Classifications

• • 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
  • A61L31/145—Hydrogels or hydrocolloids
• • 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
  • A61L27/28—Materials for coating prostheses
  • A61L27/34—Macromolecular materials
• • 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
  • A61L27/52—Hydrogels or hydrocolloids
• • 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
  • A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
  • A61L29/08—Materials for coatings
  • A61L29/085—Macromolecular materials
• • 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
  • A61L31/08—Materials for coatings
  • A61L31/10—Macromolecular materials
• • 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
  • 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
  • A61L2300/20—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing organic materials
  • A61L2300/22—Lipids, fatty acids, e.g. prostaglandins, oils, fats, waxes
• • 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
  • A61L2300/20—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing organic materials
  • A61L2300/23—Carbohydrates
  • A61L2300/232—Monosaccharides, disaccharides, polysaccharides, lipopolysaccharides
• • 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
  • A61L2300/20—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing organic materials
  • A61L2300/252—Polypeptides, proteins, e.g. glycoproteins, lipoproteins, cytokines
• • 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
  • A61L2300/20—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing organic materials
  • A61L2300/258—Genetic materials, DNA, RNA, genes, vectors, e.g. plasmids
• • 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
  • A61L2300/606—Coatings

Definitions

• the present invention relates to the delivery of medicaments, such as drugs, from within or upon the surface of implantable medical devices, hi another aspect, the invention relates to hydrogel matrices containing these and other medicaments.
• Hydrogels are typically described as hydrophilic polymer networks that are capable of absorbing large amounts of water, yet are themselves insoluble because of the presence of physical or chemical crosslinks, entanglements or crystalline regions. Hydrogels have found extensive use in biomedical applications, including as coatings and drug delivery systems. Hydrogels are often sensitive to the conditions of their surrounding environment, such that the swelling ratio of the materials can be affected by temperature, pH, ionic strength and/or the presence of a swelling agent. Several parameters can be used to define or characterize hydrogels, including the swelling ratio under changing conditions, the permeability coefficient of certain solutes, and the mechanical behavior of the hydrogel under conditions of its intended use. When used as drug delivery systems these changes in the environment can often be controlled or predicted in order to regulate drug release. (See Bell and Peppas, cited below).
• hydrogel A particular type of hydrogel that has been described in recent years involves the combination of poly(methacrylic acid) (“PMAA”) backbones and polyethylene glycol (“PEG”) grafts.
• PMAA poly(methacrylic acid)
• PEG polyethylene glycol
• the hydrogels exhibit swelling transitions, in various solvent systems, and in response to external stimuli. These transitions, in turn, can lead to the formation or disruption of hydrogen-bonded complexes between the backbone and graft portions.
• the article describes the role of hydrophobic interactions in stabilizing the complexes.
• hydrogels for the delivery of medicaments, including those hydrogels based on the combination of polyalkylene glycols and poly(mefh)acrylates.
• polymers having reversible hydrophobic functionalities e.g., polymers having Lewis acid and Lewis base segments.
• the segments are hydrophilic and will either swell or dissolve in water. When incorporated into a polymer, the segments form water-insoluble or hydrophobic complexes. Upon changes in pH, temperature or solvent type, the complexes can dissociate, giving large transitions in viscosity, emulsification ability and mechanical strength.
• the polymers are said to be useful as reversible emulsifiers, super- absorbing resins, or as coatings for pharmaceutical agents.
• the Bell and Peppas papers exemplified the swelling behavior of P(MAA-g- EG) samples containing 40:60, 50:50 and 60:40 ratios (weight percent) of PMAA:PEG, using PEG grafts having molecular weights of 200, 400 and 1000.
• the resultant hydrogels were evaluated by several means, including mechanical testing to determine shear modulus. The authors found that as the molecular weight of the PEG graft was increased, the modulus of the networks decreased in both the complexed and uncomplexed state.
• a further method known to coat the surface of medical devices with antibiotics involves first coating the selected surfaces with benzalkonium chloride followed by ionic bonding of the antibiotic composition. See, e.g., Solomon, D. D. and Sherertz, R. J., J. Controlled Release, 6:343-352 (1987) and U.S. Pat. No. 4,442,133. Yet other methods of coating surfaces of medical devices with antibiotics are taught in U.S. Pat. No. 4,895,566 (a medical device substrate carrying a negatively charged group having a pK of less than 6 and a cationic antibiotic bound to the negatively charged group); U.S. Pat. No.
• the ionically complexed drug in the outer layer Upon exposure to body tissue of a medical device covered with such coating, the ionically complexed drug in the outer layer is released into body fluid or tissue. Following release of such complexed drug, the ionic surfactant complex sites in the outer layer are left vacant.
• the antibiotics and/or antiseptics quickly leach from the surface of the device into the surrounding environment. Over a relatively short period of time, the amount of antibiotics and/or antiseptics present on the surface decreases to a point where the protection against bacterial and fungal organisms is no longer effective.
• orthopedic fracture fixation devices such as intramedullary nails and external fixation pins, much of the antimicrobial coating sloughs off due to grating of the coated implant against the bone during insertion of the implant.
• medicament coatings continue to be sought to provide improved durability.
• US Patent No. 5,853,745 (Darouiche), describes a durable antimicrobial coated orthopedic device or other medical implant having a durable material layer that decreases the rate of leaching of antimicrobial agents into the surrounding environment.
• the patent provides an antimicrobial coated medical implant or orthopedic device having mechanical resiliency to minimize or avoid sloughing of the antimicrobial layer from the device during insertion.
• the medical implant has one or more of its surfaces coated with a composition comprising an antimicrobial coating layer comprising an antimicrobial agent in an effective concentration to inhibit the growth of bacterial and fungal organisms, and a protective coating layer formed over said antimicrobial coating layer.
• the present invention provides a crosslinkable coating composition, in both its uncrosslinked and crosslinked forms, for use in delivering a medicament from the surface of a medical device positioned in vivo. Once crosslinked, the coating composition provides a gel matrix adapted to contain the medicament in a form that permits the medicament to be released from the matrix in a prolonged, controlled, predictable and effective manner in vivo.
• the combination of gel matrix and medicament can be provided in any suitable manner and at any suitable time, e.g., the medicament can be included in one or more components of the uncrosslinked composition and/or it can be incorporated into the formed or forming matrix, e.g., at the time of use, and before, during, or after crosslinking the composition or implanting the thus-coated device into a tissue site.
• a gel matrix When applied as a coating to the surface of a medical device, a gel matrix can be formed thereon by a process that includes a complexation reaction between carboxylic acid groups and ether groups.
• the coating composition preferably comprises a polymeric reagent formed by the polymerization of the following monomers: a) about 1 to about 20 mole % of a polyether monomer, b) about 5 to about 75 mole % of a carboxylic acid-containing monomer, such that the effective ratio of ether groups to carboxylic acid groups in the resultant copolymer is between about 1 to 1 and about 10 to 1, c) optionally, about 0.1 to about 10 mole % of a photoderivatized monomer, and d) an amount of a hydrophilic monomer suitable to bring the composition to 100% (e.g., about 0 to about 93.9 mole % of a hydrophilic monomer).
• the polymeric reagent When the polymeric reagent is applied as a coating to the surface of a medical device, noncovalent interactions occur between carboxylic acid groups and ether groups, thus contributing to the formation of a gel matrix.
• the application of UN light provides photochemical attachment to the substrate as well as the formation of covalent crosslinks within the matrix.
• the matrix, thus formed, provides both improved durability and tenacity of the coating in a manner that prolongs the delivery of the medicaments incorporated into the matrix.
• the uncrosslinked composition comprises a polymeric reagent formed by the polymerization of the following monomers: a) methoxy poly(ethylene glycolmethacrylate) ("methoxyPEGMA"), as the polyether monomer, in an amount of between about 5 and about 15 mole %, b) (meth)acrylic acid, as the carboxylic acid-containing monomer component, present in an amount of between about 30 and about 50 mole %, c) photoderivatized monomer, present in an amount of between about 1 to about 7 mole %, and d) acrylamide monomer, as a hydrophilic monomer, present in an amount of between about 30 and about 70 mole %.
• methoxyPEGMA methoxy poly(ethylene glycolmethacrylate)
• a matrix of this invention provides an optimal and improved combination of such properties as medicament release profile, durability, tenacity, solubility, swellability, and coating thickness.
• Such a matrix can be used with a wide range of surface materials and configurations, and in turn, is widely applicable and useful with a variety of implanted devices.
• composition of this invention preferably includes between about 1 and about 20 mole % of a polyether monomer and preferably from about 5 to about 15 mole %. Most preferably, the polyether monomer is used at a final concentration of about 8 to about 12 mole %.
• the term "mole %" as used herein will be determined by the molecular weight of the monomer components.
• the polyether monomer is preferably of the group of molecules referred to as alkoxy (poly)alkyleneglycol (meth)acrylates.
• the alkoxy substituents of this group may be selected from the group consisting of methoxy, ethoxy, propoxy, and butoxy.
• the (poly)alkylene glycol component of the molecule maybe selected from the group consisting of (poly)propylene glycol and (polyethylene glycol.
• the (poly)alkylene glycol component preferably has a nominal weight average molecular weight ranging from about 200 g/mole to about 2000 g/mole, and ideally from about 800 g/mole to about 1200 g/mole.
• polyether monomers examples include methoxy PEG methacrylates, PEG methacrylates, and (poly)propylene glycol methacrylates.
• Such polyether monomers are commercially available, for instance, from Polysciences, Inc., (Warrington, PA).
• a composition of this invention preferably includes between about 5 to about 75 mole % of a carboxylic acid-containing monomer, such that the effective ratio of ether groups to carboxylic acid groups in the resultant copolymer is between about 1 to 1 and about 10 to 1.
• Preferred concentrations of the carboxylic acid-containing monomer are between about 30 to about 50 mole %. Most preferably, the carboxylic acid-containing monomer is used at a concentration between about 30 to about 40 mole %.
• These monomers can be obtained commercially, for instance, from Sigma- Aldrich, Inc. (St. Louis, MO).
• Preferred carboxylic acid-containing monomers are selected from carboxyl substituted ethylene compounds, also known as alkenoic acids.
• Examples of particularly preferred carboxylic acid-containing monomers include acrylic, methacryhc, maleic, crotonic, itaconic, and citraconic acid.
• Most preferred examples of carboxylic acid-containing monomers include acrylic acid and methacryhc acid.
• a composition of the present invention preferably includes between about 0.1 and about 10 mole % of a photoderivatized monomer, more preferably between about 1 and about 7 mole %, and most preferably between about 3 and about 5 mole %.
• suitable photoderivatized monomers are ethylenically substituted photoactivatable moieties which include N-[3-(4- benzoylbenzoamido)propyl]methacrylamide (“BBA-APMA”), 4(2-acryloxyethoxy)- 2-hydroxybenzophenone, 4-methacryloxy-2-hydroxybenzophenone, 4-methacryloxy- 2-hydroxybenzophenone, 9-vinyl anthracene, and 9-anthracenylmethyl methacrylate.
• An example of a preferred photoderivatized monomer is BBA-APMA.
• Photoreactive species are defined herein, and preferred species are sufficiently stable to be stored under conditions in which they retain such properties. See, e.g., U.S. Patent No. 5,002,582, the disclosure of which is incorporated herein by reference.
• Latent reactive groups can be chosen that are responsive to various portions of the electromagnetic spectrum, with those responsive to ultraviolet and visible portions of the spectrum (referred to herein as "photoreactive") being particularly preferred.
• Photoreactive species respond to specific applied external stimuli to undergo active specie generation with resultant covalent bonding to an adjacent chemical structure, e.g., as provided by the same or a different molecule. Photoreactive species are those groups of atoms in a molecule whose covalent bonds remain unchanged under conditions of storage but upon activation by an external energy source, form covalent bonds with other molecules.
• the photoreactive species generate active species such as free radicals and particularly nitrenes, carbenes, and excited states of ketones upon absorption of electromagnetic energy.
• Photoreactive species can be chosen to be responsive to various portions of the electromagnetic spectrum, and photoreactive species that are responsive to, e.g., ultraviolet and visible portions of the spectrum, are preferred and can be referred to herein occasionally as "photochemical group” or "photogroup.”
• photoreactive species in photoreactive aryl ketones are preferred, such as acetophenone, benzophenone, anthraquinone, anthrone, and anthrone-like heterocycles, i.e., heterocyclic analogs of anthrone such as those having N, O, or S in the 10- position, or their substituted, e.g., ring substituted, derivatives.
• preferred aryl ketones include heterocyclic derivatives of anthrone, including acridone, xanthone, and thioxanthone, and their ring substituted derivatives. Particularly preferred are thioxanthone, and its derivatives, having excitation energies greater than about 360 nm.
• ketones are preferred since they are readily capable of undergoing the activation/inactivation reactivation cycle described herein.
• Benzophenone is a particularly preferred photoreactive moiety, since it is capable of photochemical excitation with the initial formation of an excited singlet state that undergoes intersystem crossing to the triplet state.
• the excited triplet state can insert into carbon-hydrogen bonds by abstraction of a hydrogen atom (from a support surface, for example), thus creating a radical pair. Subsequent collapse of the radical pair leads to formation of a new carbon-carbon bond.
• a reactive bond e.g., carbon-hydrogen
• the ultraviolet light-induced excitation of the benzophenone group is reversible and the molecule returns to ground state energy level upon removal of the energy source.
• Photoactivatible aryl ketones such as benzophenone and acetophenone are of particular importance inasmuch as these groups are subject to multiple reactivation in water and hence provide increased coating efficiency.
• the azides constitute a preferred class of photoreactive species and include derivatives based on arylazides (C 6 R 5 N 3 ) such as phenyl azide and particularly 4-fluoro- 3-nitrophenyl azide, acyl azides (-CO-N 3 ) such as benzoyl azide and p-methylbenzoyl azide, azido formates (-O-CO-N 3 ) such as ethyl azidoformate, phenyl azidoformate, sulfonyl azides (-SO 2 -N 3 ) such as benzenesulfonyl azide, and phosphoryl azides (RO) 2 PON 3 such as diphenyl phosphoryl azide and diethyl phosphoryl azide.
• arylazides C 6 R 5 N 3
• acyl azides such as benzoyl azide and p-methylbenzoyl azide
• azido formates -O-CO-N 3
• Diazo compounds constitute another class of photoreactive species and include derivatives of diazoalkanes (-CHN 2 ) such as diazomethane and diphenyldiazomethane, diazoketones (- CO-CHN 2 ) such as diazoacetophenone and l-trifluoromethyl-l-diazo-2-pentanone, diazoacetates (-O-CO-CHN ) such as t-butyl diazoacetate and phenyl diazoacetate, and beta-keto-alpha-diazoacetates (-CO-CN 2 -CO-O-) such as t-butyl alpha diazoacetoacetate.
• diazoalkanes -CHN 2
• diazoketones - CO-CHN 2
• diazoacetates -O-CO-CHN
• the coating agents Upon activation of the photoreactive species, the coating agents are covalently bound to each other and/or to the material surface by covalent bonds through residues of the photoreactive species.
• Exemplary photoreactive species, and their residues upon activation, are shown as follows.
• a composition of the present invention includes about 0 to about 93.9 mole %, preferably from about 30 to about 70 mole %, and most preferably from about 40 to about 60 mole % of a suitable hydrophilic monomer component.
• suitable hydrophilic monomers provide an optimal combination of such properties as water solubility, biocompatability, and wettability. Most preferably, the hydrophilic monomer improves or provides the resultant polymeric complex with improved water solubility, though noting that the carboxylic acid-containing monomer may be hydrophilic as well, and can contribute to this effect.
• Hydrophilic monomers are preferably taken from the group consisting of alkenyl substituted amides.
• Examples of preferred hydrophilic monomers include acrylamide, N-vinylpyrrolidone, methacrylamide, acrylamido propanesulfonic acid
• AMPS acrylamide
• Acrylamide is an example of a particularly preferred hydrophilic monomer. Such monomers are available commercially from a variety of sources, e.g.,
• the word "medicament”, as used herein, will refer to a wide range of biologically active materials or drags that can be incorporated into a coating composition of the present invention.
• the substances to be incorporated preferably do not chemically interact with the composition during fabrication, or during the release process.
• Additives such as inorganic salts, BSA (bovine serum albumin), and inert organic compounds can be used to alter the profile of substance release, as known to those skilled in the art.
• the term "medicament”, in turn, will refer to a peptide, protein, carbohydrate, nucleic acid, lipid, polysaccharide or combinations thereof, or synthetic inorganic or organic molecule, that causes a biological effect when administered in vivo to an animal, including but not limited to birds and mammals, including humans.
• Nonlimiting examples are antigens, enzymes, hormones, receptors, peptides, and gene therapy agents.
• Suitable gene therapy agents include a) therapeutic nucleic acids, including antisense DNA and antisense RNA, and b) nucleic acids encoding therapeutic gene products, including plasmid DNA and viral fragments, along with associated promoters and excipients.
• therapeutic nucleic acids including antisense DNA and antisense RNA
• nucleic acids encoding therapeutic gene products including plasmid DNA and viral fragments, along with associated promoters and excipients.
• other molecules that can be incorporated include nucleosides, nucleotides, antisense, vitamins, minerals, and steroids.
• Coating compositions prepared according to this process can be used to deliver drugs such as nonsteroidal anti-inflammatory compounds, anesthetics, chemotherapeutic agents, immunotoxins, immunosuppressive agents, steroids, antibiotics, antivirals, antifungals, and steroidal antiinflammatories, anticoagulants.
• drugs such as nonsteroidal anti-inflammatory compounds, anesthetics, chemotherapeutic agents, immunotoxins, immunosuppressive agents, steroids, antibiotics, antivirals, antifungals, and steroidal antiinflammatories, anticoagulants.
• drugs such as nonsteroidal anti-inflammatory compounds, anesthetics, chemotherapeutic agents, immunotoxins, immunosuppressive agents, steroids, antibiotics, antivirals, antifungals, and steroidal antiinflammatories, anticoagulants.
• hydrophobic drags such as lidocaine or tetracaine can be included in the coating and are released over several hours.
• Classes of medicaments which can be incorporated into coatings of this invention include, but are not limited to, anti- AIDS substances, anti-cancer substances, antibiotics, anti-viral substances, enzyme inhibitors, neurotoxins, opioids, hypnotics, antihistamines, immunosuppresents (e.g., cyclosporin), tranquilizers, anti- convulsants, muscle relaxants and anti-Parkinson substances, anti-spasmodics and muscle contractants, miotics and anti-cholinergics, iminunosuppressants (e.g.
• cyclosporine anti-glaucoma solutes, anti-parasite and/or anti-protozoal solutes, anti - hypertensives, analgesics, anti-pyretics and anti-inflammatory agents (such as NSAJD's), local anesthetics, ophthalmics, prostaglandins, anti-depressants, anti- psychotic substances, anti-emetics, imaging agents, specific targeting agents, neurotransmitters, proteins and cell response modifiers.
• NSAJD's non- Kleemann and J. Engel, Georg Thieme Nerlag, Stuttgart/ ⁇ ew York, 1987, incorporated herein by reference.
• Antibiotics are art recognized and are substances which inhibit the growth of or kill microorganisms. Antibiotics can be produced synthetically or by microorganisms. Examples of antibiotics include penicillin, tetracycline, chloramphenicol, minocycline, doxycycline, vancomycin, bacitracin, kanamycin, neomycin, gentamycin, erythromycin and cephalosporins.
• cephalosporins examples include cephalothin, cephapirin, cefazolin, cephalexin, cephradine, cefadroxil, cefamandole, cefoxitin, cefaclor, cefuroxime, cefonicid, ceforanide, cefotaxime, moxalactam, ceftizoxime, ceftriaxone, and cefoperazone.
• Antiseptics are recognized as substances that prevent or arrest the growth or action of microorganisms, generally in a nonspecific fashion, e.g., either by inliibiting their activity or destroying them.
• antiseptics include silver sulfadiazine, chlorhexidine, glutaraldehyde, peracetic acid, sodium hypochlorite, phenols, phenolic compounds, iodophor compounds, quaternary ammonium compounds, and chlorine compounds.
• Anti-viral agents are substances capable of destroying or suppressing the replication of viruses.
• anti- viral agents include ⁇ -methyl-P-adamantane methylamine), hydroxy-ethoxymethylguanine, adamantanamine, 5-iodo-2'- deoxyuridine, trifluorothymidine, interferon, and adenine arabinoside.
• Enzyme inhibitors are substances which inhibit an enzymatic reaction.
• enzyme inhibitors include edrophonium chloride, ⁇ - methylphysostigmine, neostigmine bromide, physostigmine sulfate, tacrine HCL, tacrine, 1-hydroxy maleate, iodotubercidin, p-bromotetramisole, 10-(a- diethylaminopropionyl)- phenothiazine hydrochloride, calmidazolium chloride, hemicholinium-3, 3,5-dinitrocatechol, diacylglycerol kinase inhibitor I, diacylglycerol kinase inhibitor II, 3-phenylpropargylaminie, ⁇ -monomethyl-L-arginine acetate, carbidopa, 3-hydroxybenzylhydrazine HCl, hydralazine HCl, clorgyline HCl, deprenyl
• Anti-pyretics are substances capable of relieving or reducing fever.
• Anti-inflammatory agents are substances capable of counteracting or suppressing inflammation. Examples of such agents include aspirin (salicylic acid), indomethacin, sodium indomethacin trihydrate, salicylamide, naproxen, colchicine, fenoprofen, sulindac, diflunisal, diclofenac, indoprofen and sodium salicylamide.
• Local anesthetics are substances which have an anesthetic effect in a localized region. Examples of such anesthetics include procaine, lidocaine, tetracaine and dibucaine.
• Imaging agents are agents capable of imaging a desired site, e.g., tumor, in vivo.
• imaging agents include substances having a label which is detectable in vivo, e.g., antibodies attached to fluorescent labels.
• the term antibody includes whole antibodies or fragments thereof.
• Cell response modifiers are chemotactic factors such as platelet-derived growth factor (pDGF).
• Other chemotactic factors include neutrophil-activating protein, monocyte chemoattractant protein, macrophage-inflammatory protein, SIS (small inducible secreted), platelet factor, platelet basic protein, melanoma growth stimulating activity, epidermal growth factor, transforming growth factor (alpha), fibroblast growth factor, platelet-derived endothelial cell growth factor, insulin-like growth factor, nerve growth factor and bone growth/cartilage-inducing factor (alpha and beta).
• pDGF platelet-derived growth factor
• Other chemotactic factors include neutrophil-activating protein, monocyte chemoattractant protein, macrophage-inflammatory protein, SIS (small inducible secreted), platelet factor, platelet basic protein, melanoma growth stimulating activity, epidermal growth factor, transforming growth factor (alpha), fibroblast growth factor, platelet-derived endothelial cell growth
• cell response modifiers are the interleukins, interleukin inhibitors or interleukin receptors, including interleukin 1 through interleukin 10; interferons, including alpha, beta and gamma; hematopoietic factors, including erythropoietin, granulocyte colony stimulating factor, macrophage colony stimulating factor and granulocyte-macrophage colony stimulating factor; tumor necrosis factors, including alpha and beta; transforming growth factors (beta), including beta-1, beta-2, beta-3, inhibin, activin, and DNA that encodes for the production of any of these proteins.
• the coating composition of the present invention can be used in combination with a variety of devices, including those used on a temporary, transient or permanent basis upon and/or within the body.
• medical devices suitable for the present invention include, but are not limited to catheters, implantable vascular access ports, blood storage bags, vascular stents, blood tubing, central venous catheters, arterial catheters, vascular grafts, intraaortic balloon pumps, heart valves, cardiovascular sutures, total artificial hearts and ventricular assist pumps, extracorporeal devices such as blood oxygenators, blood filters, hemodialysis units, hemoperfusion units, plasmapheresis units, hybrid artificial organs such as pancreas or liver and artificial lungs, as well as filters adapted for deployment in a blood vessel in order to trap emboli (also known as "distal protection devices").
• vascular stents such as self- expanding stents and balloon expandable stents.
• self-expanding stents useful in the present invention are illustrated in U.S. Pat. Nos. 4,655,771 and
• the surfaces of the medical devices maybe formed from polymeric, metallic and/or ceramic materials.
• Suitable polymeric materials include, without limitation, polyurethane and its copolymers, silicone and its copolymers, ethylene vinyl-acetate, thermoplastic elastomers, polyvinyl chloride, polyolefins, cellulosics, polyamides, polyesters, polysulfones, polytetrafluorethylenes, polycarbonates, acrylonitrile butadiene styrene copolymers, acrylics, polylactic acid, polyglycolic acid, polycaprolactone, polylactic acid-polyethylene oxide copolymers, cellulose, collagens, and chitins.
• Metallic materials include metals and alloys based on titanium (such as nitinol, nickel titanium alloys, thermo-memory alloy materials), stainless steel, tantalum, nickel-chrome, or cobalt-chromium (such those available under the tradenames ElgiloyTM and PhynoxTM).
• Metallic materials also include clad composite filaments, such as those disclosed in WO 94/16646.
• ceramic materials include ceramics of alumina and glass-ceramics such as those available under the tradename MacorTM.
• the substrates that can be coated with a composition of the present invention include materials that are substantially insoluble in body fluids and that are generally designed and constructed to be placed in or onto the body or to contact fluid of the body.
• the substrates preferably have the physical properties such as strength, elasticity, permeability and flexibility required to function for the intended purpose; can be purified, fabricated and sterilized easily; will substantially maintain their physical properties and function during the time that they remain implanted in or in contact with the body.
• substrates examples include: metals such as titanium/titanium alloys, TiNi (shape memory/super elastic), aluminum oxide, platinum platinum alloys, stainless steels, MP35N, elgiloy, haynes 25, stellite, pyrolytic carbon, silver or glassy carbon; polymers such as polyurethanes, polycarbonates, silicone elastomers, polyolefms including polyethylenes or polypropylenes, polyvinyl chlorides, polyethers, polyesters, nylons, polyvinyl pyrrolidones, polyacrylates and polymethacrylates such as polymethylmethacrylate (“PMMA”), n-Butyl cyanoacrylate, polyvinyl alcohols, polyisoprenes, rubber, cellulosics, polyvinylidene fluoride (“PNDF”), polytetrafluoroethylene, ethylene tetrafluoroethylene copolymer (“ETFE”), acrylonitrile butadiene ethylene, polyvin
• Substrates made using these materials can be coated or remain uncoated, and derivatized or remain underivatized.
• Medical devices upon or into which the composition can be coated include, but are not limited to, surgical implants, prostheses, and any artificial part or device which replaces or augments a part of a living body or comes into contact with bodily fluids, particularly blood.
• the substrates can be in any shape or form including tubular, sheet, rod and articles of proper shape.
• Various medical devices and equipment usable in accordance with the invention are known in the art. Examples of devices include catheters, suture material, tubing, and fiber membranes. Examples of catheters include central venous catheters, thoracic drain catheters, angioplasty balloon catheters.
• tubing examples include tubing used in extracorporeal circuitry, such as whole blood oxygenators.
• membranes examples include polycarbonate membranes, haemodialysis membranes, membranes used in diagnostic or biosensor devices. Also included are devices used in diagnosis, as well as polyester yarn suture material such as polyethylene ribbon, and polypropylene hollow fiber membranes.
• medical devices include the following: autotransfusion devices, blood filters, blood pumps, blood temperature monitors, bone growth stimulators, breathing circuit connectors, bulldog clamps, cannulae, grafts, implantible pumps, impotence and incontinence implants, intra-ocular lenses, leads, lead adapters, lead connectors, nasal buttons, orbital implants, cardiac insulation pads, cardiac jackets, clips, covers, dialators, dialyzers, disposable temperature probes, domes, drainage products, drapes, ear wicks, electrodes, embolic devices, esophageal stethoscopes, fracture fixation devices, gloves, guide wires, hemo filtration devices, hubs, intra-arterial blood gas sensors, intracardiac suction devices, intrauterine pressure devices, nasal spetal splints, nasal tampons, needles, ophthalmic devices, PAP brushes, periodontal fiber adhesives, pessary, retention cuffs, sheeting, staples, stomach ports, surgical instruments, transducer protectors
• a solution of the copolymer is prepared at a concentration of about 1% to a concentration of about 10% in water or an aqueous buffer solution.
• an organic solvent such as isopropyl alcohol (“IP A") can be included in the solution at concentrations varying from about 1 to about 40%.
• IP A isopropyl alcohol
• the medical device or surface to be coated can be dipped into the copolymer solution, or, alternatively, the copolymer solution can be applied to the surface of the device by spraying or the like. At this point, the device can be air- dried to evaporate the solvent or can proceed to the illumination step without drying.
• the devices can be rotated and illuminated with UV light for 5-10 minutes to insure an even coat of the coating.
• Coating thicknesses can be evaluated using scanning electron microscopy (SEM) in both the dry and hydrated forms. The difference in thickness between the dry and the hydrated condition is not generally significant.
• the thickness of the coating ranges from about 0.5 microns to about 20 microns and preferably from about 2 microns to about 10 microns.
• the device may be placed in a rotating fixture to facilitate the coverage of the device's surface.
• a rotating fixture For example, to coat the entire surface of a vascular stent, the ends of the device are fastened to a rotating fixture by resilient retainers, such as alligator clips.
• the stent is rotated in a substantially horizontal plane around its axis.
• the spray nozzle of the airbrush is typically placed 2-4 inches from the device. The thickness of the coating can be adjusted by the speed of rotation and the flow rate of the spray nozzle.
• Medicament is typically incorporated into the matrix after the matrix itself has been coated onto a medical device.
• a solution of medicament or medicaments is prepared and the matrix-coated device is soaked in the solution.
• Medicament is absorbed into the matrix from the solution.
• Various solvents can be used to form the medicament solution as the amount of medicament absorbed by the matrix can be controlled by the solvent solution.
• the pH and/or the ionic strength of the medicament solution can be adjusted to control the degree of medicament absorption by the matrix. After soaking in medicament solution for a period of time, the medical device is removed and air dried.
• a coating of the present invention is preferably sufficiently durable and tenacious to permit the coating to remain on the device surface, in vivo, for a period of time sufficient for its intended use, including the delivery of medicaments.
• the durability and/or tenacity of various coatings, on various surfaces can be assessed using conventional techniques.
• Applicants for instance, have constructed a device that includes the use of an adjustable O-ring connected to a high-end torque screw-driver. Using this device it is possible to place a constant and replicable force on a coated medical device, e.g., a catheter.
• the coated medical device to be tested is inserted into the O-ring and the torque applied to a desired level.
• the coated device is pulled through the device a predetermined number of times.
• the coated device is then removed from the O-ring and the device evaluated to determine the amount of matrix remaining on the surface.
• the matrix remaining on the surface can be detected either directly, e.g., by staining, and/or indirectly, e.g., using a drag loading and release assay.
• a medical device coated with a formulation of the present invention preferably retains the ability to absorb and release at least 75% of its initial capacity.
• suitable biomaterials include those substances that do not possess abstractable hydrogens to which the photogroups can form covalent bonds. Such biomaterials can be used in a variety of ways.
• biomaterials can be made suitable for coating via photochemistry by applying a suitable primer coating which bonds to the biomaterial surface and provides a suitable substrate for binding by the photogroups.
• metals and ceramics having oxide groups on their surfaces can be made suitable for coupling via photochemistry by adding a primer coating that binds to the oxide groups and provides abstractable hydrogens.
• metals include, but are not limited to, titanium, stainless steel, and cobalt chromium
• ceramics can include, but are not limited to, silicon nitride, silicon carbide, zirconia, and alumina, as well as glass, silica, and sapphire.
• One suitable class of primers for metals and ceramics are organosilane reagents, which bond to the oxide surface and provide hydrocarbon groups (Brzoska, J.B., et. al., Langmuir 10:4367-4373, 1994). This reference teaches that -SiH groups are suitable alternatives for bonding of photogroups.
• various tie layers can be applied to various metals, glass, and ceramics, which can in turn serve as sources of abstractable hydrogens for photochemical coupling to the surface.
• Various polymeric materials such as Nylon, polystyrene, polyurethane, polyethylene terepthalate, and various monomeric analogs used to prepare such polymers could be used for such tie layers. See, for instance, U.S. Pat. Nos. 5,443,455; 5,749,837; 5,769,796; 5,997,517.
• the present invention further includes the optional use of additional, e.g., "clad", layers covering and/or between layers of the composition in either a continuous or discontinuous fashion.
• additional e.g., "clad” layers covering and/or between layers of the composition in either a continuous or discontinuous fashion.
• one or more outer layers of one or more other materials e.g., a hydrophilic or protective outer coating
• a coating prepared as described herein can be photoimmobilized or otherwise bound, absorbed or attached on or to a coating prepared as described herein.
• such an additional coating can be applied on top of a medicament absorbing layer, either before and/or after medicament has been absorbed into the matrix. It is preferable to add the additional layer before medicament has been absorbed.
• a solution of the same or of a different copolymer can be prepared and the coated device dipped, sprayed or otherwise contacted with the solution and illuminated as described previously.
• the coated device can then be contacted with, e.g., soaked in, the medicament solution as described previously. Medicament will pass through the top coat and be absorbed by the underlying matrix. When placed in the body, the medicament will be released as described herein.
• a coating with enhanced lubricity, hemocompatibility, or other desired property can be incorporated into the medical device surface, thus forming a device coating that provides multiple desired properties.
• BBA-C1 Compound D 4-Benzoylbenzoic acid (BBA), 1.0 kg (4.42 moles), was added to a dry 5 liter Morton flask equipped with reflux condenser and overhead stirrer, followed by the addition of 645 ml (8.84 moles) of thionyl chloride and 725 ml of toluene.
• the product was transferred to a separatory funnel and the organic layer was removed and set aside as extract #1.
• the aqueous was then extracted with 3 X 1250 ml of CH 2 C1 2 , keeping each extraction as a separate fraction.
• the four organic extracts were then washed successively with a single 1250 ml portion of 0.6 N NaOH beginning with fraction #1 and proceeding through fraction #4. This wash procedure was repeated a second time with a fresh 1250 ml portion of 0.6 N NaOH.
• the organic extracts were then combined and dried over Na SO 4 .
• the rate of addition was controlled to keep the reaction temperature below 10°C at all times. After the addition was complete, the ice bath was removed and the mixture was left to stir overnight.
• the product was diluted with 2400 ml of water and transferred to a separatory funnel. After thorough mixing, the aqueous layer was removed and the organic layer was washed with 2400 ml of 2 N NaOH, insuring that the aqueous layer was basic. The organic layer was then dried over Na 2 SO and filtered to remove drying agent. A portion of the CHC1 3 solvent was removed under reduced pressure until the combined weight of the product and solvent was approximately 3000 g.
• the desired product was then precipitated by slow addition of 11.0 liters of hexane to the stirred CHC1 solution, followed by overnight storage at 4°C.
• the product was isolated by filtration and the solid was rinsed twice with a solvent combination of 900 ml of hexane and 150 ml of CHC1 3 . Thorough drying of the solid gave 900 g of N- lSf'-(t-butyloxycarbonyl)-3-aminopropyl]-methacrylamide, m.p. 85.8°C by differential scanning calorimetry ("DSC").
• a 3 -neck, 2 liter round bottom flask was equipped with an overhead stirrer and gas sparge tube.
• Methanol 700 ml
• HCl gas was bubbled into the solvent at a rate of approximately 5 liters/minute for a total of 40 minutes.
• the molarity of the final HCl/MeOH solution was determined to be 8.5 M by titration with 1 N NaOH using phenolphthalein as an indicator.
• N-[N'-(t-butyloxycarbonyl)-3-aminopropyl]methacrylamide 900 g (3.71 moles) was added to a 5 liter Morton flask equipped with an overhead stirrer and gas outlet adapter, followed by the addition of 1150 ml of methanol solvent. Some solids remained in the flask with this solvent volume. Phenothiazine, 30 mg, was added as an inhibitor, followed by the addition of 655 ml (5.57 moles) of the 8.5 M HCl/MeOH solution. The solids slowly dissolved with the evolution of gas but the reaction was not exothermic. The mixture was stirred overnight at room temperature to insure complete reaction.
• the solution was deoxygenated with a helium sparge for 60 minutes at 60° C, then sealed under argon and heated overnight at 60°C.
• the resulting product was dialyzed against deionized water using 12,000-14,000 molecular weight cutoff tubing for 66 to 96 hours, then filtered through Whatman #1 filter paper before being lyophilized to give 190 g of polymer.
• the resultant polymer was identified as methacryhc acid-co-methoxy PEGlOOO-MA-co-BBA-APMA having the following general structure (Compound TV).
• a series of polymers of the general formula of Compound IN were synthesized as generally described in Example 4.
• the mole percent of acrylamide and methoxy PEGIOOO monomethacrylate were varied while the mole percent of the BBA-APMA (Compound III) was constant at four mole percent.
• the ratios of the other groups to carbonyl groups in the various polymers were calculated assuming each mole of the methoxy PEGIOOO monomethacrylate contained 23 ether groups.
• a list of the various polymers prepared and the composition of the various polymers are listed below. The following compounds were synthesized in a manner analogous to that described above with respect to Compound TV.
• the mole % BBA-APMA was constant at 4 mole %.
• the composition of the various polymers were:
• the longevity of the antiseptic release was evaluated by transferring the rods from one agar surface to a fresh agar surface for zone of inhibition analysis.
• the 2 cm (0.8 in.) SS rods were laid parallel on to a Mueller-Hinton agar surface that was incubated with approximately a 1 x 10 CFU/ml of Staphylococcus epidermidis (ATCC 35984).
• the agar plates containing the parts were incubated overnight at 37°C.
• the zones of inhibition or areas of no bacterial growth were measured across the diameter of the part. Samples were transferred daily to new agar plates with fresh lawns of S. epidermidis until no zones of inhibition were present.
• the CDA containing rods produced zones starting at approximately 34 mm and leveling off to 15-18 mm by day 4 and continued at that size through day 14 while the HCP containing parts produced zones starting at approximately 33 mm and leveling off to 30 mm by day 3 and continued at that size through day 14 (end of experiment).
• Chlorhexidine Digluconate (“CHG) on Stainless Steel Rods Tested Against Staphylococcus epidermidis, Staphylococcus aureus. Escherichia coli, and Candida albicans
• Stainless steel (SS, 304) rods (0.75 in., 2 cm) were pretreated and a solution of compound IN was prepared as described in Example 6.
• a portion of the rods (0.6 in., 1.6 cm) was dip-coated into the coating solution by dipping into the solution at 0.5 cm (0.2 in.)/sec, swelling for 30 seconds and withdrawing at a rate of 0.2 cm (0.08 in.)/sec for the first 1.2 cm (0.5 in.) of the rod, the reduced to 0.05 cm (0.02 in.) for the last 0.4 cm (0.16 in.) of the rod.
• the rods were air-dried for 15 minutes and UV illuminated for 5 minutes with rotation as described in Example 6. Two coats were applied.
• Chlorhexidine digluconate (CHG) 100 mg/ml was diluted further in deionized (DI) water.
• Compound IV-coated parylene treated and uncoated rods were sterilized for 20 minutes in 70% PA and air-dried. All of the rods were soaked for one hour at room temperature in the CHG solution. The parts were then air-dried overnight.
• CHG-incorporated parts as well as uncoated and Compound-IV coated without CHG were tested in the zone of inhibition assay agent S. epidermidis (ATCC 35984), S. aureus (ATCC 25923) E. coli (ATCC 25922) and C. albicans (ATCC 10231) as described in Example 6.
• the parylene-only sample with drag gave zones starting at 22 mm and dropped off to no zones by 5 days.
• the Compound IN-coated samples with drag had zones starting at 20 mm and gradually decreased to no zones by day 21.
• C. albicans The controls with no drug for both uncoated and Compound IV-coated produced no zones.
• the uncoated parts with CHG produced zones starting at 17 mm for day one only.
• the parylene-only samples with drag gave zones starting at 19 mm and lasted only 2 days.
• the Compound IN-coated samples with drug gave zones that started at 28 mm and gradually decreased to zero zones by day 18.
• S. aureus The controls with no drag for both uncoated and Compound IV-coated did not produce zones.
• the uncoated parts with CHG produced zones starting at 23 and dropped off to no zones by day 4.
• the parylene-only samples with drag gave zones starting at 25 mm and dropped off to no zones by day 3.
• the Compound IN-coated samples with drug had zones starting at 23 mm and gradually decreased to 13 mm through day 12.
• Chlorhexidine Digluconate (CHG) on Titanium Rods Tested against S. epidermidis, S. aureus, E. coli. and C. albicans
• Titanium (90 Ti/6 A1/4V) rods (0.75 in., 2 cm) were pretreated with parylene and a Compound IV solution was prepared as described in Example 6.
• the rods were dip coated as described in Example 7, except that the entire rod was coated.
• the rods were air-dried and UV cured as described in Example 6. Two coats were applied.
• the uncoated, parylene treated, and Compound IV-coated rods were sterilized in 70% IPA for 20 minutes and air-dried.
• the samples were then incorporated with CHG at 100 mg/ml in DI water for one hour at room temperature with agitation.
• the rods were rinsed by dipping three times into tubes containing DI water and air-dried overnight.
• the quantity of CHG eluted from the rods was also determined.
• the individual rods were placed into test tubes containing 2 ml of Phosphate Buffer Saline ("PBS") and were incubated at 37°C overnight with agitation. The rods were transferred to fresh PBS daily, and the eluates were diluted into the High Pressure Liquid Chromatography (HPLC) mobile phase to solubilize the CHG.
• HPLC High Pressure Liquid Chromatography
• aureus The uncoated and parylene-only gave zone of 14-16 mm on day 1 and dropped off to no zones by day 3.
• the Compound IN samples with drug gave zones starting at 20 mm and gradually decreasing to 12 mm on day 16. They were discontinued on day 20 due to contamination.
• E. coli Uncoated and parylene-only gave zones of 13-14 mm on day 1 and dropped off to no zones by day 3. The
• BAK Benzalkonuim Chloride
• PebaxTM rods (0.75 in., 2 cm) were wiped clean with an IPA soaked cloth and a Compound IN solution was prepared as described in Example 6. The rods were dipped at 3.0 cm (1.2 in.)/sec into, 30 sec dwell, and a 3.0 cm (1.2 in.)/sec out of solution. The rods were air-dried for approximately ten minutes and UN illuminated for 3 minutes with rotation as described in Example 6. Two coats were applied and a portion of the PebaxTM rods were cut into 1 cm (0.4 in.) pieces for the zone of inhibition testing.
• BAK and CHG were prepared at 100 mg/ml in DI water and the samples were incorporated for one hour at room temperature with agitation. The rods were rinsed three times in DI water and air-dried overnight.
• S. epidermidis The samples were tested in the zone of inhibition assay against S. epidermidis (ATCC 35984) andE. coli (ATCC 25922) as described in Example 6 except the rods were placed perpendicular into the agar.
• S. epidermidis results The Compound IV coatings containing BAK gave zones starting at 26 mm and gradually decreasing to no zones by day 16. The CHG coated rods gave zones that started at 22 mm and gradually decreased to 12 mm on day 16 when the study was discontinued.
• E. coli The BAK coated rods gave zones that started at 11 mm but lasted only 2 days. The CHG coated rods gave zones that started at 15 mm and gradually decreased to 9 mm on day 16 when the study was discontinued.
• the polyurethane (PU) catheter material was wiped clean with IPA and a solution of Compound IV for coating was prepared as described in Example 6.
• the rods were dip coated in the coating solution by dipping into the solution at 1.0 cm (0.4 in.)/sec, dwelling for 30 seconds, and withdrawing at a rate of 0.5 cm (0.2 in.)/sec.
• the rods were air-dried for 15 minutes and UV illuminated for three minutes with rotation as described in Example 6. Two coats of the Compound IN coating were applied.
• the Compound IV coated rods were wiped with 70% IPA and dried for one hour.
• the rods were cut into 2 cm lengths and the CHG was incorporated by dipping the rods into a 200 mg/ml solution of CHG for one hour at room temperature and then rinsed three times in DI water.
• the samples were air-dried overnight and tested in the zone of inhibition assay against S. epidermidis (ATCC25984) as described in Example 6.
• ADC Alexidine Dihydrochloride
• a solution of alexidine dihydrochloride (ADC) (lOOmg/ml) in 50% methanol was prepared with heat.
• the PU rods were cut into 1 cm lengths and incorporated with the alexidine in the ADC solution in a warm water bath.
• the rods were incorporated for one hour, rinsed three times in DI water, and air-dried over night.
• the samples were tested in the zone of inhibition against S. epidermidis (ATCC 35984) as described in Example 6.
• Example 12 Release of Vancomycin ("VA") on Coated PU Rods Tested Against S. epidermidis Polyurethane rods (6 in., 15 cm) were wiped clean as described in Example 9 and a Compound IV solution was prepared as in Example 6. The rods were dip coated in the coating solution by dipping into the solution at 2.0 cm (0.8 in.)/sec, dwelling for 30 seconds, and withdrawing at 2.0 (0.8 in.)/sec. The rods were air-dried for 15 minutes and UN illuminated for four minutes with rotation as described in Example 6. Two coats were applied. A solution of vancomycin (V A) was prepared at 50 mg/ml in DI water. The rods were incorporated with VA in the VA solution for one hour at room temperature, rinsed three times in DI water, air-dried, and cut into 1 cm pieces. The samples were tested against S. epidermidis (ATCC35984) as described in Example 6.
• VA Vancomycin

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