WO2002049688A1 - Materiaux polymeres biocompatibles - Google Patents

Materiaux polymeres biocompatibles Download PDF

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Publication number
WO2002049688A1
WO2002049688A1 PCT/GB2001/005583 GB0105583W WO0249688A1 WO 2002049688 A1 WO2002049688 A1 WO 2002049688A1 GB 0105583 W GB0105583 W GB 0105583W WO 0249688 A1 WO0249688 A1 WO 0249688A1
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WIPO (PCT)
Prior art keywords
additive
bio
compatible
moieties
polymer
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PCT/GB2001/005583
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English (en)
Inventor
Brian Wilson
John Neil Devine
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Victrex Manufacturing Limited
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Priority to AU2002222245A priority Critical patent/AU2002222245A1/en
Publication of WO2002049688A1 publication Critical patent/WO2002049688A1/fr

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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L29/00Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
    • A61L29/04Macromolecular materials
    • A61L29/06Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L27/00Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/14Macromolecular materials
    • A61L27/18Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L31/00Materials 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
    • A61L31/04Macromolecular materials
    • A61L31/06Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds

Definitions

  • This invention relates to bio-compatible polymeric materials and particularly, although not exclusively, provides a bio-compatible polymeric material, a method of producing such a material and the use of such a material in medical treatment, for example in a prosthesis.
  • prosthetic devices such as orthopaedic, dental or maxill ⁇ facial implants.
  • prosthetic devices such as orthopaedic, dental or maxill ⁇ facial implants.
  • nearly half a million patients receive bone implants each year in the US with the majority being artifical hip and knee joints made from titanium or colbalt-chrome alloys.
  • these materials are too stiff leading to bone resorption, loosening of the implant and, consequently, have lifetimes of less than 10 years.
  • medical devices or prostheses such as pacemakers, vascular grafts, stents, heart valves, catheters and dental implants that contact body tissues or fluids of living persons or animals have been developed and used clinically.
  • a bio-compatible polymeric material for use in medical applications, wherein said material comprises a polymer and an additive, wherein bio-compatible moieties are associated with moieties at the ends of chains of the additive.
  • bio-compatible has generally been used to refer to a material which is compatible with use in medical applications, for example by not being toxic or otherwise harmful to living materials. It also encompasses materials which have a biological or physiological effect when associated with living materials.
  • Bio-compatible moieties suitably refer to moieties which are compatible with use in medical applications, for example by not being toxic or otherwise harmful to living material. Such bio-compatible moieties may be arranged to bond (for example to form ionic or covalent bonds) or otherwise interact with materials present in human or animal bodies in order to improve their integration and acceptance by such bodies .
  • any alkyl, akenyl or alkynyl moiety suitably has up to 8, preferably up to 6, more preferably up to 4, especially up to 2, carbon atoms and may be of straight chain or, where possible, of branched chain structure.
  • methyl and ethyl are preferred alkyl groups and C 2 alkenyl and alkynyl groups are preferred.
  • optional substituents of an alkyl, alkenyl or alkynyl group may include halogen atoms, for example fluorine, chlorine, bromine and iodine atoms, and nitro, cyano, alkoxy, hydroxy, a ino, alkylamino, sulphinyl, alkylsulphinyl, sulphonyl, alkylsulphonyl, amido, alkylamido, alkoxycarbonyl, haloalkoxycarbonyl and haloalkyl groups.
  • optionally substituted alkyl, alkenyl or alkynyl groups are unsubstituted.
  • said bio-compatible polymeric material has improved or enhanced bio-compatibility compared to said polymer in the absence of said additive having bio- compatible moieties associated therewith.
  • said additive when associated with bio-compatible moieties has improved or enhanced bio-compatibility compared to said additive in the absence of associated said moieties.
  • Bio-compatible moieties suitably include moieties arranged to reduce adverse biological reactions when the polymeric material is introduced into (or otherwise associated with) a human or animal body.
  • adverse biological reactions associated with introduction into a human or animal body of said polymer having said bio-compatible moieties may be less compared to use of the same polymer but which does not include associated bio- compatible moieties.
  • said polymer has phenyl moieties; carbonyl or sulphone moieties; and ether or thioether moieties in the polymer backbone.
  • said polymer has a moiety of formula
  • phenyl moieties in units I, II, and III are independently optionally substituted and optionally cross- linked; and wherein m,r,s,t,v,w and z independently represent zero or a positive integer, E and E' independently represent an oxygen or a sulphur atom or a direct link, G represents an oxygen or sulphur atom, a direct link or a -0-Ph-O- moiety where Ph represents a phenyl group and Ar is selected from one of the following moieties (i)*, (i)**, (i) to (x) which is bonded via one or more of its phenyl moieties to adjacent moieties
  • the middle phenyl may be 1,4- or 1,3- substituted.
  • a phenyl moiety may have 1,4- or 1,3-, especially 1,4-, linkages to moieties to which it is bonded.
  • Said polymer may include more than one different type of repeat unit of formula I; more than one different type of repeat unit of formula II; and more than one different type of repeat unit of formula III. Preferably, however, only one type of repeat unit of formula I, II and/or III is provided.
  • Said moieties I, II and III are suitably repeat units.
  • units I, II and/or III are suitably bonded to one another - that is, with no other atoms or groups being bonded between units I, II, and III.
  • phenyl moieties in units I, II or III are optionally substituted, they may be optionally substituted by one or more halogen, especially fluorine and chlorine, atoms or alkyl, cycloalkyl or phenyl groups.
  • Preferred alkyl groups are C ⁇ _ ⁇ o, especially C ⁇ _ 4 , alkyl groups.
  • Preferred cycloalkyl groups include cyclohexyl and multicyclic groups, for example adamantyl.
  • said phenyl moieties are not optionally- substituted as described.
  • said polymer is cross-linked, it is suitably cross-linked so as to improve its properties.
  • Any suitable means may be used to effect cross-linking.
  • cross-linking between polymer chains may be effected via sulphur atoms on respective chains.
  • said polymer is not optionally cross-linked as described.
  • the respective phenylene moieties may independently have 1,4- or 1,3-linkages to the other moieties in the repeat units of formulae II and/or III.
  • said phenylene moieties have 1,4- linkages.
  • the polymeric chain of the polymer does not include a -S- moiety.
  • G represents a direct link.
  • a represents the mole % of units of formula I in said polymer, suitably wherein each unit I is the same;
  • "b” represents the mole % of units of formula II in said polymer, suitably wherein each unit II is the same;
  • "c” represents the mole % of units of formula III in said polymer, suitably wherein each unit III is the same.
  • a is in the range 45-100, more preferably in the range 45-55, especially in the range 48-52.
  • the sum of b and c is in the range 0-55, more preferably in the range 45-55, especially in the range 48- 52.
  • the ratio of a to the sum of b and c is in the range 0.9 to 1.1 and, more preferably, is about 1.
  • the sum of a, b and c is at least 90, preferably at least 95, more preferably at least 99, especially about 100.
  • said polymer consists essentially of moieties I, II and/or III.
  • Said polymer may be a homopolymer having a repeat unit of general formula or a homopolymer having a repeat unit of general formula
  • A, B, C and D independently represent 0 or 1 and E,E' ,G,Ar,m,r,s, t,v,w and z are as described in any statement herein.
  • said polymer may be a homopolymer having a repeat unit of general formula
  • A, B, C, and D independently represent 0 or 1 and E, E', G, Ar, m, r, s, t, v, w and z are as described in any statement herein.
  • m is in the range 0-3, more preferably 0-2, especially 0-1.
  • r is in the range 0-3, more preferably 0-2, especially 0-1.
  • t is in the range 0-3, more preferably 0-2, especially 0-1.
  • s is 0 or 1.
  • v is 0 or 1.
  • w is 0 or 1.
  • z is 0 or 1.
  • said polymer is a homopolymer having a repeat unit of general formula IV.
  • Ar is selected from the following moieties (xi)*, (xi)**,(xi) to (xxi) :
  • the middle phenyl may be 1,4- or 1,3- substituted.
  • (xv) is selected from a 1,2-, 1,3-, or a 1,5- moiety;
  • (xvi) is selected from a 1,6-, 2,3-, 2,6- or a
  • One preferred class of polymers does not include any moieties of formula III, but suitably only includes moieties of formulae I and/or II .
  • said polymer is a homopolymer or random or block copolymer as described, said homopolymer or copolymer suitably includes a repeat unit of general formula IV.
  • Such a polymer may, in some embodiments, not include any repeat unit of general formula V.
  • Suitable moieties Ar are moieties (i)*, (i) , (ii) , (iii) and (iv) and, of these, moieties (i)*, (i) and (iv) are preferred.
  • Other preferred moieties Ar are moieties (xi)*, (xii) , (xi) , (xiii) and (xiv) and, of these, moieties (xi)*, (xi) and (xiv) are especially preferred.
  • polymers which consist essentially of phenyl moieties in conjunction with ketone and/or ether moieties. That is, in the preferred class, the polymer does not include repeat units which include -S-, -S0 2 - or aromatic groups other than phenyl.
  • Preferred polymers of the type described include:
  • polymers described in (a) and (b) are preferred, with the polymer described in (a) being especially preferred.
  • bio-compatible moieties are preferably associated with the surface of said bio-compatible polymeric material and, suitably, do not substantially penetrate the bulk of the material.
  • moieties at the ends of chains of said additive within the bulk thereof are different compared to moieties (i.e. bio-compatible moieties) associated with ends of chains of said additive at the surface of the bio- compatible polymeric material.
  • the concentration of bio-compatible moieties at a surface of said bio- compatible polymeric material is preferably greater than the concentration in the bulk of said material . Consequently, said bio-compatible moieties are suitably associated with chain ends of said additive which are at the surface of the polymer.
  • the concentration of chain end moieties at the surface may be greater than the concentration in the bulk. Chain ends of said additive below the surface of the polymeric material preferably do not include associated bio-compatible moieties.
  • Said additive suitably makes up at least 0.1 wt%, preferably at least 0.3 wt%, more preferably at least 0.5 wt%, especially at least 0.7 wt% of said bio-compatible polymeric material .
  • the amount of said additive in said bio-compatible polymeric material may be less than 5 wt%, preferably less than 4 wt%, more preferably less than 3 wt%, especially less than 2 wt%.
  • a moiety at the end of a chain of the additive may be situated at the end of a chain (which could be a branched or straight chain but is preferably a straight chain) which has at least 4, suitably at least 6, preferably at least 8, more preferably at least 10, especially at least 12 chain atoms, which are preferably carbon atoms.
  • Said moiety may be situated at the end of a chain (preferably a carbon atom chain) which has at least 4, suitably at least 6, preferably at least 8, more preferably at least 10, especially at least 12 chain atoms, which are preferably carbon atoms in a line (i.e. the number of chain atoms referred to does not include any chain atoms which may form branches extending from the atoms which are in a line) .
  • Said additive may include chain atoms which form branches extending from atoms in a line but preferably does not include branches .
  • said additive includes branches, preferably the branches do not include moieties which are, or are arranged to be, associated with the bio- compatible moieties of the bio-compatible material.
  • Said moiety at . the end of a chain of said additive is preferably situated at an end of a line of atoms (preferably a line of carbon atoms) which is the longest line of atoms of said additive.
  • Said additive suitably includes less than 4, preferably less than 3, more preferably less than 2, moieties associated with bio-compatible moieties.
  • Said additive preferably includes a single moiety associated with a bio-compatible moiety and preferably includes no other moiety capable of being associated with bio- compatible moieties.
  • Said additive is preferably not a polymer having moieties I, II and/or III as described above for said polymer.
  • said additive is not any type of polymer.
  • Said additive is preferably an optionally-substituted hydrocarbon, more preferably an optionally-substituted alkane, alkene, or alkyne especially an optionally- substituted alkane.
  • Said additive may have at least 6, suitably at least 8, preferably at least 10, more preferably at least 12, especially at least 14 carbon atoms.
  • the number of carbon atoms may be less than 30, suitably less than 25, preferably less than 20, more preferably less than 18.
  • the invention extends to a bio-compatible polymeric material for use in medical applications, wherein said material comprises a polymer and an additive, wherein a surface of said material includes said additive, with bio- compatible moieties being associated with moieties at the end of chains of the additive and wherein the bulk of said polymeric material does not include associated bio- compatible moieties.
  • the concentration of bio-compatible moieties at the surface of said polymeric material is greater than the concentration in the bulk.
  • Said polymer may include fluorine atoms associated with its chain ends.
  • the glass transition temperature (T g ) of said polymer may be at least 135°C, suitably at least 150°C, preferably at least 154°C, more preferably at least 160°C, especially at least 164°C. In some cases, the Tg may be at least 170°C, or at least 190°C or greater than 250°C or even 300°C.
  • Said polymer suitably the bulk thereof, (in the absence of said additive and/or associated bio-compatible moieties) may have an inherent viscosity (IV) of at least 0.1, suitably at least 0.3, preferably at least 0.4, more preferably at least 0.6, especially at least 0.7 (which corresponds to a reduced viscosity (RV) of least 0.8) wherein RV is measured at 25°C on a solution of the polymer in concentrated sulphuric acid of density 1.84gcm "3 , said solution containing lg of polymer per 100cm "3 of solution. IV is measured at 25°C on a solution of polymer in concentrated sulphuric acid of density 1.84gcm 3 , said solution containing 0. lg of polymer per 100cm 3 of solution.
  • IV is measured at 25°C on a solution of polymer in concentrated sulphuric acid of density 1.84gcm 3 , said solution containing 0. lg of polymer per 100cm 3 of solution.
  • both RV and IV both suitably employ a viscometer having a solvent flow time of approximately 2 minutes .
  • the main peak of the melting endotherm (Tm) for said polymer suitably the bulk thereof, (if crystalline) may be at least 300°C.
  • said polymer suitably the bulk thereof,
  • crystallinity in the absence of said additive and/or associated bio- compatible moieties, has at least some crystallinity or is crystallisable.
  • the existence and/or extent of crystallinity in a polymer is preferably measured by wide angle X-ray diffraction, for example as described by Blundell and Osborn (Polymer 24, 953, 1983) .
  • crystallinity may be assessed by Differential Scanning Calorimetry (DSC) .
  • Said polymer suitably the bulk thereof, (in the absence of said additive and/or associated bio-compatible moieties) may have a number average molecular weight in the range 2000-80000. Preferably said molecular weight is at least 14,000. The molecular weight may be less than 60,000.
  • Said bio-compatible polymeric material may include a blend of polymers which comprises said polymer along with another polymer which is preferably a different type of polymer compared to said polymer but may otherwise have any feature of said polymer described here. For example, it may include moieties I and/or II and/or III.
  • Said bio-compatible polymeric material suitably has a tensile strength (according to ISO R527) of at least 80, preferably at least 90, especially at least 95 MPa.
  • the tensile strength may be less than 360, suitably less than
  • It preferably less than 140 MPa. It preferably has an elongation at break (according to ISO R527) of at least 40, preferably at least 50%. It preferably has a tensile modulus (according to ISO R527) of greater than 2.5, preferably greater than 3, especially greater than 3.5
  • the tensile modulus may be less than 40, suitably less than 30, preferably less than 20, more preferably less than 10 GPa. It preferably has a flexural strength
  • the flexural strength may be less than 650, preferably less than 400, more preferably less than 260, especially less than 200 MPa. It preferably has a flexural modulus (according to ISO R178) of at least 3, preferably at least 3.5, especially at least 4 GPa.
  • the flexural modulus may be less than 60, suitably less than 25, preferably less than 20 especially less than 10 GPa.
  • the aforementioned properties can be adjusted by appropriate selection of polymers and/or any reinforcement means included in said support material to suit particular applications.
  • a continuous carbon fibre polyetheretherketone may typically have a tensile strength of about 350 MPa, a tensile modulus of 36 GPa, an elongation of 2%, a flexural modulus of 50 GPa and a flexural strength of 620 MPa.
  • a polyaryetherketone with 30% of high performance fibres typically may have a tensile strength of 224 MPa, a tensile modulus of 13 GPa, a tensile elongation of 2%, a flexural modulus of 20 GPa and a flexural strength of 250 MPa.
  • Said bio-compatible polymeric material may include one or more fillers for providing desired properties.
  • Said material preferably incorporates an X-ray contrast medium. Fillers and/or said X-ray contrast medium is/are preferably distributed substantially uniformly throughout said material.
  • an X-ray contrast medium suitably comprises less than 25wt%, preferably less than 20wt%, more preferably less than 15wt%, especially less than 10wt% of said bio-compatible material. Where it is provided, at least 2wt% may be included.
  • Preferred X-ray contrast mediums are particulate and preferably are inorganic. They preferably have low solubility in body fluids. They preferably also have a sufficient density compared to that of the polymer to create an image, if a compounded mixture of the polymer and contrast medium are X-ray imaged. Barium sulphate and zirconium oxide are examples. Said particulate material is suitably physically held in position by entrapment within the polymer.
  • said bio-compatible polymeric material includes a major amount of said polymer, especially one having moieties I, II and/or III, described according to said first aspect.
  • a “major” amount may mean greater than 50 wt%, suitably greater than 65 wt%, preferably greater than 80 wt%, more preferably greater than 95 wt%, especially greater than 98 wt% of the referenced material is present relative to the total weight of relevant material present .
  • said blend preferably includes at least two polymers of a type according to said first aspect.
  • said at least two polymers preferably include moieties I, II and/or III as described above.
  • a said blend preferably includes a major amount of higher (or the highest) number average molecular weight polymer.
  • Said bio-compatible polymeric material preferably includes a major amount of a higher molecular weight polymer.
  • a said bio-compatible moiety may be selected from an anticoagulant agent such as heparin and heparin sulfate, an antithrombotic agent, a clotting agent, a platelet agent, an anti-inflammatory agent, an antibody, an antigen, an immunoglobulin, a defence agent, an enzyme, a hormone, a growth factor, a neurotransmitter, a cytokine, a blood agent, a regulatory agent, a transport agent, a fibrous agent, a protein such as avidin, a glycoprotein, a globular protein, a structural protein, a membrane protein and a cell attachment protein, a peptide such as a glycopeptide, a structural peptide, a membrane peptide and a cell attachment peptide, a proteoglycan, a toxin, an antibiotic agent, an antibacterial agent, an antimicrobial agent such as pencillin, ticarcillin, carbenicillin, ampicillin, oxacillian, cefazolin
  • PEG poly(ethylene glycol)
  • PEO poly(ethylene oxide)
  • PEO poly(ethylene oxide)
  • PNVP poly(N-vinyl-2- pyrrolidone)
  • PNVP poly (2-hydroxyethyl methacrylate
  • HEMA HEMA co-polymers
  • PVA poly (vinyl alcohol)
  • PVA polyacrylamide
  • PMMA polyacrylamide
  • PMMA suitably having a PEG chain on each of the side groups, polysiloxanes (e.g. polydimethylsiloxanes (PDMS)), ionic water-soluble polymers like poly(acrylic acid) (PAAc) ) and a polyurethane .
  • PDMS polydimethylsiloxanes
  • PAAc poly(acrylic acid)
  • said bio-compatible moieties may comprise bone morphogenic protein (BMP) as described in US4563489 and patents cited therein and the contents of the aforesaid are incorporated herein.
  • BMP bone morphogenic protein
  • Said BMP may be provided in combination, for example in admixture, with a physiologically acceptable biodegradable organic polymer and said biodegradable polymer may be associated with moieties at the ends of chains of the additive, for example by being covalently bonded to moieties at the ends of chains.
  • the combination of said biodegradable polymer and BMP defines said bio-compatible moieties.
  • Said biodegradable polymer is preferably a biodegradable polylactic acid; or alternatively, other physiologically acceptable biodegradable organic polymers which are structurally equivalent to polylactic acid can be used as the delivery system for BMP.
  • examples include poly(hydroxy organic carboxylic acids) e.g. poly(hydroxy aliphatic carboxylic acids) , polyglycollic acid, polyglactin, polyglactic acid and poly adonic acids.
  • said bio-compatible moieties may be selected from inorganic crystalline structures, inorganic amorphous structures, organic crystalline structures and organic amorphous structures .
  • Preferred bio-compatible moieties are phosphorous based ceramics, for example calcium-phosphorous ceramics. Phosphates in general are suitable but calcium phosphates and calcium apatite are preferred. Especially preferred is hydroxyapatite, a synthetic Ca-P ceramic.
  • Linking moieties for example linking atoms or groups may extend between said additive and said bio-compatible moieties. Said linking moieties may be covalently bonded to moieties at the ends of chains of said additive. Said linking moieties may be covalently bonded to said bio- compatible moieties or may otherwise be associated with said moieties.
  • a said linking moiety may be associated with a single bio-compatible moiety or, alternatively, a said linking moiety may be associated with more than one bio-compatible moiety.
  • said linking moiety may be mono-functional or multi-functional, for association with one or more bio- compatible moieties.
  • Multi-functional linking moieties may be able advantageously to be associated with more bio- compatible moieties and may, therefore, provide a means to increase the concentration of bio-compatible moieties associated with said additive.
  • bio-compatible moieties may be associated with moieties at the ends of chains of said additive by any suitable means, for example covalent bond(s), hydrogen bond(s) , encapsulation in a matrix which is bonded to or otherwise interacts with said end groups, or ionic interaction (s) , it is preferred that there are covalent bonds between the bio-compatible moieties and said additive or there are ionic interactions between said bio- compatible moieties and said additive.
  • An additive/bio-compatible moiety arrangement may be represented by the formula:
  • AC-EG' .BM' where AC represents a said additive chain which suitably is a low molecular weight chain, suitably with Mn ranging from 250-3000 which is suitably arranged to anchor the additive into the polymer; EG 1 represents a moiety at the end of said chain; and BM 1 represents a bio-compatible moiety.
  • EG 1 may include said aforementioned linking moiety.
  • EG' and EG' .BM 1 may be the same, for example where an end group of the additive is itself bio- compatible. A -S0 3 H end group may fall into this category. Preferably, however, EG' and EG' .BM' represent different moieties.
  • the bond between AC and EG' is suitably a covalent bond.
  • the interaction between EG' and BM' may be by any suitable means as described above.
  • the interaction is preferably by means of a covalent bond or an ionic interaction.
  • a method of making a bio-compatible polymeric material for use in medical applications including the step of causing bio-compatible moieties to become associated with moieties at the ends of chains of an additive, wherein said additive is mixed with a polymer.
  • the method includes the step of blending said polymer and said additive, suitably at an elevated temperature, suitably at greater than 200°C, preferably at greater than 300°C, more preferably at greater than 325°C, especially at greater than 350°C.
  • the blending is preferably undertaken using a high shear mixer.
  • the amount of said additive in said blend may be at least 0.2 wt%, suitably at least 0.4 wt%, preferably at least 0.6 wt%, more preferably at least 0.8 wt%.
  • the amount may be less than 5 wt%, suitably less than 4 wt%, preferably less than 3 wt%, more preferably less than 2 wt%, especially less than 1.5 wt%.
  • the method preferably includes the step of treating a mixture of the polymer and the additive so that, when in solid form, the concentration of additive at a surface of the solid is greater than in the bulk of the solid.
  • the method preferably includes treating the mixture to cause migration of additive to a surface of a solid.
  • Said additive preferably includes a functional group at the end of a chain thereof, wherein preferably said functional group facilitates the migration of the additive to a surface of the solid.
  • said functional group is preferably relatively incompatible with the polymer which suitably forms a major part of the bio-compatible material.
  • a mixture of polymer and additive may be treated by injection moulding. In the melt, the additive should be evenly distributed through the bulk of the polymer. However, as the polymer begins to cool additive molecules, suitably having relatively short chains, migrate to the surface.
  • a said functional group of said additive may be post- functionalised to enable association with bio-compatible moieties.
  • the method preferably includes the step of treating a mixture of said polymer and said additive with a material for providing bio-compatible moieties (hereinafter "BCM material") arranged to provide bio-compatible moieties for association with moieties at the ends of chains of the additive.
  • BCM material a material for providing bio-compatible moieties
  • Said BCM material may be arranged to provide any of the bio-compatible moieties described herein.
  • Said mixture comprising said polymer and said additive may be provided as a solid.
  • said bio-compatible moieties are caused to become associated with a surface of said solid, preferably with moieties at the ends of chains of the additive present at a surface of said solid.
  • Said solid is preferably shaped so as to represent at least a part of a device for use in medical applications.
  • said device may be a component of an implant for a human or animal body, for example an orthopaedic or dental implant or vascular graft.
  • Said solid may be provided in a desired shape by any suitable means, for example by injection or compression moulding or by film formation techniques or extrusion.
  • the bio-compatible polymeric material is not engineered or otherwise treated in a manner which may result in substantial depletion of the bio-compatible moieties associated with its surface.
  • association of bio-compatible moieties with said moieties at the ends of chains may be effected in any suitable way which will depend on the nature of the BCM material and/or the identity of moieties at the ends of chains of the additive.
  • the method may include causing covalent bond formation between the additive and said bio-compatible moieties.
  • association of the additive and bio- compatible moieties may be effected by other means, for example by ionic interactions.
  • the method may include the step of treating an additive of general formula
  • AC represents a said additive chain and EG represents a moiety at the end of the chain with a material (BM) arranged to supply a bio-compatible material (BM 1 ) thereby to produce an additive bio-compatible moiety arrangement represented by the formula AC-EG' .BM' as described above wherein EG' .BM' represents an association between a moiety at the end of a chain of the additive and the bio-compatible material, wherein EG' represents a residue of end group EG or may represent EG, for example where there is no covalent bond formation between EG 1 and BM' ; and BM' represents a residue of bio-compatible material BM or may represent BM where there is no covalent bond formation between EG' and BM' .
  • EG may include any suitable functional groups arranged to become associated with suitable functional groups provided on BM.
  • BM may include any suitable functional group that is arranged to become associated with functional groups included in EG and may be selected from any of the functional groups referred to above for EG provided that a selected functional group provided by EG is capable of becoming associated with, suitably reacting, with a selected functional group provided by BM.
  • BM may be provided by reaction of EG with more than one functional group.
  • a BM' may represent a polyurethane which may be prepared when EG provides a hydroxy group and BM provides a diisocyanate and a diol; or wherein EG provides an isocyanate group and BM provides a diisocyanate and a diol. In both cases, two different compounds BM may be used.
  • BM may be provided by a monomer or monomers having a functional group arranged to react with EG and being arranged to polymerise to provide a polymeric moiety BM' .
  • EG may be ionic in character, for example it may be -COOM or -S0 3 M and such a group may be arranged to ionically associate with an ionic moiety provided by BM.
  • an amide bond may be formed between EG and BM.
  • said group EG may be multi-functional, thereby enabling it to associate with a plurality of bio- compatible moieties.
  • multi-functionality may be provided by dendritic or hyperbranched end groups.
  • the polymer comprising moieties I, II and/or III may be prepared as described in WO00/15691 and/or EP1879, the contents of which are incorporated herein by reference.
  • the aforementioned document describes processes for preparing the polymers which are generally nucelophilic processes. Nonetheless, electrophilic processes can be used, by analogy to the processes described in US 5081215, US4808693, US4708448 and US5081215.
  • a device for use in medical applications wherein said device comprises a bio- compatible polymeric material according to said first aspect or made in a method according to said second aspect .
  • Said device is preferably a prosthetic device, for example an implant such as an orthopaedic, dental or maxillofacial implant or a component thereof; or a device, for example a catheter, which is arranged to be temporarily associated with a human or animal body.
  • Said device is preferably a prosthetic device as described.
  • An orthopaedic device may be an implant for a body joint, for example a hip or knee joint or spine fusion device.
  • a said device may include a part or parts made out of said bio-compatible polymeric material and a part or parts made out of other materials.
  • said device includes at least 50wt%, preferably at least 65wt%, more preferably at least 80wt%, especially at least 95wt% of said bio-compatible polymeric material.
  • said device may consist essential of said bio- compatible polymeric material .
  • a method of making a device comprising: forming a material into a shape which represents or is a precursor of a device or a part of a device for use in medical applications wherein said material comprises a polymer and an additive wherein moieties at the ends of chains of the additive are arranged to be associated with bio-compatible moieties; and treating material in said shape (preferably the surface thereof) thereby to cause bio-compatible moieties to associate with said moieties at the ends of chains of the additive (preferably moieties present at or near the surface of said material) .
  • the invention extends to the use of a bio-compatible polymeric material comprising a polymer and an additive, wherein bio-compatible moieties are associated with moieties at the ends of chains of the additive in the manufacture of a device for use in a medical treatment, for example in surgery. Any feature of any aspect of any invention or embodiment described herein may be combined with any feature of any aspect of any other invention or embodiment described herein.
  • the reaction mixture was allowed to cool, milled and washed with acetone and water.
  • the resulting polymer was dried in an air oven at 120°C.
  • the polymer had Inherent Viscosity (IV) of 1.15. IV is measured at 25°C on a solution of polymer in concentrated sulphuric acid of density 1.84 gem "3 , said solution containing O.lg of polymer per 100cm 3 of solution.
  • Example 2 Blending of polyetheretherketone with hexadecanesulphonic acid sodium salt
  • the sodium salt migrates to the surface and this can be shown by determining the level of sulphur on the surface of the blend (e.g. by X- ray. photoelectron spectroscopy (XPS) ) and comparing it to the polymer of Example 1 in the absence of any additive.
  • XPS X- ray. photoelectron spectroscopy
  • Example 2 The polymer film of Example 2 was placed in a 250ml flanged flask fitted with a reflux condenser, a magnet follower and a nitrogen inlet and outlet and with charged 0.1M hydrochloric acid (120ml) . Under a nitrogen atmosphere and with continuous stirring the contents were heated to 50°C for 6 hours. The reaction mixture was allowed to cool to room temperature, the sample was removed, washed with deionised water until the pH was neutral and dried.
  • Example 4 Calcium Phosphate Deposition on a sulphonic acid and sodium sulphonate-surface modified polyetheretherketone .
  • a supersaturated calcium phosphate solution containing 5mM CaCl 2 , l,5mM KH 2 P0 4 and 1.5mM Na 2 HP0 4 was prepared by mixing 0.1M Na 2 HP0 4 solution (1.5ml) and deionised water (92ml), followed by the slow addition of 0.1M CaCl 2 solution (5.0ml). The solution was stirred for 3 minutes and film samples, from Examples 2 and 3, were immersed in the solution for 1 hour. The films were washed with deionised water and blown dry with nitrogen. The process can be repeated several times to achieve a desired thickness of deposited calcium phosphate.
  • Example 5 Blending of polyetheretherketone with hexadecylaniline.
  • the film of the surface modified polyetheretherketone of Example 5 was placed in a 250ml round-bottomed flask fitted with a magnetic follower and a nitrogen inlet and outlet and containing N,N-dimethylacetamide (60ml) , and disuccinimidylsuberate (150mg) .
  • the contents were stirred under an atmosphere of nitrogen at room temperature for 2 hrs.
  • the specimen was removed, washed with ether and dried in vacuo for lOhrs at 50°C.
  • the dried sample was stirred at 20°C for 24 hr under an atmosphere of nitrogen in a solution of the peptide GRGDS (80mg) in an aqueous buffer solution (40ml), pH 9.
  • the functionalised polyetheretherketone was washed successively with the buffer solution and ether.
  • Example 1 The polymer of Example 1 was blended with octadecanamide (1% w/w) at 360°C in a Brabender high shear mixer which was continuously purged with nitrogen. The mixture was compression moulded to produce a film 5 cm x 5cm x 125 ⁇ m.
  • Example 9 Reaction of surface modified polyetheretherketone containing carboxylic acid groups with the peptide GRGDS
  • a surface modified polyetheretherketone film from Example 8 was stirred at 10°C for 1 hr under an atmosphere of nitrogen in an aqueous solution of the water soluble carbodiimide, l-ethyl-3- (3-dimethylamino propyl) - carbodiimide) (8g) dissolved in buffer at pH 4.5 (0.1M 2- (N-morpholino) ethanesulphonic acid) (40ml). The sample of polyetheretherketone was removed and washed with buffer solution.
  • the sample was stirred at 20°C for 24 hr under an atmosphere of nitrogen in a solution of the peptide GRGDS (160mg) in phosphate-buffered saline solution (40ml) (Na 2 HP0 4 , 1.15g; KH 2 P0 4 , 0.2g; NaCl . 8g; KC1, 0.2g; MgCl 2/ O.lg; CaCl 2 . 0. lg in 1 Litre of distilled water) .
  • the functionalised polyetheretherketone was washed successively with phosphate buffer and distilled water. Each carboxyl group of the functionalised polyetheretherketone reacts with a separate peptide.

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  • Health & Medical Sciences (AREA)
  • Chemical & Material Sciences (AREA)
  • Veterinary Medicine (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Public Health (AREA)
  • General Health & Medical Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Epidemiology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Transplantation (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Medicinal Chemistry (AREA)
  • Dermatology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Surgery (AREA)
  • Vascular Medicine (AREA)
  • Materials For Medical Uses (AREA)

Abstract

Matériau polymère biocompatible conçu pour être utilisé dans le domaine médical et comprenant un polymère, par exemple, polyétheréthercétone ou polyéthercétone combiné à un additif, par exemple, hexadécylaniline ou octadécanamide, les fractions biocompatibles étant associées à des fractions situées aux extrémités des chaînes de l'additif.
PCT/GB2001/005583 2000-12-21 2001-12-18 Materiaux polymeres biocompatibles WO2002049688A1 (fr)

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Cited By (2)

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DE102004008314A1 (de) * 2004-02-20 2005-09-15 Friadent Gmbh Verwendung von Zirkonoxid-haltigen Polyaryletherketonen zur Herstellung von Zahnersatz
WO2017109114A1 (fr) * 2015-12-23 2017-06-29 Diania Technologies Limited Objets polymères thermoformés contenant un additif

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US5217492A (en) * 1982-09-29 1993-06-08 Bio-Metric Systems, Inc. Biomolecule attachment to hydrophobic surfaces
US5370696A (en) * 1991-12-09 1994-12-06 Smith & Nephew Richards, Inc. Prosthetic implants with a highly crystalline coating
WO2000015691A1 (fr) * 1998-09-11 2000-03-23 Victrex Manufacturing Limited Polymeres echangeurs d'ions
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US5217492A (en) * 1982-09-29 1993-06-08 Bio-Metric Systems, Inc. Biomolecule attachment to hydrophobic surfaces
US5370696A (en) * 1991-12-09 1994-12-06 Smith & Nephew Richards, Inc. Prosthetic implants with a highly crystalline coating
US6096525A (en) * 1996-11-25 2000-08-01 Meadox Medicals, Inc. Bonding bio-active materials to expanded polytetrafluoroethylene or polyethylene terephthalate via an isocyanate-terminated spacer
WO2000015691A1 (fr) * 1998-09-11 2000-03-23 Victrex Manufacturing Limited Polymeres echangeurs d'ions
DE19902942A1 (de) * 1999-01-26 2000-07-27 Creavis Tech & Innovation Gmbh Aminofunktionalisierte Polyoxyalkane
EP1099468A2 (fr) * 1999-11-10 2001-05-16 DEUTSCHE INSTITUTE FÜR TEXTIL- UND FASERFORSCHUNG STUTTGART Stiftung des öffentlichen Rechts Membrane microporeuse hydrophile

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NOISET OLIVIER ET AL: "Surface modification of poly(aryl ether ether ketone) (PEEK) film by covalent coupling of amines and amino acids through a spacer arm", JOURNAL OF POLYMER SCIENCE, POLYMER CHEMISTRY EDITION, JOHN WILEY AND SONS. NEW YORK, US, vol. 35, no. 17, December 1997 (1997-12-01), pages 3779 - 3790, XP002180806, ISSN: 0887-624X *

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102004008314A1 (de) * 2004-02-20 2005-09-15 Friadent Gmbh Verwendung von Zirkonoxid-haltigen Polyaryletherketonen zur Herstellung von Zahnersatz
DE102004008314B4 (de) * 2004-02-20 2006-02-09 Friadent Gmbh Verwendung von Zirkonoxid-haltigen Polyaryletherketonen zur Herstellung von Zahnersatz
WO2017109114A1 (fr) * 2015-12-23 2017-06-29 Diania Technologies Limited Objets polymères thermoformés contenant un additif

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