlled release of the antibiotic agent is sufficient to prevent or reduce bacteria colonization on the surface of the implantable medical device.
  • the device can also be incorporated with other functions, such as the enhancement of tissue attachment on the outer surface of the envelope by coating the surface of the film in direct contact with body tissue with one or more growth factors.
  • the article can be designed to have any shape and size according to the needs of the medical device to be implanted.
  • the film of the article described in FIG. 1 can be formed by at least one layer or several layers of biodegradable polymer film. At least one of said polymers layers contains an antibiotic agent. However, different layers may have different functions, such as a drug incorporation layer, a drug release control layer, a layer to promote tissue-ingrowth after implantation etc.
  • FIG. 4 provides various multilayer films according to aspects of the invention.
  • the single layer to multiple layer films may have a total thickness of the film is from 1 ⁇ m to 2000 ⁇ m (e.g. from 10 ⁇ m to 500 ⁇ m, such as from 40 ⁇ m to 300 ⁇ m).
  • the thickness of each layer of the polymer film may be from 0.01 ⁇ m to 1000 ⁇ m (e.g. from 0.01 ⁇ m to 200 ⁇ m).
  • Design 4-1 shows a 3-layer film, in which the middle layer may be a piece of drug-containing biodegradable polymer film with at least one or more drugs 1 , the outer two layers 2 may be biodegradable polymer films further comprising a releasing agent blend, but without any active agent which can be formed by the same or different polymer materials.
  • Design 4-2 depicts a 3-layer film, in which the middle layer is a piece of drug-containing biodegradable polymer film with at least one or more drugs 3 , the surface of this film ( 3 ) is coated with a layer of drug-containing biodegradable polymer layers with one or more drugs 4 .
  • Design 4-3 depicts a 5-layer film, in which the middle three layers are similar to design 4-2, with the outer two surface layers being biodegradable polymer layers that may contain a releasing agent and are with/without drug 5 .
  • Design 4-4 shows a 4-layer film, in which the middle two layers 6 contain a drug, with the films in the outer surfaces 5 are biodegradable polymer layers that may contain a releasing agent and are with/without drug.
  • Design 4-5 shows a 2-layer film, in which both layers are with one or two drugs 7 .
  • Design 4-6 shows a 5-layer film, in which the middle layer may be a piece of biodegradable elastic polymer film without any active agent or releasing agent 8 , the surface of this film ( 8 ) is coated with a layer of drug-containing biodegradable polymer layers with one or more drugs 4 , and the two outer surface layers are a blend of polymer and releasing agent that may or may not contain a drug 9 .
  • Design 4-7 shows a 7-layer film in which the middle layer may be a piece of biodegradable elastic polymer film without any active agent or releasing agent 8 , the surface of this film ( 8 ) is coated with a layer of drug-containing biodegradable polymer layers with one or more drugs 4 , the two layers immediately after is a blend of polymer with or without releasing agent 10 , and the outer surface layer is a blend of polymer and releasing agent that may or may not contain a drug 9 .
  • films may be prepared by making each layer separately and stacking these individual film layers together through heat-melting, heat-compression, chemical grafting, electrostatic adsorption, chemical crosslinking etc.
  • a film layer may also be used as a substrate and be spray- or dip-coated on one or both surfaces to form a further polymer layer (or layers).
  • the preferred film preparation methods are film casting, spray coating and heat compression.
  • the various embodiments described above are not intended to be limiting and the principles provided can be used to generate, further designs having different drug or polymer compositions and/or different film properties that do not departs from the spirit and scope of the current invention (e.g. that do not depart from the scope of the currently claimed invention). Designs that may be mentioned herein include those where the film comprises at least 2-layers.
  • the main purpose of the invention is to be able to control the drug release profile of one or more active agents independently in a drug-polymer matrix for different drugs. As different active agents have different potencies and different hydrophilicity, it is rather challenging to control the drug release profile by using one polymer formulation for each drug.
  • the designs shown in FIG. 4 enable one to control the drug release profile of different active agents separately to achieve a desired drug release profile for both agents.
  • the antibiotic article can be tailored to different shapes and dimension to partially cover or fully wrap an implantable medical device.
  • the thickness of each layer ranges from 0.01 ⁇ m to 1000 ⁇ m (e.g. from 0.01 ⁇ m to 200 ⁇ m).
  • the antibiotic article is bioabsorable, which can provide a temporary anchorage for implantable medical device and gradually be absorbed/excreted by the body to provide comfort to patient.
  • the article eliminates direct contact between the implanted medical device and tissue layer and may reduce the implanted device's migration or erosion.
  • the article is fully resorbable with good mechanical strength.
  • the growth of tissue on the surface of the antibiotic article can be controlled by incorporating a layer of growth factor on the surface according to surgeons' needs.
  • the sockets and/or films of the current invention provide the following advantages:
  • a sample of the film was cut into a 2 cm ⁇ 2 cm size, which was immersed in a vial containing 4 mL of PBS buffer (as the elution medium) for continuous drug elution testing.
  • the vial was placed in a 37° C. incubator shaker. At periodic intervals, the elution medium was withdrawn for reverse phase HPLC analysis to determine the eluted amount of rifampicin and minocycline and replaced with fresh PBS solution (4 mL). The cumulative drug release was calculated and plotted (see FIGS. 4-6 ).
  • Table 1 and FIG. 4 list a series of designs that were used in the examples.
  • the table lists a number of polymers that can be used to generate compositions according to the current invention (whether alone or in combination), as well as antibiotics. It will be understood that alternative polymers and antibiotics may be used.
  • Example 1 Design 4-1, Film Codes 1-1 and 1-2
  • PLCL resin 700 mg of sorbitol and 160 mg of minocycline (film code 1-1; rifampicin for film code 1-2) were dissolved in 10 mL acetone/ethanol solvent mixture of the ratio of 5:5 v/v. The mixture was mixed evenly for more than 4 hours. After the mixing, the solution was homogeneous and 5 mL of the solution was then poured onto a glass plate and drawn by a film applicator to form a film upon drying. The film was removed from the glass plate after the film was completely dry, following evaporation of the solvent.
  • 1.8 g PLCL resin and 50 mg sorbitol were dissolved in 10 mL of acetone.
  • a homogeneous solution was poured onto a glass plate and drawn by a film applicator to form a film following evaporation of the solvent. The film was then removed from the glass plate.
  • composition according to design 4-1 was prepared using two films according to 1-B sandwiching a film according to 1-A.
  • the resulting stack of films were aligned and compressed by a heat compressor at 60° C., 6 MPa for 50 seconds.
  • the middle three layers were prepared by following procedure in Example 2.
  • the two outer layers were prepared by following Example 1-B.
  • the stack of 5 layers of films were aligned properly and compressed by a heat compressor at 60° C., 6 MPa for 50 seconds.
  • the outer two layers were prepared by following Example 1-B.
  • the two middle drug-polymer layers were prepared by following Example 2-B.
  • the resulting films were aligned properly and compressed by a heat compressor at 60° C., 6 MPa for 50 seconds.
  • the two layers were prepared by following Example 1-A and 2-A.
  • Film compression procedure is the same as 1-C.
  • PLCL resin was heat compressed at 150° C., 60 Mpa for 1 minute.
  • PLCL resin 250 mg of polysorbate and 160 mg of minocycline (film code 1-1; rifampicin for film code 1-2) were dissolved in 10 mL acetone/ethanol solvent mixture of the ratio of 5:5 v/v. The mixture was mixed evenly for more than 4 hours. After the mixing, the solution was homogeneous and 5 mL of the solution was then poured onto a glass plate and drawn by a film applicator to form a film upon drying. The film was removed from the glass plate after the film was completely dry, following evaporation of the solvent.
  • a composition according to design 4-6 was prepared using two films according to 6-C sandwiching a film 6-A coated according to 6-B. The resulting stack of films were aligned and compressed by a heat compressor at 60° C., 6 MPa for 50 seconds.
  • 1.8 g PLCL resin and 50 mg of polysorbate were dissolved in 10 mL acetone/ethanol solvent mixture of the ratio of 5:5 v/v. The mixture was mixed evenly for more than 4 hours. After the mixing, the solution was homogeneous and 5 mL of the solution was then poured onto a glass plate and drawn by a film applicator to form a film upon drying. The film was removed from the glass plate after the film was completely dry, following evaporation of the solvent.
  • a composition according to design 4-7 was prepared using two films according to 7-A sandwiching a film 6-A coated according to 6-B. The stack is further sandwiched between two films according to 6-C. The resulting stack of films were aligned and compressed by a heat compressor at 60° C., 6 MPa for 50 seconds.
  • Film preparation procedure is the same as Example 1-A to prepare a single layer.
  • PLCL resin and 160 mg of minocycline were dissolved in 10 mL acetone/ethanol solvent mixture of the ratio of 5:5 v/v. The mixture was mixed evenly for more than 4 hours. After the mixing, the solution was homogeneous and 5 mL of the solution was then poured onto a glass plate and drawn by a film applicator to form a film upon drying. The film was removed from the glass plate after the film was completely dry, following evaporation of the solvent.
  • the film was prepared by following the protocol in Example 3.
  • the middle layer was prepared by using a drug mixture of 120 mg minocycline and 160 mg rifampin.
  • the two intermittent layers were prepared by spray coating of minocycline by following Example 2-B.
  • the outer two layers were prepared by following Example 1-B.
  • the stack of 5 layers of films were aligned properly and compressed by a heat compressor at 60° C., 6 MPa for 50 seconds.
  • the cumulative releasing profiles of two antibiotics are shown in FIG. 6 .
  • FIG. 5 shows the cumulative release of two antibiotics from different layered film designs and single films prepared in Examples 1 to 9 (film codes 1-1 to 1-18).
  • the drug density of both antibiotics is between 0.05 mg to 0.1 mg/cm 2 .
  • the absence of releasing agent results in a film with very slow release, while the presence of releasing agent gives a high initial burst with a fast releasing profile.
  • minocycline is more hydrophilic than rifampin, minocycline releases much faster.
  • the release profile and initial burst rate of rifampin and minocycline are tuned and well-controlled through the different designs.
  • the zone-of-inhibition (ZOI) for the film was determined according to the Kirby-Bauer method.
  • the study chose to test Escherisia Coli ( E. coli ) and S. aureus, S. epidermidisas demonstration.
  • E. coli has the highest minimum inhibitory concentration (MIC) among the other bacteria that are commonly found in humans.
  • the MIC of E. coli is 20 times higher than S. aureus, S. epidermidis , MRSA, S. capitis etc.
  • E. coli were inoculated into Lysogeny broth (LB broth) from a stock solution and incubated at 37° C. and then evenly spread over the entirety of an agar plate by a disposable spreader. A 15 mm diameter film was firmly pressed into the center of an agar plate and incubated at 37° C. Pieces were transferred to other fresh agar plates using sterile forceps every 24 hr. The diameter of the ZOI was measured and recorded every day.
  • Lysogeny broth LB broth
  • the elasticity and fit of the socket was tested using different socket sizes and CIED sizes. A good fit is when the CIED could be easily inserted into the socket, and does not fall out when overturned and held by the socket.

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US15/563,527 2015-03-31 2016-03-31 Elastic antimicrobial film and socket made therefrom Abandoned US20180193537A1 (en)

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PCT/SG2016/050158 WO2016159885A1 (en) 2015-03-31 2016-03-31 Elastic antimicrobial film and socket made therefrom

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