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US20020072584A1 - Biostability of polymeric structures - Google Patents

Biostability of polymeric structures Download PDF

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Publication number
US20020072584A1
US20020072584A1 US09/985,821 US98582101A US2002072584A1 US 20020072584 A1 US20020072584 A1 US 20020072584A1 US 98582101 A US98582101 A US 98582101A US 2002072584 A1 US2002072584 A1 US 2002072584A1
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Prior art keywords
solvent
polymeric material
extraction
swelling
solubility parameter
Prior art date
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Abandoned
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US09/985,821
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English (en)
Inventor
Eamon Brady
Ann Cannon
Fergal Farrell
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Salviac Ltd
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Salviac Ltd
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Filing date
Publication date
Priority claimed from PCT/IE1999/000038 external-priority patent/WO2000067812A1/fr
Priority claimed from PCT/IE1999/000037 external-priority patent/WO2000067811A1/fr
Application filed by Salviac Ltd filed Critical Salviac Ltd
Assigned to SALVIAC LIMITED reassignment SALVIAC LIMITED ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: CANNON, ANN MARLE, FARRELL, FERGAL, BRADY, EAMON
Publication of US20020072584A1 publication Critical patent/US20020072584A1/en
Abandoned legal-status Critical Current

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    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12N—MICROORGANISMS OR ENZYMES; COMPOSITIONS THEREOF; PROPAGATING, PRESERVING, OR MAINTAINING MICROORGANISMS; MUTATION OR GENETIC ENGINEERING; CULTURE MEDIA
    • C12N5/00—Undifferentiated human, animal or plant cells, e.g. cell lines; Tissues; Cultivation or maintenance thereof; Culture media therefor
    • C12N5/0068—General culture methods using substrates
    • 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
    • A61L29/04—Macromolecular materials
    • A61L29/06—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
    • A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
    • A61L29/14—Materials characterised by their function or physical properties, e.g. lubricating compositions
    • A61L29/146—Porous materials, e.g. foams or sponges
    • 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
    • A61L31/146—Porous materials, e.g. foams or sponges
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
    • C08G18/00—Polymeric products of isocyanates or isothiocyanates
    • C08G18/06—Polymeric products of isocyanates or isothiocyanates with compounds having active hydrogen
    • C08G18/08—Processes
    • C08G18/10—Prepolymer processes involving reaction of isocyanates or isothiocyanates with compounds having active hydrogen in a first reaction step
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
    • C08G18/00—Polymeric products of isocyanates or isothiocyanates
    • C08G18/06—Polymeric products of isocyanates or isothiocyanates with compounds having active hydrogen
    • C08G18/28—Polymeric products of isocyanates or isothiocyanates with compounds having active hydrogen characterised by the compounds used containing active hydrogen
    • C08G18/40—High-molecular-weight compounds
    • C08G18/48—Polyethers
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
    • C08G2101/00—Manufacture of cellular products
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
    • C08G2110/00—Foam properties
    • C08G2110/0008—Foam properties flexible
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
    • C08G2110/00—Foam properties
    • C08G2110/0083—Foam properties prepared using water as the sole blowing agent
    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12N—MICROORGANISMS OR ENZYMES; COMPOSITIONS THEREOF; PROPAGATING, PRESERVING, OR MAINTAINING MICROORGANISMS; MUTATION OR GENETIC ENGINEERING; CULTURE MEDIA
    • C12N2531/00—Microcarriers
    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12N—MICROORGANISMS OR ENZYMES; COMPOSITIONS THEREOF; PROPAGATING, PRESERVING, OR MAINTAINING MICROORGANISMS; MUTATION OR GENETIC ENGINEERING; CULTURE MEDIA
    • C12N2533/00—Supports or coatings for cell culture, characterised by material
    • C12N2533/30—Synthetic polymers

Definitions

  • This invention relates to biocompatible polymeric structures suitable for long term implantation within a living human body, and as a substratum for cell, tissue and organ growth technologies.
  • a serious limitation associated with the processes and materials available to the biomedical designer today is the fact that virtually all materials available today require some level of additives.
  • An additional limitation of current materials is that polymerization reactions are far from perfect and generate materials which contain low molecular weight material, oligomers, unreacted monomers, catalysts, stabilizers and a host of other additives within the material. Irrespective of the source, these chemicals present a serious problem as they can leach into the tissue surrounding the implant.
  • This invention therefore is directed towards providing process and material technologies that can produce leachable free polymer systems with properties suitable for implantation.
  • solvent extracting the polymeric material with an extraction solvent the solvent being a solvent which generates a volumetric swelling and having a solubility parameter of from 17 to 27 MPa 0.5 .
  • the solvent extraction technique involves extracting the polymer in the presence of a swelling solvent.
  • the solvent swells the material of the implant by more than 30%, more preferably by more than 100% and still more preferably by more than 150%.
  • the solubility parameter of the solvent extraction system is selected for compatibility with the solubility parameter of the polymeric material or its phases.
  • the solubility parameter of the solvent extraction system is within ⁇ 4 MPa 1 ⁇ 2 of the solubility parameter of the polymer or its phases.
  • solubility parameter is from 18-24 MPa 1 ⁇ 2 .
  • the hydrogen-bonding component of the solvent solubility parameter is in excess of 3 MPa 1 ⁇ 2 .
  • the solvent solubility parameter is selected such that it is similar to that of material leachables.
  • the solvent is miscible with water.
  • the solvent has a vapour pressure in excess of 2 kPa. More preferably the vapour pressure is in excess of 5 kPa. Even more preferably the vapour pressure is in excess of 10 kPa.
  • the vapour pressure of MEK is 12.6 kPa, while the vapour pressure of THF is 21.6 kPa at room temperature.
  • the solvent selected has a low content of stabilizers and other additives and is non-reactive.
  • MEK is the preferred solvent due to its excellent ability to swell cross-linked polyurethanes, its miscibility with water, its high vapour pressure, its stability and it can be obtained at high level of purity.
  • the method includes the step of removing residual solvent from the structure, after solvent extraction.
  • residual solvent is removed by treatment with water.
  • the solvent is removed by freeze drying or by thermally induced phase separation.
  • the biocompatible material may for example be a polyether polyurethane, a polycarbonate urethane, a polydimethylsiloxane urethane, a polyester urethane, a fatty acid derived polyurethane, a polybutadiene polyurethane, a urethane urea of any of the above or mixtures.
  • the polyurethane is a polyether polyurethane, a polycarbonate polyurethane or a polydimethylsiloxane polyurethane.
  • the material is in the form of a medical implant.
  • the implant may be a septal defect occluder, a vessel occluder, a vessel defect occluder, a mammary prosthesis, a muscle bulking agent, a gynecological implant, a vascular graft, an embolising implant, a pacemaker housing cover, or an embolic filter.
  • the material may be in the form of a porous substratum for cell growth, tissue growth, organ growth or organ reconstruction.
  • the article may be formed from an organic diisocyanate, a polyol, a chain extender and a blowing agent.
  • a cross-lining agent may be employed to enhance the cross-linking of the material.
  • a catalyst and surfactant may also be employed.
  • the blowing agent is preferably water.
  • the ratios of the reaction components are selected to promote the formation of a three dimensional porous molecular structure of polyurethane biomaterial.
  • the article may be processed by a metering and mixing process, wherein the chemical components are aggressively mixed and dispensed into a vessel and chain extension and blowing reactions occur substantially simultaneously.
  • the article is processed by a reactive moulding process, wherein the chemical components are mixed and dispensed into a vessel wherein chain extension occurs.
  • the polyurethane scaffold has a pore size of from 10 microns to 300 microns. Ideally the scaffold has a pore size of between 35 microns to 200 microns.
  • the biocompatible, leachable free polyurethanes of this invention are derived from organic diisocyanates and polyols.
  • the reaction step converts the chemical precursors into a 3 dimensional molecular cross-linked structure.
  • a 3-dimensional network of this kind is insoluble and intractable.
  • the biomaterial is a three dimensional structure at a molecular level allows it to be processed aggressively to remove leachable chemicals from the material.
  • Low molecular weight chemicals have the potential to leach from the article and result in toxic reactions in living cells.
  • the severity of the inflammation, following implantation of a synthetic material is strongly dependent on the type and quantity of chemicals that can migrate from the implant to the surrounding tissue.
  • the processes of the invention expand the biomaterials volume at a molecular level. This expansion facilitates the removal of leachables such as monomers, oligomers, high molecular weight linear polymers, catalysts, surfactants, and other additives.
  • the solvent extraction process also reduces any internal stresses within the material.
  • the solvent expands the material by separating the molecular chains and suspending the chains in a solvent matrix. This loss of interchain attraction seriously compromises the mechanical properties of the matrix during the extraction step.
  • the 3-dimensional cross-links however provide the materials with molecular memory and prevent the molecular structure from being completely solubilised.
  • the recovery step removes the solvent and de-swells the material to its original state.
  • multiple solvent swelling extractions may be carried out. These extractions preferably use solvents that have an affinity for different leachables.
  • Low solubility parameter solvents have an affinity for surfactant leachables.
  • Moderate solubility parameter solvents are used to remove the bulk of the leachables including soft phase monomers, oligomers and diols.
  • High solubility parameter solvents have an affinity for hard phase monomers, dimers, oligomers and amine catalysts.
  • affinity of a particular leachable to a solvent must be off set against the ability of the solvent to swell the matrix. Higher swelling ratio solvents tend to be most effective in removing a wide spectrum of leachables.
  • the process of the invention is specifically designed to the treatment of polyurethane polymers. More specifically the invention is designed to treat polyurethane porous structures and scaffolds. However it is recognised that the principles of the invention can be applied to other materials. Indeed, most cross-linked polymer materials can be treated by the processes of the invention. The optimum swelling solvents will naturally have different solubility parameters to those specified for polyurethanes.
  • This process enhances the material biocompatible for use as an implantable medical device or as a 3 dimensional matrix for use as a cell scaffold in tissue engineering applications.
  • Altering the chemical precursors and the processing conditions of the material may alter the pore size and the density of the material, as required, to meet the requirements of the application.
  • the scaffold is immersed in the swelling solvent and placed in an ultrasonic chamber for a minimum of six hours.
  • the ultrasonic bath facilitates solvent penetration of the scaffold and assists in the migration of leachables from the polymer into the solvent.
  • the solvent is diluted by the drop wise addition of non-solvent, miscible with the solvent over a period of 1-3 hours.
  • the concentration of solvent should be less than 5% after the addition of non-solvent.
  • the scaffold is then immersed in pure non-solvent for 7-8 hours.
  • the scaffold is dried in an oven for 72 hours to remove all traces of the non-solvent.
  • This process is carried out in a fashion whereby material is subjected to minimal mechanical stress during the processing. This is particularly important during the swollen phase.
  • Achieving incredibly low levels of leachables may require multiple solvent swelling extraction steps. Different solvents may be used in each extraction steps.
  • Leachable levels can be measured gravimetrically or analytically (chromatography). HPLC grade water extraction of the materials or scaffold at 40° C. should produce a leachables content less than 1.0 mg per g. More preferably the water extracted leachables content is less than 10 ⁇ g per g: Even more preferably the water extracted leachables content is less than 0.1 ⁇ g per g. Extraction times in excess of 12 hours should be employed. These levels are near or below the level of detection for many analytical systems and may be demonstrated by extrapolation.
  • the exposure of the processed scaffold to a solvent whose solubility parameter is between 18 MPa 1 ⁇ 2 and 24 MPa ⁇ fraction (1/2) ⁇ , at 40° C. should produce a leachables content less than 10.0 mg per g in the solvent. More preferably the solvent extracted leachables content is less than 100 ⁇ g per g. Even more preferably the solvent extracted leachables content of the scaffold is less than 10.0 ⁇ g per g.
  • Suitable solvents for this assessment of polyurethane biomaterials include MEK, DMA and THF.
  • Solvents that provide the maximum swelling are preferred per this invention.
  • the volume swelling during solvent extraction should be above 30%.
  • the solvent swelling should be in excess of 100%. Even more preferable is solvent swelling in excess of 150%.
  • the level of solvent swelling decreases as the average molecular weight between cross-links decreases. However a minimum cross-link density is necessary to provide solvent swelling memory.
  • the molecular weight between cross-links of the material should preferably be between 300 and 6,000. Preferably the molecular weight between cross-links of the material is between 800 and 2,000. At very high cross-link densities the ability of the polymer to swell in the presence of a swelling solvent is diminished. At very low cross-ink densities large amounts of the polymer structure become solubilised. This creates recovery problems or results in a loss of structure.
  • the 3-dimensional molecular structure is important to achieving the physical and chemical characteristics of the invention.
  • the three dimensional aspect is achieved with polyurethane's either by incorporating a trifunctional entity within the formulation or by employing an isocyanate index in excess of 1.
  • Linear polymer systems cannot be subjected to such an aggressive solvent extraction since the use of a solvent with a similar solubility parameter will cause both the polymer and it's leachables to dissolve.
  • the biocompatible polyurethanes of this invention are useful for the manufacture of catheters, vascular grafts, septal occluders, vessel occluders, embolisation devices, mammary prosthesis, pacemaker housing covers, a stent cuffs, a stent covering, a tissue bridge, a vessel defect occluder, a muscle bulking agent, a gynecological implant, a vascular graft, an embolic filter and other such implant and blood contacting devices.
  • the material is in the form of a medical implant.
  • the material may be in the form of a porous substratum for cell growth, tissue growth, organ growth or organ reconstruction.
  • biostable polyurethanes of this invention are based on organic diisocyanates, polyols, and diol, diamine or water chain extenders and combinations thereof.
  • organic diisocyanates are of the general formula:
  • R is an aliphatic, aromatic, cycloaliphatic, or an aliphatic-aromatic hydrocarbon entity containing between 4 and 24 carbon atoms and “n” varies between 2.0 and 3. More preferably, R contains between 4 and 15 carbon atoms. Where n is 2, a polymer with a linear molecular structure may be produced. A three dimensional molecular network may be produced where n varies from 2.0 to 3.0. Ideally n should be 2.
  • Suitable isocyanates include: p-phenylene diisocyanate, tetramethylene diisocyanate, cyclohexane 1,2-diisocyanate, m-tetramethylxylene diisocyanate, hexamethylene diisocyanate, 2,4 diphenylmethane diisocyanate, 4,4 diphenylmethane diisocyanate, 2,4 toluene diisocyanate, 2,6 toluene diisocyanate, cyclohexane 1,4 diisocyanate, isophorone diisocyanate, 4,4-dicyclohexylmethane diisocyanate, 4,4-dicyclohexylmethane diisocyanate, and mixtures of the above.
  • isocyanates can be used to manufacture suitable materials; 2,4 diphenylmethane diisocyanate, 4,4 diphenylmethane diisocyanate, 2,4 toluene diisocyanate, 2, 6 toluene diisocyanate, cyclohexane 1,4 diisocyanate, isophorone diisocyanate, 4,4-dicyclohexylmethane diisocyanate, and mixtures of the above.
  • polyols may be used per this invention. These include polyether polyols, polyester polyols, polycarbonate polyols, silicone based polyols, fatty acid derived polyols, polybutadiene polyols.
  • the molecular weights of the polyols is in excess of 400 and less than 6000. More preferably the molecular weight is between 600 and 2500.
  • Polyether polyols, PDMS polyols and polycarbonate polyols are preferred for long term implantation applications.
  • Polyether polyols that may be used include products obtained by the polymerisation of cyclic oxide, for example, ethylene oxide, propylene oxide, butylene oxide, or tetrahydrofuran.
  • Useful polyether polyols include polytetramethylene glycols obtained by the polymerisation of tetrahydrofuran. Polyols of differing molecular weights can be used together in a single formulation. Multiple polyols can be used in a single formulation.
  • the polyurethanes of this invention are based on diol, diamine, alkanolamine, water chain extenders or mixtures of these.
  • Diol chain extenders react with isocyanate to generate urethane linkages.
  • Most diols or diamines make suitable chain extenders.
  • chain extenders include, ethylene glycol, 1,4 butanediol, diethylene glycol, triethylene glycol, 1,2 propane diol, 1,3 propane diol, 1,5 pentane diol, ethylene diamine, 1,4 diaminobutane, 1,6 diaminohexane, 1,7 diaminoheptane, 1,8 diaminooctane, and 1,5 diaminopentane.
  • Useful catalysts are widely available in the marketplace and include organic and inorganic salts of bismuth, lead, tin, iron, antimony, cadmium, cobalt, aluminum, mercury, zinc, cerium, molybdenum, vanadium, copper, manganese and zirconium, as well as phosphines and tertiary amines.
  • Tertiary amines are an important class of catalyst in which the nitrogen atom is not directly attached to an aromatic ring.
  • tertiary armines are: triethylamine, N,N,N′,N′-tetramethylenediamine, N-N,N′,N′-tetramethyl-1,3-butanediamine, bis-2-dimethylaminoethyl ether, N,N-dimethylcyclohexylamine, N,N-dimethylbenzylamine, N-methylmorpholine, N-ethylmorpholine, 1,4-diazabicyclo-[2.2.2] octane and the like.
  • Standard cross-linking agents may also be employed to improve the cross-linked aspect of the material.
  • TEA is an exemplary example.
  • the one shot process, the quasiprepolymer method or the prepolymer method can be used to prepare the polyurethanes of this invention.
  • the solubility parameter and hydrogen bonding parameters of the solvent will affect the suitability of the solvent.
  • the solubility of the solvents of the invention is typically in the region of 17-27 MPa 1 ⁇ 2 . More preferably the solubility parameter is from 18-24 MPa 1 ⁇ 2 .
  • the solvent system used for the extract system should have a solubility parameter in the same range as that of the biomaterial or scaffold.
  • Solvents that may be used include methylethyl ketone, tetrahydrofuran, 1,2-dichloroethane, propan-2-ol, and combinations of the above. Many other solvents have suitable properties and could equally be employed.
  • the materials are mixed at 50-60° C. for a minimum of 25-30 minutes.
  • the polyol resin is stored in containers, under a blanket of nitrogen gas.
  • An isocyanate pre-polymer is prepared from flake MDI (Desmodur from Bayer) and PTMEG (Terathane 1000 MW from DuPont). The amount of MDI and polyol used yield a NCO % content by weight of 15.6% and can be readily determined by those skilled in the art.
  • a number of polyether polyurethane biomaterials are prepared at varying isocyanate indices using techniques described in our copending patent. The following isocyanate index materials were reacted and cured in a cylindrical mould; 0.95, 0.99, 1.04, 1.08, 1.13, 1.18, 1.23 and 1.29. The samples were cut to a length of 15 mm and had a diameter of 21.5 mm.
  • a 250 ml wide necked conical flask was filled with MEK to the 250 ml mark.
  • a separate flask was used for samples of each index. Five samples were placed in each flask. The flasks were stoppered and placed in a water filled ultrasonic bath. The bath was at room temperature. The flasks were sonified for 6 hours. After the 6 hours the samples were removed from the flask by pouring the contents into a sieve. The samples were rinsed in water and placed in an oven at 80° C. to dry. The samples were weighed at 30 minute intervals until the weight stabilised. The weight loss for each sample was measured.
  • This biomaterial scored zero when subjected to the Cytotoxicity test as outlined in ISO standard 10993-5. This is the lowest possible score with this test method. This means that when cell growth media, previously incubated with the biomaterial, supported the growth of L-929 cells and did not induce a cytopathic effect. Media incubated with cytotoxic materials induce cytopathic effects when incubated with L-929 cells. The extent of cytopathic effect can be correlated to the cytotoxicity of the biomaterial.
  • This polyether polyurethane biomaterial was also implanted in the gluteal muscle of rats and left for up to 6 months. The histological analysis conducted on the explants indicated that the implant was well tolerated in the animal model and did not induce any adverse inflammatory response.

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US09/985,821 1999-05-07 2001-11-06 Biostability of polymeric structures Abandoned US20020072584A1 (en)

Applications Claiming Priority (5)

Application Number Priority Date Filing Date Title
PCT/IE1999/000038 WO2000067812A1 (fr) 1999-05-07 1999-05-07 Biostabilite de structures polymeres
IEPCT/IE99/00038 1999-05-07
IEPCT/IE99/00037 1999-05-07
PCT/IE1999/000037 WO2000067811A1 (fr) 1999-05-07 1999-05-07 Produit de polyether-polyurethane biostable
PCT/IE2000/000058 WO2000067814A1 (fr) 1999-05-07 2000-05-08 Biostabilite de structures polymeriques

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PCT/IE2000/000058 Continuation WO2000067814A1 (fr) 1999-05-07 2000-05-08 Biostabilite de structures polymeriques

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US09/985,819 Abandoned US20020072550A1 (en) 1999-05-07 2001-11-06 Biostable polyurethane products
US09/985,821 Abandoned US20020072584A1 (en) 1999-05-07 2001-11-06 Biostability of polymeric structures
US11/152,780 Abandoned US20070003594A1 (en) 1999-05-07 2005-06-15 Tissue engineering scaffold
US12/271,336 Expired - Fee Related US8168431B2 (en) 1999-05-07 2008-11-14 Tissue engineering scaffold comprising polyurethane material having voids interconnected by pores

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US11/152,780 Abandoned US20070003594A1 (en) 1999-05-07 2005-06-15 Tissue engineering scaffold
US12/271,336 Expired - Fee Related US8168431B2 (en) 1999-05-07 2008-11-14 Tissue engineering scaffold comprising polyurethane material having voids interconnected by pores

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AU4606700A (en) 2000-11-21
DE60003178D1 (de) 2003-07-10
DE60003178T2 (de) 2004-04-08
US8168431B2 (en) 2012-05-01
US20020072550A1 (en) 2002-06-13
WO2000067814A1 (fr) 2000-11-16
WO2000067813A1 (fr) 2000-11-16
EP1176995A1 (fr) 2002-02-06
EP1176994A1 (fr) 2002-02-06
AU4606600A (en) 2000-11-21
AU4426600A (en) 2000-11-21
EP1176993A1 (fr) 2002-02-06
EP1176993B1 (fr) 2003-06-04
WO2000067815A1 (fr) 2000-11-16
US20090163612A1 (en) 2009-06-25

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