WO2008067531A2 - Fiber reinforced composite material - Google Patents

Fiber reinforced composite material Download PDF

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Publication number
WO2008067531A2
WO2008067531A2 PCT/US2007/086067 US2007086067W WO2008067531A2 WO 2008067531 A2 WO2008067531 A2 WO 2008067531A2 US 2007086067 W US2007086067 W US 2007086067W WO 2008067531 A2 WO2008067531 A2 WO 2008067531A2
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WO
WIPO (PCT)
Prior art keywords
composite
composite material
fiber
mpa
matrix
Prior art date
Application number
PCT/US2007/086067
Other languages
French (fr)
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WO2008067531A3 (en
Inventor
John Rose
Malcolm Brown
Nicola Macauley
Mike Hall
Original Assignee
Smith & Nephew, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Smith & Nephew, Inc. filed Critical Smith & Nephew, Inc.
Priority to DE602007011671T priority Critical patent/DE602007011671D1/en
Priority to CN2007800438419A priority patent/CN101594831B/en
Priority to EP07864978A priority patent/EP2120745B1/en
Priority to AU2007325001A priority patent/AU2007325001B2/en
Priority to CA2679365A priority patent/CA2679365C/en
Priority to JP2009539508A priority patent/JP2010511751A/en
Priority to US12/516,573 priority patent/US8722783B2/en
Priority to AT07864978T priority patent/ATE493081T1/en
Publication of WO2008067531A2 publication Critical patent/WO2008067531A2/en
Publication of WO2008067531A3 publication Critical patent/WO2008067531A3/en
Priority to US14/262,018 priority patent/US20140235754A1/en

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Classifications

    • 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
    • A61L31/12Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
    • A61L31/125Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix
    • A61L31/128Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix containing other specific inorganic fillers not covered by A61L31/126 or A61L31/127
    • CCHEMISTRY; METALLURGY
    • C08ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08KUse of inorganic or non-macromolecular organic substances as compounding ingredients
    • C08K7/00Use of ingredients characterised by shape
    • C08K7/02Fibres or whiskers
    • C08K7/04Fibres or whiskers inorganic
    • C08K7/14Glass
    • 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
    • A61L31/12Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
    • A61L31/125Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix
    • A61L31/129Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix containing macromolecular fillers
    • 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
    • A61L31/14Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L31/148Materials at least partially resorbable by the body
    • CCHEMISTRY; METALLURGY
    • C08ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08JWORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
    • C08J5/00Manufacture of articles or shaped materials containing macromolecular substances
    • C08J5/04Reinforcing macromolecular compounds with loose or coherent fibrous material
    • C08J5/0405Reinforcing macromolecular compounds with loose or coherent fibrous material with inorganic fibres
    • C08J5/043Reinforcing macromolecular compounds with loose or coherent fibrous material with inorganic fibres with glass fibres
    • CCHEMISTRY; METALLURGY
    • C08ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08JWORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
    • C08J5/00Manufacture of articles or shaped materials containing macromolecular substances
    • C08J5/04Reinforcing macromolecular compounds with loose or coherent fibrous material
    • C08J5/046Reinforcing macromolecular compounds with loose or coherent fibrous material with synthetic macromolecular fibrous material
    • CCHEMISTRY; METALLURGY
    • C08ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08KUse of inorganic or non-macromolecular organic substances as compounding ingredients
    • C08K3/00Use of inorganic substances as compounding ingredients
    • C08K3/18Oxygen-containing compounds, e.g. metal carbonyls
    • C08K3/24Acids; Salts thereof
    • C08K3/26Carbonates; Bicarbonates
    • CCHEMISTRY; METALLURGY
    • C08ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08KUse of inorganic or non-macromolecular organic substances as compounding ingredients
    • C08K9/00Use of pretreated ingredients
    • C08K9/02Ingredients treated with inorganic substances
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00004(bio)absorbable, (bio)resorbable or resorptive
    • CCHEMISTRY; METALLURGY
    • C08ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08KUse of inorganic or non-macromolecular organic substances as compounding ingredients
    • C08K3/00Use of inorganic substances as compounding ingredients
    • C08K3/18Oxygen-containing compounds, e.g. metal carbonyls
    • C08K3/24Acids; Salts thereof
    • C08K3/26Carbonates; Bicarbonates
    • C08K2003/265Calcium, strontium or barium carbonate

Definitions

  • the present disclosure relates to bioresorbable composites and more specifically to a fiber reinforced polymer composite material that is used to make bioresorbable products, RELATED ART
  • the currently marketed bioresorbable products include those products manufactured from injection molded polymers, polymer blends, and co-polymers. These products have been utilized in the areas of craniomaxilofacial implants and non-load bearing fracture fixation implants, such as pins and screws, for wrist and ankle applications and for reattaching soft tissues, such as ligaments and tendons, to bone. In addition, there are also some spinal products available that make use of the compressive properties of these polymers. Products including these materials are easy to process, but are limited by the mechanical properties of the materials. These materials have a tensile strength in the range of between about 50 MPa to about 100 MPa. Depending on the choice of polymer or co-polymer, products in this category retain the majority of their strength for less than about 12 weeks. Therefore, these materials are not suitable for fracture fixation applications beyond simple non-loaded pins and screws.
  • bioresorbable products include self reinforced products that have improved strength due to orientation of the polymer during processing of the product. Even though these products have improved strength, their flexural strength is still only around 250 MPa. This limits the uses of this technology for fracture fixation to screws and pins.
  • composites have been made where the matrix was a polymer with the same chemical composition as the fiber or where the matrix was a blend with the majority of the blend being a polymer with the same chemical composition as the matrix. These composites have an initial flexural strength of between 120 to 140 MPa, with most of this strength lost within about 12 weeks of use.
  • a fiber polymer composite contains at least 50% of fiber by volume, it would be anticipated that a calcium carbonate-containing matrix would interfere adversely with the interface between the polymer matrix and reinforcing fibers. This could result in the fiber-reinforced composite substantially weakening or even falling apart before complete healing of a fracture.
  • the fiber and matrix material have certain requirements.
  • the fiber needs to have both a high initial tensile strength, and the ability to retain the majority of this strength, for the fracture to heal.
  • the fibers need to be highly orientated and be present at about 40% by volume of the composite.
  • the fibers should also have some crystallinity, as this imparts stability against relaxation of the orientation in the fiber.
  • the matrix material also needs to be able to retain the majority of its strength for a suitable time, approximately between about 6 to about 12 weeks, for the fracture to heal.
  • the matrix should have a sufficiently high initial molecular weight.
  • Additives such as calcium carbonate or other buffering materials, can be added to the matrix to control the degradation rate.
  • the amount of the buffering material should be around 30% by weight of the matrix without adversely interfering with the interface between the polymer matrix and the reinforcing fibers.
  • the matrix material needs to be processable at a temperature which is low enough to not significantly affect the strength of the fiber and adhere well enough to the fiber to allow stress transfer from the matrix to the fiber.
  • both semi- crystalline and amorphous co-polymers can be used.
  • Semi-crystalline co-polymers are typically composed of lactic acid and one or more additional monomer units whose function is to lower the melting point of the co-polymer matrix to a point where the strength of the fiber is not affected during the consolidation step.
  • Amorphous or non- crystalline materials, such as poly (D- lactide) acid polymers, are suitable for processing with the fiber, as they soften at relatively low temperatures. However, these materials do not have a long strength retention time.
  • This strength retention can be improved by incorporating a buffering material, such as calcium carbonate, into the matrix material.
  • a buffering material such as calcium carbonate
  • the calcium carbonate acts as both a buffer and also reduces the thermal sensitivity of the polymer to breakdown during processing.
  • the affect of the calcium carbonate is to both slow the rate of degradation of the polymer and help preserve the molecular weight during processing, without adversely interfering with the interface between the polymer matrix and the reinforcing fibers.
  • the present disclosure incorporates these requirements to produce a bioresorbable material which has a high initial strength and retains a significant proportion of this strength for a useful time.
  • the present disclosure relates to a fiber reinforced composite material including a PLLA fiber material, such as a continuous PLLA fiber material, and a matrix material that does not have the same chemical element composition as the fiber material.
  • the composite further includes a degradation controlling agent dispersed in the matrix material.
  • the degradation controlling agent includes a buffer material selected from a group including calcium carbonate, calcium hydrogen carbonates, calcium phosphates, tricalcium phosphates, dicalcium phosphates, magnesium carbonate, and sodium carbonate.
  • the degradation controlling agent includes a common salt.
  • the degradation controlling agent is selected from a group including a buffer material, a common salt, and combinations thereof.
  • the degradation controlling agent is between about 0.1% to about 40% by weight of the matrix material.
  • the composite further includes an accelerant dispersed in the fiber or matrix material.
  • the PLLA fiber material is about 50% by volume of the composite.
  • the fiber material, which is bioabsorbable has a tensile strength of between about 500 MPa to about 2000 MPa and a molecular weight of between about 290,000 g/mol and about 516,000 g/mol.
  • the matrix material is bioresorbable and is selected from a group including a polymer, a copolymer, and a polymer blend.
  • the blend when a polymer blend is used as the matrix, the blend includes at least two polymers and at least one of the polymers has a chemical element composition that is different to that of the fiber.
  • the polymer having a chemical element composition that is different to that of the fiber comprises at least 50% of the polymer blend.
  • the polymer having a chemical element composition that is different to that of the fiber comprises more than 50% of the polymer blend.
  • the matrix material is bioabsorbable.
  • the composite has an initial tensile strength of at least 250 MPa and retains at least 75% of the initial tensile strength for at least 8 weeks.
  • the composite material includes a flexural strength of about 200 MPa and a shear strength of at least 140 MPa.
  • the present disclosure includes a fiber reinforced composite material having a matrix material, a glass fiber material, and a degradation controlling agent.
  • the matrix material is selected from a group including a polymer, a copolymer, and a polymer blend.
  • the matrix material is bioabsorbable.
  • the glass fiber material is bioabsorbable.
  • the glass fiber material includes a tensile strength between about 300 MPa and about 1200 MPa.
  • the glass fiber material includes a hydrophobic material.
  • the glass fiber material is about 50% by volume of the composite.
  • the degradation controlling agent is dispersed in the matrix material.
  • the degradation controlling agent is coated on a surface of the fiber material.
  • the degradation controlling agent is between about 0.1% to about 40% by weight of the matrix material.
  • the degradation controlling agent includes a buffer material selected from a group including calcium carbonate, calcium hydrogen carbonates, calcium phosphates, tricalcium phosphates, dicalcium phosphates, magnesium carbonate, and sodium carbonate.
  • the degradation controlling agent includes a common salt, hi an embodiment, the degradation controlling agent is selected from a group including a buffer material, a common salt, and combinations thereof.
  • the composite has an initial tensile strength of at least 250 MPa and retains the initial tensile strength for at least 8 weeks.
  • the composite includes an initial flexural strength of between about 250 MPa and about 400 MPa.
  • the composite includes an initial flexural modulus of between about 20-30 GPa.
  • the composite retains about 98% of an initial mass for at least 2 weeks.
  • the present disclosure includes a fiber reinforced composite material having a matrix material, a fiber material, and a degradation controlling agent.
  • the present disclosure includes a fiber reinforced composite material having a matrix material and a glass fiber material, wherein the glass fiber material includes a tensile strength of between about 300 MPa and about 1200 MPa.
  • the present disclosure includes a fiber reinforced composite material having a PLLA fiber material and a matrix material, wherein the fiber material includes a molecular weight of between about 290,000 g/mol and about 516,000 g/mol.
  • the present disclosure relates to a fiber-reinforced composite material having a PLLA fiber material and a matrix material that does not have the same chemical element composition as the fiber material.
  • a continuous PLLA fiber is extruded and drawn to provide the fiber with a tensile strength of between about 500 MPa to about 2000 MPa and a molecular weight of between about 290,000 g/mol to about 516,000 g/mol.
  • the extrusion and drawing process used to make the fiber may be any extrusion and drawing process known to one of ordinary skill in the art.
  • the PLLA fiber material is about 50% by volume of the composite and is bioabsorbable.
  • the matrix material which is bioabsorbable and selected from a group that includes a polymer, a copolymer, and a polymer blend, is then made.
  • a matrix material that does not have the same chemical element composition as the fiber material is defined as the following: If the matrix material is a polymer, then the polymer may not be a pure polylactide material. If the matrix material is a copolymer, then at least one of the monomeric species is not a lactone monomer. If the matrix material is a polymer blend, then at least one of the polymers has a chemical element composition that is different to that of the fiber.
  • the polymer that has a chemical element composition different to that of the fiber comprises at least 50% or more of the polymer blend.
  • a matrix material that has the same chemical element composition as the fiber material which is also within the scope of this disclosure, is defined as the following: If the matrix material is a polymer, then the polymer is a pure polylactide material. If the matrix material is a copolymer, then both monomeric species are lactone monomers. If the matrix material is a polymer blend, then both polymers are pure polylactide materials.
  • the composite may further include a degradation controlling agent.
  • the degradation controlling agent may include a buffer material, a common salt, and combinations thereof.
  • the buffer material is selected from a group including, but not limited to, calcium carbonate, calcium hydrogen carbonates, calcium phosphates, tricalcium phosphates, dicalcium phosphates, magnesium carbonate, and sodium carbonate.
  • the common salt is water soluble and may be organic or inorganic.
  • the salt may be based on, without limitation, one of the following: a Group I metal, including but not limited to, lithium, sodium, and potassium; a Group II metal, including but not limited to, beryllium, magnesium, calcium, strontium, and barium; transition metals, including but not limited to, copper, zinc, silver, gold, iron, and titanium; a Group III metal, including but not limited to, aluminum and boron.
  • the salt may include, without limitation, a carbonate, a hydrogen carbonate, a phosphate, a hydrogen phosphate, silicates, polyphosphates, and polysilicates.
  • the salt may be a single element, a compound, or a mixture thereof.
  • the degradation controlling agent is dispersed in the matrix material and is used as a buffer agent and to slow the degradation of the composite.
  • the degradation controlling agent is between about 0.1% to about 40% by weight of the matrix material.
  • the composite may further include an accelerant, such as the tertiary butyl ester of lauric acid or the ditertiary butyl ester of fumaric acid, dispersed in the matrix material or fiber material. Other accelerants known to those of ordinary skill in the art may be used. Use of these accelerants accelerates the degradation rate of the fiber or matrix.
  • the composite material has an initial tensile strength of at least 250 MPa and retains at least 75% of this initial tensile strength for at least 8 weeks. For the purposes of this disclosure, an initial tensile strength is taken to mean the tensile strength of the composite material prior to degradation.
  • the composite has a fiexural strength of about 200 MPa and a shear strength of at least 140 MPa.
  • the present disclosure relates to a fiber-reinforced composite material including a matrix material, a glass fiber material, and a degradation controlling agent.
  • the matrix material may be any biodegradable polymer, polymer blend, copolymer, or other biodegradable material known to those skilled in the art.
  • biodegradable polymers include alpha-polyhydroxy acids, polyglycolide (PGA), poly(L-lactide), poly(D,L-lactide), poly(.epsilon.-caprolactone), poly(trimethylene carbonate), poly(ethylene oxide) (PEO), poly(.beta.hydroxybutyrate) (PHB), poly(.beta.-hydroxyvalerate) (PHVA), poly(p- dioxanone) (PDS), poly(ortho esters), tyrosine-derived polycarbonates, polypeptides, polyurethane, and combinations thereof.
  • the glass fiber material is bioabsorbable and represents about 50% by volume of the composite.
  • the glass fiber material may be extruded and drawn by any extrusion and drawing process known to one of ordinary skill in the art.
  • the fiber includes a tensile strength of between about 300 MPa and about 1200 MPa.
  • the fiber material may include a hydrophobic material to slow down the degradation of the glass fiber material.
  • the hydrophobic material may be a component of the composition of the glass fiber material or coated on a surface of the glass fiber material. Examples of hydrophobic materials include, without limitation, polycaprolactone, poly-para-xylylene (e.g. Parylene), isomers and co-polymers of polylactide, polypeptide, ceramic materials (i.e.
  • the glass fibers include about 50 mol % potassium oxide (P2O 5 ), about 30 mol % calcium oxide (CaO), about 15 mol % sodium oxide (Na 2 O), and 5 mol % iron oxide (Fe 2 O 3) .
  • P2O 5 potassium oxide
  • CaO calcium oxide
  • Na 2 O sodium oxide
  • Fe 2 O 3 iron oxide
  • glass fibers of different compositions may be used.
  • the degradation controlling agent may be of the same type as the degradation controlling agents described above and may be dispersed in the matrix material or coated on a surface of the fiber material.
  • the agent acts as a means to control the degradation of the composite and/or the glass fiber. Specifically, with regards to the glass fibers, it is believed that the common salt substantially reduces the release of ions from the fibers.
  • the degradation controlling agent is dispersed in the matrix material, the agent represents between about 0.1% to about 40% by weight of the matrix material.
  • the composite has an initial tensile strength of at least 250 MPa and is able to retain this initial tensile strength for at least 8 weeks.
  • the composite includes an initial flexural strength of between about 250 MPa and about 400 MPa.
  • the composite retains about 98% of an initial mass for at least 2 weeks when it is placed in in-vivo conditions.
  • the reinforcing fibers of both composites preferably have mechanical properties that are not substantially compromised when tested in a physiological (aqueous, 37° C.) environment.
  • the fibers are preferably insoluble in the solvent used to dissolve the matrix polymer.
  • the degradation controlling agent of both composites must be one that reacts with the acid by-products that are generated during the degradation of the polymer fiber or matrix or the glass fiber, including, without limitation, lactic acid, glycolic acid, caproic acid, and different forms of phosphoric acid.
  • the particles may have a number of sizes, ranging from about 1 mm to about 10 ran, and geometries, such as needle, cubic, platelet, fibers, spheres, and other geometries known to one of ordinary skill in the art. It is important, but not required, that the particles have a shape that enhances the mechanical properties of the particles.
  • Biological agents such as cells, growth factors, antibiotics, anti-microbials, or other such factors may be added to one or more components of the composites to promote healing of the fracture.
  • PLLA fiber was first made by taking PLLA granules with a nominal intrinsic viscosity of 3.8 and extruding the granules into a fiber.
  • a single screw extruder fitted with a gear pump and a 2 mm spinneret die was used. The extruder also had a provision for air cooling.
  • the extruded fiber was batched on spools for the next processing step. Subsequently, the fiber was progressively stretched at elevated temperatures to produce a final diameter of ca. 100 microns and a draw ratio between about 8 and about 15.
  • the final molecular weight of the drawn fiber was between about 290,000 g/mol "1 to about 516,000 gmol "1 .
  • the resultant fiber had an average tensile strength of greater than about 800 MPa.
  • Composites were then made using an 85:15 co-polymer of PDLLA and PGA with a 35 % weight addition of calcium carbonate (CaCO 3 ) as the matrix material.
  • the drawn poly (L-lactide) fibers were then wound around a support frame of parallel bars that were held a constant distance apart. For each sample the fiber was wrapped 75 times around the support frame, resulting in 150 fibers in each composite.
  • the matrix was dissolved in a solvent, methyl acetate, at 10% wt/vol of solvent.
  • the solvent/polymer mixture was then coated onto the fibers.
  • the composite was then placed in a vacuum oven at 40 0 C for 12 hours to remove the solvent.
  • the composite was then placed in a cylindrical mold and heated to 165°C. This temperature is used to melt the matrix material to allow it to flow and consolidate the composite. Once thermal equilibrium was reached, slight tension was applied to the fibers to align them in the mold. The mold was then closed completely to consolidate the fibers and the matrix. The closed mold was then maintained at 165°C for up to 5 minutes and then removed from the heated press and placed between cool metal blocks to cool the composite down to room temperature to allow tension to be released from the fibers.
  • Composites were made that included poly-L-lactic acid (PLLA) fibers and a copolymer matrix of poly-L-lactic acid (PLLA) and polyglycolic acid (PGA) (PLGA 85: 15) using the method described in example 1.
  • the composite did not include calcium carbonate or other degradation controlling agents.
  • the flexural and shear properties of the resultant pins were tested, via a 3-point bending test, after aging in PBS at 37°C. The results are given in Table 3. TABLE 3
  • the coated fiber strips were cut into 120 mm lengths and compression molded at 16O 0 C to produce composite bars with nominal measurements of 10 x 3 x 120 mm. The bars were accurately measured and weighed to calculate their compositions.
  • the flexural mechanical properties of the composites were tested using a 3 point bend test method. The length/distance ratio of the composites was 32 and the test speed was 4.74 mrn/min. The moduli were determined from 3 measurements and the strength/strain to failure from 1 specimen.
  • the compositions and mechanical properties results are shown in Table 6.
  • the table shows that the glass fiber composites have substantially similar flexural strengths to the polymer fiber composites in Table 2.
  • the modulus is a quantity that expresses the degree to which a substance possesses a property, such as elasticity.
  • the composites were compression moulded in an aluminium mould with a cavity measuring 120 x 3 x 10 mm.
  • the mould was lined with a strip of PTFE impregnated glass cloth to allow the product to be removed more easily.
  • the moulding was done at 160 0 C under 100 kN pressure.
  • the mould was pre-heated and then strips were loaded into the cavity by hand one or two at a time. Once the mould was full, the pressure was applied for a few seconds, the mould was then re-opened, and further strips added. This was repeated until no further strips could be forced into the mould.
  • the mould was then cooled to room temperature under pressure.
  • the composite bars were trimmed and then capped with a layer of filled matrix to seal the ends.
  • the weights and compositions of the fibers are shown in Table 7. TABLE 7
  • the polymer fiber composite material of the present disclosure includes a polylactic acid fiber of high strength and a matrix material that is suitable for working with this fiber.
  • the matrix allows for a good interfacial strength between the fiber and the matrix, which provides the composite with a high mechanical strength and a decreased degradation rate.
  • polymer and glass fiber composite materials having a concentration of buffering material that has been shown to not adversely interfere with the interface between the polymer matrices and the fiber materials. Rather, the testing results show that the buffering material works to provide the composite with the ability to retain a majority of its initial strength over a longer period of time by slowing the rate of degradation of the polymer matrix and, in the glass fiber composite, the degradation rate of the glass fiber.
  • a composite material containing a matrix material and a mixture of the above- described glass and polymer fibers, with or without a degradation controlling agent, is also within the scope of this disclosure.
  • the matrix and the glass and polymer fibers may be of the same type and made by the same processes as the above-described matrices and polymer/glass fibers.
  • the degradation contolling agents may be of the same type as described above.
  • the processing conditions for making the composite may be the same as the processing conditions for making the above-described polymer fiber composites.

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Abstract

The present disclosure relates to a fiber reinforced composite material. In an embodiment, the composite material includes a PLLA fiber material and a matrix material that does not have the same chemical element composition as the fiber material. Other fiber reinforced composite materials are also disclosed.

Description

Fiber Reinforced Composite Material
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a PCT International Application of United States Patent Application No. 60/867,978, filed November 30, 2006, the disclosure of which is incorporated herein by reference in its entirety.
BACKGROUND OF THE INVENTION FIELD OF THE INVENTION
[0002] The present disclosure relates to bioresorbable composites and more specifically to a fiber reinforced polymer composite material that is used to make bioresorbable products, RELATED ART
[0003] Metal products have been used in fracture fixation due to their high strength. While these products perform well, there are a significant number of occurrences where these products can cause problems to the patient. In some cases the presence of the metal implant can cause irritation of the soft tissue around the implant, in severe cases this necessitates the removal of the implant. The procedure to remove the metal products exposes the patient to the risks associated with undergoing a major medical procedure and also adds to the overall cost of healing the original fracture. One potential solution to substantially reduce the need to remove fracture fixation hardware is to use bioresorbable devices to fix the fracture. However, the currently available bioresorbable materials and products do not have the required combination of initial strength and retention of this strength for suitable fracture healing to occur.
[0004] The currently marketed bioresorbable products include those products manufactured from injection molded polymers, polymer blends, and co-polymers. These products have been utilized in the areas of craniomaxilofacial implants and non-load bearing fracture fixation implants, such as pins and screws, for wrist and ankle applications and for reattaching soft tissues, such as ligaments and tendons, to bone. In addition, there are also some spinal products available that make use of the compressive properties of these polymers. Products including these materials are easy to process, but are limited by the mechanical properties of the materials. These materials have a tensile strength in the range of between about 50 MPa to about 100 MPa. Depending on the choice of polymer or co-polymer, products in this category retain the majority of their strength for less than about 12 weeks. Therefore, these materials are not suitable for fracture fixation applications beyond simple non-loaded pins and screws.
[0005] Other currently marketed bioresorbable products include self reinforced products that have improved strength due to orientation of the polymer during processing of the product. Even though these products have improved strength, their flexural strength is still only around 250 MPa. This limits the uses of this technology for fracture fixation to screws and pins.
[0006] Recently, devices have been manufactured from fiber reinforced polymer composites utilizing polyglycolic acid (PGA) fibers. These composites have a good initial strength, but suffer a rapid loss in strength due to the rapid hydrolysis of these fibers. Devices have been manufactured using PLLA fibers and PDLLA as the matrix material. Unfortunately, this matrix breaks down rapidly and results in the composites having a rapid loss in strength. Other attempts have used co-polymers containing PLLA as the reinforcing fiber, such as PLLA- co-PGA copolymers at a ratio of 82:18. However, there has been difficulty in finding a suitable polymer matrix material that can be processed into a composite without degrading or breaking this reinforcing fiber. Most recently, composites have been made where the matrix was a polymer with the same chemical composition as the fiber or where the matrix was a blend with the majority of the blend being a polymer with the same chemical composition as the matrix. These composites have an initial flexural strength of between 120 to 140 MPa, with most of this strength lost within about 12 weeks of use.
[0007] Attempts to slow down the degradation of the polymer matrix have included modifying the composition to increase the hydrophobicity of the polymer. However, this increases either the crystallinity of the polymer matrix, which is undesirable from a biological perspective, or it makes the polymer too ductile if a hydrophobic rubbery component, such as polycaprolactone (PCL), is added. Buffering materials, such as calcium carbonate, have also been added to polymers to slow degradation rates and improve the biological properties, such as osteoconductivity. However, in order to gain the beneficial effects of calcium carbonate it needs to be present at high levels, about 30% by weight of the composition. Since a fiber polymer composite contains at least 50% of fiber by volume, it would be anticipated that a calcium carbonate-containing matrix would interfere adversely with the interface between the polymer matrix and reinforcing fibers. This could result in the fiber-reinforced composite substantially weakening or even falling apart before complete healing of a fracture.
[0008] In order to make a suitable fiber-reinforced composite material, the fiber and matrix material have certain requirements. The fiber needs to have both a high initial tensile strength, and the ability to retain the majority of this strength, for the fracture to heal. To have a high initial strength, the fibers need to be highly orientated and be present at about 40% by volume of the composite. In addition, the fibers should also have some crystallinity, as this imparts stability against relaxation of the orientation in the fiber.
[0009] The matrix material also needs to be able to retain the majority of its strength for a suitable time, approximately between about 6 to about 12 weeks, for the fracture to heal. In order to accomplish this, the matrix should have a sufficiently high initial molecular weight. As the polymers degrade, the molecular weight decreases and the polymers become brittle and lose their mechanical properties. Additives, such as calcium carbonate or other buffering materials, can be added to the matrix to control the degradation rate. The amount of the buffering material should be around 30% by weight of the matrix without adversely interfering with the interface between the polymer matrix and the reinforcing fibers.
[0010] In addition, the matrix material needs to be processable at a temperature which is low enough to not significantly affect the strength of the fiber and adhere well enough to the fiber to allow stress transfer from the matrix to the fiber. To accomplish this, both semi- crystalline and amorphous co-polymers can be used. Semi-crystalline co-polymers are typically composed of lactic acid and one or more additional monomer units whose function is to lower the melting point of the co-polymer matrix to a point where the strength of the fiber is not affected during the consolidation step. Amorphous or non- crystalline materials, such as poly (D- lactide) acid polymers, are suitable for processing with the fiber, as they soften at relatively low temperatures. However, these materials do not have a long strength retention time. This strength retention can be improved by incorporating a buffering material, such as calcium carbonate, into the matrix material. In this case, the calcium carbonate acts as both a buffer and also reduces the thermal sensitivity of the polymer to breakdown during processing. Taken together, the affect of the calcium carbonate is to both slow the rate of degradation of the polymer and help preserve the molecular weight during processing, without adversely interfering with the interface between the polymer matrix and the reinforcing fibers. [0011] The present disclosure incorporates these requirements to produce a bioresorbable material which has a high initial strength and retains a significant proportion of this strength for a useful time.
SUMMARY OF THE INVENTION
[0012] In one aspect, the present disclosure relates to a fiber reinforced composite material including a PLLA fiber material, such as a continuous PLLA fiber material, and a matrix material that does not have the same chemical element composition as the fiber material. In an embodiment, the composite further includes a degradation controlling agent dispersed in the matrix material. In another embodiment, the degradation controlling agent includes a buffer material selected from a group including calcium carbonate, calcium hydrogen carbonates, calcium phosphates, tricalcium phosphates, dicalcium phosphates, magnesium carbonate, and sodium carbonate. In yet another embodiment, the degradation controlling agent includes a common salt. In an embodiment, the degradation controlling agent is selected from a group including a buffer material, a common salt, and combinations thereof. In a further embodiment, the degradation controlling agent is between about 0.1% to about 40% by weight of the matrix material. In yet a further embodiment, the composite further includes an accelerant dispersed in the fiber or matrix material. In a further embodiment, the PLLA fiber material is about 50% by volume of the composite. In an embodiment, the fiber material, which is bioabsorbable, has a tensile strength of between about 500 MPa to about 2000 MPa and a molecular weight of between about 290,000 g/mol and about 516,000 g/mol.
[0013] In an embodiment, the matrix material is bioresorbable and is selected from a group including a polymer, a copolymer, and a polymer blend. In another embodiment, when a polymer blend is used as the matrix, the blend includes at least two polymers and at least one of the polymers has a chemical element composition that is different to that of the fiber. In yet another embodiment, the polymer having a chemical element composition that is different to that of the fiber comprises at least 50% of the polymer blend. In a further embodiment, the polymer having a chemical element composition that is different to that of the fiber comprises more than 50% of the polymer blend. In yet a further embodiment, the matrix material is bioabsorbable.
[0014] In yet a further embodiment, the composite has an initial tensile strength of at least 250 MPa and retains at least 75% of the initial tensile strength for at least 8 weeks. In an embodiment, the composite material includes a flexural strength of about 200 MPa and a shear strength of at least 140 MPa.
[0015] In another aspect, the present disclosure includes a fiber reinforced composite material having a matrix material, a glass fiber material, and a degradation controlling agent. In an embodiment, the matrix material is selected from a group including a polymer, a copolymer, and a polymer blend. In an embodiment, the matrix material is bioabsorbable. In another embodiment, the glass fiber material is bioabsorbable. In yet another embodiment, the glass fiber material includes a tensile strength between about 300 MPa and about 1200 MPa. In a further embodiment, the glass fiber material includes a hydrophobic material. In yet a further embodiment, the glass fiber material is about 50% by volume of the composite.
[0016] In an embodiment, the degradation controlling agent is dispersed in the matrix material. In another embodiment, the degradation controlling agent is coated on a surface of the fiber material. In yet another embodiment, the degradation controlling agent is between about 0.1% to about 40% by weight of the matrix material. In a further embodiment, the degradation controlling agent includes a buffer material selected from a group including calcium carbonate, calcium hydrogen carbonates, calcium phosphates, tricalcium phosphates, dicalcium phosphates, magnesium carbonate, and sodium carbonate. In yet a further embodiment, the degradation controlling agent includes a common salt, hi an embodiment, the degradation controlling agent is selected from a group including a buffer material, a common salt, and combinations thereof.
[0017] In yet a further embodiment, the composite has an initial tensile strength of at least 250 MPa and retains the initial tensile strength for at least 8 weeks. In an embodiment, the composite includes an initial flexural strength of between about 250 MPa and about 400 MPa. In another embodiment, the composite includes an initial flexural modulus of between about 20-30 GPa. In yet another embodiment, the composite retains about 98% of an initial mass for at least 2 weeks.
[0018] In yet another aspect, the present disclosure includes a fiber reinforced composite material having a matrix material, a fiber material, and a degradation controlling agent.
[0019] In a further aspect, the present disclosure includes a fiber reinforced composite material having a matrix material and a glass fiber material, wherein the glass fiber material includes a tensile strength of between about 300 MPa and about 1200 MPa.
[0020] In yet a further aspect, the present disclosure includes a fiber reinforced composite material having a PLLA fiber material and a matrix material, wherein the fiber material includes a molecular weight of between about 290,000 g/mol and about 516,000 g/mol.
[0021] Further areas of applicability of the present disclosure will become apparent from the detailed description provided hereinafter. It should be understood that the detailed description and specific examples, while indicating the preferred embodiments of the disclosure, are intended for purposes of illustration only and are not intended to limit the scope of the disclosure. DETAILED DESCRIPTION OF THE EMBODIMENTS
[0022] The following description of the preferred embodiment(s) is merely exemplary in nature and is in no way intended to limit the disclosure, its application, or uses.
[0023] hi one aspect, the present disclosure relates to a fiber-reinforced composite material having a PLLA fiber material and a matrix material that does not have the same chemical element composition as the fiber material.
[0024] A continuous PLLA fiber is extruded and drawn to provide the fiber with a tensile strength of between about 500 MPa to about 2000 MPa and a molecular weight of between about 290,000 g/mol to about 516,000 g/mol. The extrusion and drawing process used to make the fiber may be any extrusion and drawing process known to one of ordinary skill in the art. The PLLA fiber material is about 50% by volume of the composite and is bioabsorbable.
[0025] The matrix material, which is bioabsorbable and selected from a group that includes a polymer, a copolymer, and a polymer blend, is then made. For the purposes of this disclosure, a matrix material that does not have the same chemical element composition as the fiber material is defined as the following: If the matrix material is a polymer, then the polymer may not be a pure polylactide material. If the matrix material is a copolymer, then at least one of the monomeric species is not a lactone monomer. If the matrix material is a polymer blend, then at least one of the polymers has a chemical element composition that is different to that of the fiber. The polymer that has a chemical element composition different to that of the fiber comprises at least 50% or more of the polymer blend. Alternatively, a matrix material that has the same chemical element composition as the fiber material, which is also within the scope of this disclosure, is defined as the following: If the matrix material is a polymer, then the polymer is a pure polylactide material. If the matrix material is a copolymer, then both monomeric species are lactone monomers. If the matrix material is a polymer blend, then both polymers are pure polylactide materials.
[0026] The composite may further include a degradation controlling agent. For the purposes of this disclosure, the degradation controlling agent may include a buffer material, a common salt, and combinations thereof. The buffer material is selected from a group including, but not limited to, calcium carbonate, calcium hydrogen carbonates, calcium phosphates, tricalcium phosphates, dicalcium phosphates, magnesium carbonate, and sodium carbonate. The common salt is water soluble and may be organic or inorganic. In addition, the salt may be based on, without limitation, one of the following: a Group I metal, including but not limited to, lithium, sodium, and potassium; a Group II metal, including but not limited to, beryllium, magnesium, calcium, strontium, and barium; transition metals, including but not limited to, copper, zinc, silver, gold, iron, and titanium; a Group III metal, including but not limited to, aluminum and boron. Furthermore, the salt may include, without limitation, a carbonate, a hydrogen carbonate, a phosphate, a hydrogen phosphate, silicates, polyphosphates, and polysilicates. Finally, the salt may be a single element, a compound, or a mixture thereof.
[0027] The degradation controlling agent is dispersed in the matrix material and is used as a buffer agent and to slow the degradation of the composite. The degradation controlling agent is between about 0.1% to about 40% by weight of the matrix material. The composite may further include an accelerant, such as the tertiary butyl ester of lauric acid or the ditertiary butyl ester of fumaric acid, dispersed in the matrix material or fiber material. Other accelerants known to those of ordinary skill in the art may be used. Use of these accelerants accelerates the degradation rate of the fiber or matrix. [0028] The composite material has an initial tensile strength of at least 250 MPa and retains at least 75% of this initial tensile strength for at least 8 weeks. For the purposes of this disclosure, an initial tensile strength is taken to mean the tensile strength of the composite material prior to degradation. In addition, the composite has a fiexural strength of about 200 MPa and a shear strength of at least 140 MPa.
[0029] In another aspect, the present disclosure relates to a fiber-reinforced composite material including a matrix material, a glass fiber material, and a degradation controlling agent.
[0030] The matrix material may be any biodegradable polymer, polymer blend, copolymer, or other biodegradable material known to those skilled in the art. Examples of biodegradable polymers include alpha-polyhydroxy acids, polyglycolide (PGA), poly(L-lactide), poly(D,L-lactide), poly(.epsilon.-caprolactone), poly(trimethylene carbonate), poly(ethylene oxide) (PEO), poly(.beta.hydroxybutyrate) (PHB), poly(.beta.-hydroxyvalerate) (PHVA), poly(p- dioxanone) (PDS), poly(ortho esters), tyrosine-derived polycarbonates, polypeptides, polyurethane, and combinations thereof.
[0031] The glass fiber material is bioabsorbable and represents about 50% by volume of the composite. The glass fiber material may be extruded and drawn by any extrusion and drawing process known to one of ordinary skill in the art. The fiber includes a tensile strength of between about 300 MPa and about 1200 MPa. In addition, the fiber material may include a hydrophobic material to slow down the degradation of the glass fiber material. The hydrophobic material may be a component of the composition of the glass fiber material or coated on a surface of the glass fiber material. Examples of hydrophobic materials include, without limitation, polycaprolactone, poly-para-xylylene (e.g. Parylene), isomers and co-polymers of polylactide, polypeptide, ceramic materials (i.e. hydroxyapatite and any form of calcium phosphate), and any other organic or inorganic hydrophobic material likely to slow down the penetration of water to the fiber. For the purposes of this disclosure, the glass fibers include about 50 mol % potassium oxide (P2O5), about 30 mol % calcium oxide (CaO), about 15 mol % sodium oxide (Na2O), and 5 mol % iron oxide (Fe2O3). However, glass fibers of different compositions may be used.
[0032] The degradation controlling agent may be of the same type as the degradation controlling agents described above and may be dispersed in the matrix material or coated on a surface of the fiber material. The agent acts as a means to control the degradation of the composite and/or the glass fiber. Specifically, with regards to the glass fibers, it is believed that the common salt substantially reduces the release of ions from the fibers. Where the degradation controlling agent is dispersed in the matrix material, the agent represents between about 0.1% to about 40% by weight of the matrix material.
[0033] The composite has an initial tensile strength of at least 250 MPa and is able to retain this initial tensile strength for at least 8 weeks. In addition, the composite includes an initial flexural strength of between about 250 MPa and about 400 MPa. Furthermore, the composite retains about 98% of an initial mass for at least 2 weeks when it is placed in in-vivo conditions.
[0034] The reinforcing fibers of both composites, as described above, preferably have mechanical properties that are not substantially compromised when tested in a physiological (aqueous, 37° C.) environment. The fibers are preferably insoluble in the solvent used to dissolve the matrix polymer. In addition, the degradation controlling agent of both composites must be one that reacts with the acid by-products that are generated during the degradation of the polymer fiber or matrix or the glass fiber, including, without limitation, lactic acid, glycolic acid, caproic acid, and different forms of phosphoric acid. Where the degradation controlling agent is in a particulate form, the particles may have a number of sizes, ranging from about 1 mm to about 10 ran, and geometries, such as needle, cubic, platelet, fibers, spheres, and other geometries known to one of ordinary skill in the art. It is important, but not required, that the particles have a shape that enhances the mechanical properties of the particles.
[0035] Biological agents, such as cells, growth factors, antibiotics, anti-microbials, or other such factors may be added to one or more components of the composites to promote healing of the fracture.
[0036] Further details may be derived from the examples below.
EXAMPLE 1
[0037] PLLA fiber was first made by taking PLLA granules with a nominal intrinsic viscosity of 3.8 and extruding the granules into a fiber. A single screw extruder fitted with a gear pump and a 2 mm spinneret die was used. The extruder also had a provision for air cooling. The extruded fiber was batched on spools for the next processing step. Subsequently, the fiber was progressively stretched at elevated temperatures to produce a final diameter of ca. 100 microns and a draw ratio between about 8 and about 15. The final molecular weight of the drawn fiber was between about 290,000 g/mol"1 to about 516,000 gmol"1. The resultant fiber had an average tensile strength of greater than about 800 MPa.
[0038] Composites were then made using an 85:15 co-polymer of PDLLA and PGA with a 35 % weight addition of calcium carbonate (CaCO3) as the matrix material. The drawn poly (L-lactide) fibers were then wound around a support frame of parallel bars that were held a constant distance apart. For each sample the fiber was wrapped 75 times around the support frame, resulting in 150 fibers in each composite. The matrix was dissolved in a solvent, methyl acetate, at 10% wt/vol of solvent. The solvent/polymer mixture was then coated onto the fibers. The composite was then placed in a vacuum oven at 400C for 12 hours to remove the solvent.
[0039] The composite was then placed in a cylindrical mold and heated to 165°C. This temperature is used to melt the matrix material to allow it to flow and consolidate the composite. Once thermal equilibrium was reached, slight tension was applied to the fibers to align them in the mold. The mold was then closed completely to consolidate the fibers and the matrix. The closed mold was then maintained at 165°C for up to 5 minutes and then removed from the heated press and placed between cool metal blocks to cool the composite down to room temperature to allow tension to be released from the fibers.
[0040] Samples of the composite were aged in phosphate buffer solution (PBS) at 37°C. The average diameter of the samples was about 1.7 mm. The composites were removed from the aging solution, dried, and tested using a 3-point bend test method. As shown in Table 1, the samples were tested for their initial tensile strength and their tensile strengths after 6, 10, 12, and 16 weeks. Compared to the initial tensile strength, the tensile strength of the composite during the succeeding weeks remained high. TABLE 1
Figure imgf000014_0001
EXAMPLE 2
[0041] Composites were made using the method described in Example 1, with and without CaCO3 mixed in the matrix, and with a range of different matrix materials. The resultant composites were tested for their flexural strength in 3 point bending. The pins were 2 mm in diameter and tested using a 16:1 span to diameter ratio. The results are given in Table 2, It is clear that the mechanical properties of the composites containing a degradation controlling agent are not significantly compromised by the presence of the material. TABLE 2
Figure imgf000015_0001
EXAMPLE 3
[0042] Composites were made that included poly-L-lactic acid (PLLA) fibers and a copolymer matrix of poly-L-lactic acid (PLLA) and polyglycolic acid (PGA) (PLGA 85: 15) using the method described in example 1. The composite did not include calcium carbonate or other degradation controlling agents. The flexural and shear properties of the resultant pins were tested, via a 3-point bending test, after aging in PBS at 37°C. The results are given in Table 3. TABLE 3
Figure imgf000015_0002
Figure imgf000016_0001
EXAMPLE 4
[0043] 40 g of poly(D,L-lactide-co-glycolide) were dissolved in 360 ml of CHCl3 to produce a clear solution and 61.54 g of calcium carbonate (CaCO3) filled poly(D,L-lactide-co- glycolide) were dissolved in 360 ml of CHCl3 to produce a suspension of CaCO3 particles in polymer solution. Im long skeins of glass fiber, having the properties shown in Table 4 and weighing between 4.56 g and 7.32 g, were then dipped in the solutions and suspended in a fume cupboard to allow the solvent to evaporate. The resulting coated fiber strips were vacuum dried at 800C below 1 mbar to constant mass. The weights and compositions of the dried skeins are shown in Table 5. TABLE 4
Figure imgf000016_0002
TABLE 5
Figure imgf000017_0001
The coated fiber strips were cut into 120 mm lengths and compression molded at 16O0C to produce composite bars with nominal measurements of 10 x 3 x 120 mm. The bars were accurately measured and weighed to calculate their compositions. The flexural mechanical properties of the composites were tested using a 3 point bend test method. The length/distance ratio of the composites was 32 and the test speed was 4.74 mrn/min. The moduli were determined from 3 measurements and the strength/strain to failure from 1 specimen. The compositions and mechanical properties results are shown in Table 6. The table shows that the glass fiber composites have substantially similar flexural strengths to the polymer fiber composites in Table 2. For the purposes of this disclosure, the modulus is a quantity that expresses the degree to which a substance possesses a property, such as elasticity. TABLE 6
Figure imgf000017_0002
EXAMPLE 5
[0044] Solutions of 10% w/w of poly (D-L-lactide-co-glycolide) 85:15 and 35% w/w (of the polymer weight) CaCCβ in CH2Cl2 were prepared. Approx. 50 cm lengths of glass fiber (50 mol % P2O5, 30-40 mol % CaO, 5-15 mol % Na2O, 5 mol % Fe2O3) weighing between 1.5 and 7 g were weighed, dipped in the polymer solution, and hung up to dry in a fume cupboard over night. The fibers were then vacuum dried at 800C and re-weighed. The composite strips were cut into 12 mm lengths and randomized.
[0045] The composites were compression moulded in an aluminium mould with a cavity measuring 120 x 3 x 10 mm. The mould was lined with a strip of PTFE impregnated glass cloth to allow the product to be removed more easily. The moulding was done at 1600C under 100 kN pressure. The mould was pre-heated and then strips were loaded into the cavity by hand one or two at a time. Once the mould was full, the pressure was applied for a few seconds, the mould was then re-opened, and further strips added. This was repeated until no further strips could be forced into the mould. The mould was then cooled to room temperature under pressure. The composite bars were trimmed and then capped with a layer of filled matrix to seal the ends. The weights and compositions of the fibers are shown in Table 7. TABLE 7
Figure imgf000018_0001
All samples were tested to assess flexural stiffiiess and tested to failure. Tests were performed in a 3 point bending test set-up, with a testing span of 90 mm and thickness and width measured for each sample. For modulus measurements, deflection was performed at a crosshead displacement of 4.74 mm/min using a IOON load cell. Strength was measured using a 10 kN load cell. The compositions and mechanical properties results are shown in Table 8. TABLE 8
Figure imgf000019_0001
EXAMPLE 6
[0046] Glass fiber composites, as prepared in Example 5, with and without CaCO3 filler mixed in the matrix, were immersed individually in bottles containing 300 ml of phosphate buffer saline (PBS) and placed in an incubator at 37°C. The samples were removed for analysis after 14 days, and their dry mass was recorded. The samples containing CaCCβ had retained 98% of their initial dry mass, while those without CaCCβ had only retained 63% of their initial dry mass
[0047] The polymer fiber composite material of the present disclosure includes a polylactic acid fiber of high strength and a matrix material that is suitable for working with this fiber. The matrix allows for a good interfacial strength between the fiber and the matrix, which provides the composite with a high mechanical strength and a decreased degradation rate. Also disclosed are polymer and glass fiber composite materials having a concentration of buffering material that has been shown to not adversely interfere with the interface between the polymer matrices and the fiber materials. Rather, the testing results show that the buffering material works to provide the composite with the ability to retain a majority of its initial strength over a longer period of time by slowing the rate of degradation of the polymer matrix and, in the glass fiber composite, the degradation rate of the glass fiber. [0048] A composite material containing a matrix material and a mixture of the above- described glass and polymer fibers, with or without a degradation controlling agent, is also within the scope of this disclosure. The matrix and the glass and polymer fibers may be of the same type and made by the same processes as the above-described matrices and polymer/glass fibers. In addition, the degradation contolling agents may be of the same type as described above. Furthermore, the processing conditions for making the composite may be the same as the processing conditions for making the above-described polymer fiber composites.
[0049] As various modifications could be made to the exemplary embodiments, as described above with reference to the corresponding illustrations, without departing from the scope of the disclosure, it is intended that all matter contained in the foregoing description and shown in the accompanying drawings shall be interpreted as illustrative rather than limiting. Thus, the breadth and scope of the present disclosure should not be limited by any of the above- described exemplary embodiments, but should be defined only in accordance with the following claims appended hereto and their equivalents.

Claims

CLAIMS What is claimed is:
1. A fiber reinforced composite material comprising: a PLLA fiber material; and a matrix material that does not have the same chemical element composition as the fiber material.
2. The composite material of claim 1 further comprising a degradation controlling agent dispersed in the matrix material.
3. The composite material of claim 1 further comprising an accelerant dispersed in the matrix material.
4. The composite material of claim 1 further comprising an accelerant dispersed in the PLLA fiber material.
5. The composite material of claim 2 wherein the degradation controlling agent is a buffer material selected from a group consisting essentially of calcium carbonate, calcium hydrogen carbonates, calcium phosphates, dicalcium phosphates, tricalcium phosphates, magnesium carbonate, and sodium carbonate.
6. The composite material of claim 2 wherein the degradation controlling agent is a common salt.
7. The composite material of claim 2 wherein the degradation controlling agent comprises between about 0.1 % to about 40% by weight of the matrix material.
8. The composite material of claim 1 wherein the PLLA fiber material comprises a continuous PLLA fiber material.
9. The composite material of claim 1 wherein the PLLA fiber material comprises about 50% by volume of the composite.
10. The composite material of claim 1 wherein the fiber material comprises a tensile strength of between about 500 MPa to about 2000 MPa.
11. The composite material of claim 1 wherein the fiber material comprises a tensile strength ofabout 800 MPa.
12. The composite material of claim 1 wherein the fiber material includes a molecular weight of between about 290,000 g/mol to about 516,000 g/mol.
13. The composite material of claim 1 wherein the fiber material is bioabsorbable.
14. The composite material of claim 1 wherein the matrix material is selected from a group consisting essentially of a polymer, a copolymer, and a polymer blend.
15. The composite material of claim 14 wherein the polymer blend includes at least two polymers, wherein at least one polymer of the blend has a chemical element composition that is different to that of the fiber.
16. The composite material of claim 15 wherein the polymer having a chemical element composition that is different to that of the fiber comprises at least 50% of the polymer blend.
17. The composite material claim 16 wherein the polymer having a chemical element composition that is different to that of the fiber comprises more than 50% of the polymer blend.
18. The composite material of claim 1 wherein the matrix material is bioabsorbable.
19. The composite material of claim 1 wherein the composite has an initial tensile strength of at least 250 MPa.
20. The composite material of claim 19 wherein the composite retains at least 75% of the initial tensile strength for at least 8 weeks.
21. The composite material of claim 1 wherein the composite has a flexural strength of about 200 MPa.
22. The composite material of claim 1 wherein the composite has a shear strength of at least 140 MPa.
23. A fiber reinforced composite material comprising: a matrix material; a glass fiber material; and a degradation controlling agent.
24. The composite material of claim 23 wherein the matrix material is selected from a group consisting essentially of a polymer, a copolymer, and a polymer blend.
25. The composite material of claim 23 wherein the matrix material is bioabsorbable.
26. The composite material of claim 23 wherein the fiber material comprises a bioabsorbable glass fiber material.
27. The composite material of claim 23 wherein the glass fiber material includes a tensile strength between about 300 MPa and about 1200 MPa.
28. The composite material of claim 23 wherein the glass fiber material includes a hydrophobic material.
29. The composite material of claim 23 wherein the fiber material comprises about 50 % by volume of the composite.
30. The composite material of claim 23 wherein the degradation controlling agent is dispersed in the matrix material.
31. The composite material of claim 23 wherein the degradation controlling agent is coated on a surface of the fiber material.
32. The composite material of claim 30 wherein the degradation controlling agent comprises between about 0.1 % to about 40 % by weight of the matrix material.
33. The composite material of claim 23 wherein the degradation controlling agent includes a buffer material selected from a group consisting essentially of calcium carbonate, calcium hydrogen carbonates, calcium phosphates, dicalcium phosphates, tricalcium phosphates, magnesium carbonate, and sodium carbonate.
34. The composite material of claim 33 wherein the degradation controlling agent includes a common salt.
35. The composite material of claim 23 wherein the composite has an initial tensile strength of at least 250 MPa.
36. The composite material of claim 35 wherein the composite retains the initial tensile strength for at least 8 weeks.
37. The composite material of claim 23 wherein the composite includes an initial flexural strength of between about 250 MPa and about 400 MPa.
38. The composite material of claim 23 wherein the composite includes an initial flexural modulus of between about 20-30 GPa.
39. The composite material of claim 23 wherein the composite retains about 98% of an initial mass for at least 2 weeks.
40. A fiber reinforced composite material comprising: a matrix material; a fiber material; and a degradation controlling agent.
41. A fiber reinforced composite material comprising: a matrix material; and a glass fiber material, the glass fiber material including a tensile strength of between about 300 MPa and about 1200 MPa.
42. The composite material of claim 2 wherein the degradation controlling agent is selected from a group consisting essentially of a buffer material, a common salt, and combinations thereof.
43. The composite material of claim 23 wherein the degradation controlling agent is selected from a group consisting essentially a buffer material, a common salt, and combinations thereof.
44. A fiber reinforced composite material comprising: a PLLA fiber material, the fiber material including a molecular weight of between about 290,000 g/mol to about 516,000 g/mol; and a matrix material.
PCT/US2007/086067 2006-11-30 2007-11-30 Fiber reinforced composite material WO2008067531A2 (en)

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DE602007011671T DE602007011671D1 (en) 2006-11-30 2007-11-30 FIBER REINFORCED COMPOSITE MATERIAL
CN2007800438419A CN101594831B (en) 2006-11-30 2007-11-30 Fiber reinforced composite material
EP07864978A EP2120745B1 (en) 2006-11-30 2007-11-30 Fiber reinforced composite material
AU2007325001A AU2007325001B2 (en) 2006-11-30 2007-11-30 Fiber reinforced composite material
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JP2009539508A JP2010511751A (en) 2006-11-30 2007-11-30 Fiber reinforced composite material
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Cited By (20)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2010122098A2 (en) 2009-04-23 2010-10-28 Vivoxid Oy Biocompatible composite and its use
CN102677304A (en) * 2012-05-29 2012-09-19 蔡紫林 Yarn-dyed fabric
CN104857577A (en) * 2015-05-28 2015-08-26 上海益生源药业有限公司 Absorbable bone fixation material and preparation method thereof
US9120919B2 (en) 2003-12-23 2015-09-01 Smith & Nephew, Inc. Tunable segmented polyacetal
US9770534B2 (en) 2007-04-19 2017-09-26 Smith & Nephew, Inc. Graft fixation
US9815240B2 (en) 2007-04-18 2017-11-14 Smith & Nephew, Inc. Expansion moulding of shape memory polymers
US10028776B2 (en) 2010-10-20 2018-07-24 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants
US10525169B2 (en) 2010-10-20 2020-01-07 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants, and novel composite structures which may be used for medical and non-medical applications
US10525168B2 (en) 2010-10-20 2020-01-07 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants, and novel composite structures which may be used for medical and non-medical applications
US10857261B2 (en) 2010-10-20 2020-12-08 206 Ortho, Inc. Implantable polymer for bone and vascular lesions
EP3470097B1 (en) 2017-10-16 2021-03-31 Arctic Biomaterials Oy Orthopedic bioabsorbable implants
US11058796B2 (en) 2010-10-20 2021-07-13 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants, and novel composite structures which may be used for medical and non-medical applications
US11207109B2 (en) 2010-10-20 2021-12-28 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants, and novel composite structures which may be used for medical and non-medical applications
US11291483B2 (en) 2010-10-20 2022-04-05 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants
US11351261B2 (en) 2010-10-20 2022-06-07 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants
US11352491B2 (en) 2016-09-08 2022-06-07 Schaefer Kalk Gmbh & Co. Kg Calcium-salt-containing composite powder having microstructured particles
US11441008B2 (en) 2016-09-08 2022-09-13 Schaefer Kalk Gmbh & Co. Kg Composite powder containing calcium carbonate and having microstructured particles
US11484627B2 (en) 2010-10-20 2022-11-01 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants, and novel composite structures which may be used for medical and non-medical applications
US11548998B2 (en) 2016-09-08 2023-01-10 Schaefer Kalk Gmbh & Co. Kg Inhibiting calcium carbonate additive
US11760874B2 (en) 2016-09-08 2023-09-19 Schaefer Kalk Gmbh & Co. Kg Composite powder containing calcium carbonate and having microstructured particles having inhibiting calcium carbonate

Families Citing this family (21)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9849216B2 (en) 2006-03-03 2017-12-26 Smith & Nephew, Inc. Systems and methods for delivering a medicament
US8852625B2 (en) 2006-04-26 2014-10-07 Micell Technologies, Inc. Coatings containing multiple drugs
AU2008242737B2 (en) 2007-04-19 2013-09-26 Smith & Nephew, Inc. Multi-modal shape memory polymers
CN102481195B (en) 2009-04-01 2015-03-25 米歇尔技术公司 Drug delivery medical device
JP5633291B2 (en) * 2010-10-05 2014-12-03 東洋製罐株式会社 Biodegradable resin composition
US9415440B2 (en) 2010-11-17 2016-08-16 Alcoa Inc. Methods of making a reinforced composite and reinforced composite products
GB201102468D0 (en) * 2011-02-11 2011-03-30 Univ Manchester Biocompatible composite materials
CN102247622A (en) * 2011-06-10 2011-11-23 东华大学 Degradable fiber-enhanced polycaprolactone degradable bone nail and preparation method thereof through solution method
CN103796618A (en) * 2011-07-15 2014-05-14 史密夫和内修有限公司 Fiber-reinforced composite orthopaedic device having embedded electronics
KR101269127B1 (en) * 2011-10-18 2013-05-29 포항공과대학교 산학협력단 Membrane type scaffold and fabrication method thereof
ES2706149T3 (en) * 2012-02-08 2019-03-27 Toray Industries Material sensitive to stimuli and medical material that comprises
WO2014165264A1 (en) 2013-03-12 2014-10-09 Micell Technologies, Inc. Bioabsorbable biomedical implants
KR102079613B1 (en) * 2013-05-15 2020-02-20 미셀 테크놀로지즈, 인코포레이티드 Bioabsorbable biomedical implants
CN103611198B (en) * 2013-12-03 2016-09-28 中国科学院长春应用化学研究所 A kind of absorbable medical perforated membrane and preparation method thereof
US10869954B2 (en) * 2016-03-07 2020-12-22 Ossio, Ltd. Surface treated biocomposite material, medical implants comprising same and methods of treatment thereof
CN105818492B (en) * 2016-03-29 2018-02-16 中材科技股份有限公司 A kind of bioactivity phosphate base continuous glass fibre composite material for weaving and application thereof
CN106039424B (en) * 2016-05-25 2019-04-05 南京凤源新材料科技有限公司 A kind of novel polylactic acid glass fiber composite material for skeletal fixation
DE102016116387A1 (en) * 2016-09-01 2018-03-01 Karl Leibinger Medizintechnik Gmbh & Co. Kg Fiber-reinforced bioresorbable implant and method for its production
CN110144064B (en) * 2019-05-28 2021-08-13 广东工业大学 Bio-based reinforcing material, bio-based composite material and preparation method thereof
CN112679760B (en) * 2020-11-19 2021-12-21 宁波宝亭生物科技有限公司 Preparation method of glass fiber reinforced biodegradable polymer composite material
CN116036386B (en) * 2023-02-22 2024-04-30 天津纳博特医疗器械有限公司 Absorbable glass fiber reinforced polylactic acid composite material and craniomaxillofacial nail plate system

Family Cites Families (343)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
NL216498A (en) 1955-11-30
US3531561A (en) 1965-04-20 1970-09-29 Ethicon Inc Suture preparation
BE758156R (en) 1970-05-13 1971-04-28 Ethicon Inc ABSORBABLE SUTURE ELEMENT AND ITS
US3797499A (en) 1970-05-13 1974-03-19 Ethicon Inc Polylactide fabric graphs for surgical implantation
US3736646A (en) 1971-10-18 1973-06-05 American Cyanamid Co Method of attaching surgical needles to multifilament polyglycolic acid absorbable sutures
DE2817778A1 (en) * 1977-05-09 1978-11-23 Firestone Tire & Rubber Co FIBERGLASS REINFORCED POLYAMIDE COMPOSITIONS
US4137921A (en) 1977-06-24 1979-02-06 Ethicon, Inc. Addition copolymers of lactide and glycolide and method of preparation
US4181983A (en) 1977-08-29 1980-01-08 Kulkarni R K Assimilable hydrophilic prosthesis
DE2947985A1 (en) * 1979-11-28 1981-09-17 Vsesojuznyj naučno-issledovatel'skij i ispytatel'nyj institut medicinskoj techniki, Moskva Matrix material for fixing bone fractures - consisting of a copolymer of hydrophilic and hydrophobic monomers reinforced with resorbable non-non-toxic fibres
JPS56164842A (en) * 1980-05-23 1981-12-18 Toray Industries Carbon fiber reinforced thermoplastic resin molding
JPS5798556A (en) * 1980-10-20 1982-06-18 American Cyanamid Co Refomation of polyglycolic acid obtaining variable vital body physical properties
US5110852A (en) 1982-07-16 1992-05-05 Rijksuniversiteit Te Groningen Filament material polylactide mixtures
US4700704A (en) 1982-10-01 1987-10-20 Ethicon, Inc. Surgical articles of copolymers of glycolide and ε-caprolactone and methods of producing the same
US4523591A (en) 1982-10-22 1985-06-18 Kaplan Donald S Polymers for injection molding of absorbable surgical devices
US4539981A (en) 1982-11-08 1985-09-10 Johnson & Johnson Products, Inc. Absorbable bone fixation device
US4438253A (en) 1982-11-12 1984-03-20 American Cyanamid Company Poly(glycolic acid)/poly(alkylene glycol) block copolymers and method of manufacturing the same
JPS6017118A (en) * 1983-07-06 1985-01-29 Mitsubishi Mining & Cement Co Ltd Calcium phosphate fiber
US4636215A (en) 1984-01-11 1987-01-13 Rei, Inc. Combination tray and condylar prosthesis for mandibular reconstruction and the like
US4990161A (en) 1984-03-16 1991-02-05 Kampner Stanley L Implant with resorbable stem
US4559945A (en) 1984-09-21 1985-12-24 Ethicon, Inc. Absorbable crystalline alkylene malonate copolyesters and surgical devices therefrom
US4604097A (en) * 1985-02-19 1986-08-05 University Of Dayton Bioabsorbable glass fibers for use in the reinforcement of bioabsorbable polymers for bone fixation devices and artificial ligaments
FI75493C (en) 1985-05-08 1988-07-11 Materials Consultants Oy SJAELVARMERAT ABSORBERBART PURCHASING SYNTHESIS.
US6005161A (en) 1986-01-28 1999-12-21 Thm Biomedical, Inc. Method and device for reconstruction of articular cartilage
FI80605C (en) * 1986-11-03 1990-07-10 Biocon Oy Bone surgical biocomposite material
FI81498C (en) * 1987-01-13 1990-11-12 Biocon Oy SURGICAL MATERIAL OCH INSTRUMENT.
US4756307A (en) 1987-02-09 1988-07-12 Zimmer, Inc. Nail device
JPH0781204B2 (en) * 1987-04-21 1995-08-30 株式会社バイオマテリアルユニバ−ス Polylactic acid fiber
US5527337A (en) 1987-06-25 1996-06-18 Duke University Bioabsorbable stent and method of making the same
DE8716607U1 (en) 1987-12-14 1989-01-12 Mecron Medizinische Produkte GmbH, 12277 Berlin Implantable prosthesis
US4916207A (en) 1987-12-17 1990-04-10 Allied-Signal, Inc. Polycarbonate homopolymer-based fiber compositions and method of melt-spinning same and device
JP2561853B2 (en) 1988-01-28 1996-12-11 株式会社ジェイ・エム・エス Shaped memory molded article and method of using the same
GB2215209B (en) 1988-03-14 1992-08-26 Osmed Inc Method and apparatus for biodegradable, osteogenic, bone graft substitute device
US5444113A (en) 1988-08-08 1995-08-22 Ecopol, Llc End use applications of biodegradable polymers
US5502158A (en) 1988-08-08 1996-03-26 Ecopol, Llc Degradable polymer composition
US5250584A (en) 1988-08-31 1993-10-05 G-C Dental Industrial Corp. Periodontium-regenerative materials
JPH0739506B2 (en) 1988-09-30 1995-05-01 三菱重工業株式会社 Shape memory polymer foam
US4938763B1 (en) 1988-10-03 1995-07-04 Atrix Lab Inc Biodegradable in-situ forming implants and method of producing the same
US5633002A (en) 1988-10-04 1997-05-27 Boehringer Ingelheim Gmbh Implantable, biodegradable system for releasing active substance
DE3936188A1 (en) 1988-11-01 1990-05-03 Boehringer Ingelheim Kg Continuous prodn. of bio:absorbable polyester(s) - by polymerisation in temp.-controlled extruder
FI85223C (en) 1988-11-10 1992-03-25 Biocon Oy BIODEGRADERANDE SURGICAL IMPLANT OCH MEDEL.
US5037178A (en) 1988-12-22 1991-08-06 Kingston Technologies, L.P. Amorphous memory polymer alignment device
FR2641692A1 (en) 1989-01-17 1990-07-20 Nippon Zeon Co Plug for closing an opening for a medical application, and device for the closure plug making use thereof
US5108755A (en) 1989-04-27 1992-04-28 Sri International Biodegradable composites for internal medical use
DK0401844T3 (en) 1989-06-09 1996-02-19 Aesculap Ag Resorbable moldings and processes for making them
US5294395A (en) 1989-09-01 1994-03-15 Ethicon, Inc. Thermal treatment of theraplastic filaments for the preparation of surgical sutures
DE58908155D1 (en) 1989-09-15 1994-09-08 N Proizv Ob Edinenie Kompleksn ENDOPROTHESIS OF THE HIP JOINT.
US5053035A (en) 1990-05-24 1991-10-01 Mclaren Alexander C Flexible intramedullary fixation rod
US7208013B1 (en) 1990-06-28 2007-04-24 Bonutti Ip, Llc Composite surgical devices
IL94910A (en) 1990-06-29 1994-04-12 Technion Research Dev Foundati Biomedical adhesive compositions
US5047035A (en) 1990-08-10 1991-09-10 Mikhail Michael W E System for performing hip prosthesis revision surgery
ATE139126T1 (en) 1990-09-10 1996-06-15 Synthes Ag MEMBRANE FOR BONE REGENERATION
CA2062012C (en) 1991-03-05 2003-04-29 Randall D. Ross Bioabsorbable interference bone fixation screw
DE4110316A1 (en) 1991-03-28 1992-10-01 Uwe Storch USE OF A MIXTURE FOR THE PRODUCTION OF MEDICAL IMPLANTS
EP0520177B1 (en) 1991-05-24 1995-12-13 Synthes AG, Chur Resorbable tendon and bone augmentation device
EP0523926A3 (en) 1991-07-15 1993-12-01 Smith & Nephew Richards Inc Prosthetic implants with bioabsorbable coating
DE4226465C2 (en) 1991-08-10 2003-12-04 Gunze Kk Jaw bone reproductive material
US5275601A (en) 1991-09-03 1994-01-04 Synthes (U.S.A) Self-locking resorbable screws and plates for internal fixation of bone fractures and tendon-to-bone attachment
US5500013A (en) 1991-10-04 1996-03-19 Scimed Life Systems, Inc. Biodegradable drug delivery vascular stent
US5360448A (en) 1991-10-07 1994-11-01 Thramann Jeffrey J Porous-coated bone screw for securing prosthesis
US5383931A (en) 1992-01-03 1995-01-24 Synthes (U.S.A.) Resorbable implantable device for the reconstruction of the orbit of the human skull
FI95537C (en) 1992-01-24 1996-02-26 Biocon Oy Surgical implant
ES2125329T3 (en) 1992-02-14 1999-03-01 Smith & Nephew Inc SCREWS OF POLYMER MATERIALS AND COATINGS FOR SURGICAL USES.
US5333624A (en) 1992-02-24 1994-08-02 United States Surgical Corporation Surgical attaching apparatus
US5571193A (en) 1992-03-12 1996-11-05 Kampner; Stanley L. Implant with reinforced resorbable stem
US5407445A (en) 1992-05-20 1995-04-18 Cytrx Corporation Gel composition for implant prosthesis and method of use
DE4220216C1 (en) 1992-06-20 1994-01-13 S & G Implants Gmbh Endoprosthesis - has bio-resorbable distance rings to set gap between prosthesis and bone
US5319003A (en) * 1992-09-30 1994-06-07 Union Carbide Chemicals & Plastics Technology Corporation Method for improving the mechanical performance of composite articles
WO1994008078A1 (en) 1992-10-02 1994-04-14 Cargill, Incorporated A melt-stable lactide polymer fabric and process for manufacture thereof
US5376120A (en) 1992-10-21 1994-12-27 Biomet, Inc. Biocompatible implant and method of using same
US5437918A (en) 1992-11-11 1995-08-01 Mitsui Toatsu Chemicals, Inc. Degradable non-woven fabric and preparation process thereof
US5441515A (en) 1993-04-23 1995-08-15 Advanced Cardiovascular Systems, Inc. Ratcheting stent
US5716410A (en) 1993-04-30 1998-02-10 Scimed Life Systems, Inc. Temporary stent and method of use
FR2707477A1 (en) 1993-07-02 1995-01-20 Cahlix Marc Andre Obturator for bone cavities
CA2127636C (en) 1993-07-21 2009-10-20 Cheng-Kung Liu Plasticizers for fibers used to form surgical devices
US6315788B1 (en) 1994-02-10 2001-11-13 United States Surgical Corporation Composite materials and surgical articles made therefrom
US5417712A (en) 1994-02-17 1995-05-23 Mitek Surgical Products, Inc. Bone anchor
US5569250A (en) 1994-03-01 1996-10-29 Sarver; David R. Method and apparatus for securing adjacent bone portions
AU689846B2 (en) 1994-03-29 1998-04-09 Zimmer Gmbh Screw made of biodegradable material for bone surgery purposes, and screwdriver suitable therefor
US5626861A (en) 1994-04-01 1997-05-06 Massachusetts Institute Of Technology Polymeric-hydroxyapatite bone composite
US5947893A (en) 1994-04-27 1999-09-07 Board Of Regents, The University Of Texas System Method of making a porous prothesis with biodegradable coatings
US6001101A (en) 1994-07-05 1999-12-14 Depuy France Screw device with threaded head for permitting the coaptation of two bone fragments
DE4424883A1 (en) 1994-07-14 1996-01-18 Merck Patent Gmbh Femoral prosthesis
EP0696605B1 (en) 1994-08-10 2000-09-20 Peter Neuenschwander Biocompatible block copolymer
US5837276A (en) 1994-09-02 1998-11-17 Delab Apparatus for the delivery of elongate solid drug compositions
FR2725617B1 (en) 1994-10-12 1997-09-19 Prost Didier FEMALE ROD FOR HIP PROSTHESIS
US5690671A (en) 1994-12-13 1997-11-25 Micro Interventional Systems, Inc. Embolic elements and methods and apparatus for their delivery
US5741329A (en) 1994-12-21 1998-04-21 Board Of Regents, The University Of Texas System Method of controlling the pH in the vicinity of biodegradable implants
US5634936A (en) 1995-02-06 1997-06-03 Scimed Life Systems, Inc. Device for closing a septal defect
ES2140828T3 (en) * 1995-03-13 2000-03-01 Rue De Int Ltd SECURITY ROLE.
US6027742A (en) * 1995-05-19 2000-02-22 Etex Corporation Bioresorbable ceramic composites
US5641502A (en) 1995-06-07 1997-06-24 United States Surgical Corporation Biodegradable moldable surgical material
US5633343A (en) 1995-06-30 1997-05-27 Ethicon, Inc. High strength, fast absorbing, melt processable, gycolide-rich, poly(glycolide-co-p-dioxanone) copolymers
FI98136C (en) 1995-09-27 1997-04-25 Biocon Oy A tissue-soluble material and process for its manufacture
US6113624A (en) 1995-10-02 2000-09-05 Ethicon, Inc. Absorbable elastomeric polymer
US5716413A (en) 1995-10-11 1998-02-10 Osteobiologics, Inc. Moldable, hand-shapable biodegradable implant material
US6902584B2 (en) 1995-10-16 2005-06-07 Depuy Spine, Inc. Bone grafting matrix
US6419945B1 (en) * 1996-01-17 2002-07-16 Cambridge Scientific, Inc. Buffered resorbable internal fixation devices and methods for making material therefore
US5817328A (en) 1996-01-17 1998-10-06 Cambridge Scientific, Inc. Material for buffered resorbable internal fixation devices and method for making same
US5902599A (en) 1996-02-20 1999-05-11 Massachusetts Institute Of Technology Biodegradable polymer networks for use in orthopedic and dental applications
US5856288A (en) 1996-04-26 1999-01-05 Nippon Shokubai Co., Ltd. Polyalkylene glycol-polyglyoxylate block copolymer, its production process and use
JP3731838B2 (en) 1996-04-30 2006-01-05 株式会社クレハ Polyglycolic acid oriented film and method for producing the same
EP0806283B1 (en) 1996-05-09 2003-10-01 Kureha Kagaku Kogyo Kabushiki Kaisha Stretch blow molded container and production process thereof
US6143948A (en) 1996-05-10 2000-11-07 Isotis B.V. Device for incorporation and release of biologically active agents
US5670161A (en) 1996-05-28 1997-09-23 Healy; Kevin E. Biodegradable stent
CA2252860C (en) 1996-05-28 2011-03-22 1218122 Ontario Inc. Resorbable implant biomaterial made of condensed calcium phosphate particles
US5935172A (en) 1996-06-28 1999-08-10 Johnson & Johnson Professional, Inc. Prosthesis with variable fit and strain distribution
US5824413A (en) * 1996-07-15 1998-10-20 Ppg Industries, Inc. Secondary coating for fiber strands, coated strand reinforcements, reinforced polymeric composites and a method of reinforcing a polymeric material
US5756651A (en) 1996-07-17 1998-05-26 Chronopol, Inc. Impact modified polylactide
US5904658A (en) 1996-08-23 1999-05-18 Osteobiologics, Inc. Hand-held materials tester
US7351421B2 (en) 1996-11-05 2008-04-01 Hsing-Wen Sung Drug-eluting stent having collagen drug carrier chemically treated with genipin
US5893850A (en) 1996-11-12 1999-04-13 Cachia; Victor V. Bone fixation device
US6139963A (en) * 1996-11-28 2000-10-31 Kuraray Co., Ltd. Polyvinyl alcohol hydrogel and process for producing the same
DE69732721T2 (en) 1996-12-03 2006-05-18 Osteobiologics, Inc., San Antonio BIODEGRADABLE ARTIFICIAL FILMS
US5733330A (en) 1997-01-13 1998-03-31 Advanced Cardiovascular Systems, Inc. Balloon-expandable, crush-resistant locking stent
SE512050C2 (en) 1997-01-21 2000-01-17 Nobel Biocare Ab Rotationally symmetrical leg anchoring element
US5997580A (en) 1997-03-27 1999-12-07 Johnson & Johnson Professional, Inc. Cement restrictor including shape memory material
US5977204A (en) 1997-04-11 1999-11-02 Osteobiologics, Inc. Biodegradable implant material comprising bioactive ceramic
US6071982A (en) 1997-04-18 2000-06-06 Cambridge Scientific, Inc. Bioerodible polymeric semi-interpenetrating network alloys for surgical plates and bone cements, and method for making same
JPH10298435A (en) * 1997-04-24 1998-11-10 Dainippon Ink & Chem Inc Biodegradable molding, biodegradable material and their production
JP3503045B2 (en) 1997-05-13 2004-03-02 タキロン株式会社 Shape memory biodegradable absorbent material
WO1998053768A1 (en) 1997-05-30 1998-12-03 Osteobiologics, Inc. Fiber-reinforced, porous, biodegradable implant device
US7524335B2 (en) 1997-05-30 2009-04-28 Smith & Nephew, Inc. Fiber-reinforced, porous, biodegradable implant device
US5980564A (en) 1997-08-01 1999-11-09 Schneider (Usa) Inc. Bioabsorbable implantable endoprosthesis with reservoir
US6001100A (en) 1997-08-19 1999-12-14 Bionx Implants Oy Bone block fixation implant
GB9717433D0 (en) 1997-08-19 1997-10-22 Univ Nottingham Biodegradable composites
US7541049B1 (en) 1997-09-02 2009-06-02 Linvatec Biomaterials Oy Bioactive and biodegradable composites of polymers and ceramics or glasses and method to manufacture such composites
US7985415B2 (en) 1997-09-10 2011-07-26 Rutgers, The State University Of New Jersey Medical devices employing novel polymers
SE510868C2 (en) 1997-11-03 1999-07-05 Artimplant Dev Artdev Ab Molds for use as implants in human medicine and a method for making such molds
US6168570B1 (en) 1997-12-05 2001-01-02 Micrus Corporation Micro-strand cable with enhanced radiopacity
CA2314963A1 (en) * 1998-01-06 1999-07-15 Bioamide, Inc. Bioabsorbable fibers and reinforced composites produced therefrom
US6150497A (en) 1998-01-14 2000-11-21 Sherwood Services Ag Method for the production of polyglycolic acid
WO1999040865A1 (en) 1998-02-13 1999-08-19 Chugai Seiyaku Kabushikikaisha Bone fixing pin
US6160084A (en) 1998-02-23 2000-12-12 Massachusetts Institute Of Technology Biodegradable shape memory polymers
CA2316945A1 (en) 1998-02-23 1999-08-26 Mnemoscience Gmbh Shape memory polymers
BR9908806A (en) 1998-03-11 2001-12-18 Dow Chemical Co Structures and articles manufactured having format memory made of "alpha" -olefin / vinyl or aromatic vinylidene interpolymers and / or hindered vinyl or aliphatic vinyl
US5997582A (en) 1998-05-01 1999-12-07 Weiss; James M. Hip replacement methods and apparatus
KR100569179B1 (en) 1998-05-28 2006-04-07 군제 가부시키가이샤 Lactide-containing polymer and medical material
US5939453A (en) 1998-06-04 1999-08-17 Advanced Polymer Systems, Inc. PEG-POE, PEG-POE-PEG, and POE-PEG-POE block copolymers
US20020022588A1 (en) 1998-06-23 2002-02-21 James Wilkie Methods and compositions for sealing tissue leaks
EP0968690A1 (en) 1998-07-02 2000-01-05 Sulzer Orthopädie AG Plug system for the medullary canal of a tubular bone
US6248430B1 (en) 1998-08-11 2001-06-19 Dainippon Ink And Chemicals, Inc. Lactic acid-based polymer laminated product and molded product
SE515572C2 (en) 1998-09-09 2001-09-03 Lanka Ltd Implants, ways of making it and using it
JP2000085054A (en) 1998-09-14 2000-03-28 Daicel Chem Ind Ltd Collapsible laminate and manufacture thereof
US6248108B1 (en) 1998-09-30 2001-06-19 Bionx Implants Oy Bioabsorbable surgical screw and washer system
US6162225A (en) 1998-10-26 2000-12-19 Musculoskeletal Transplant Foundation Allograft bone fixation screw method and apparatus
US6255408B1 (en) 1998-11-06 2001-07-03 Poly-Med, Inc. Copolyesters with minimized hydrolytic instability and crystalline absorbable copolymers thereof
EP1000958B1 (en) 1998-11-12 2004-03-17 Takiron Co. Ltd. Shape-memory, biodegradable and absorbable material
US6283973B1 (en) 1998-12-30 2001-09-04 Depuy Orthopaedics, Inc. Strength fixation device
US6147135A (en) 1998-12-31 2000-11-14 Ethicon, Inc. Fabrication of biocompatible polymeric composites
US6293950B1 (en) 1999-01-15 2001-09-25 Luitpold Pharmaceuticals, Inc. Resorbable pin systems
AU757391B2 (en) 1999-02-04 2003-02-20 Synthes Gmbh Bone screw
US6299448B1 (en) 1999-02-17 2001-10-09 Ivanka J. Zdrahala Surgical implant system for restoration and repair of body function
US6206883B1 (en) 1999-03-05 2001-03-27 Stryker Technologies Corporation Bioabsorbable materials and medical devices made therefrom
AU6406700A (en) 1999-03-16 2000-10-04 Regeneration Technologies, Inc. Molded implants for orthopedic applications
EP1277482A3 (en) 1999-03-19 2005-05-11 The Regents of The University of Michigan Mineralization and cellular patterning on biomaterial surfaces
EP1867348B1 (en) 1999-03-25 2012-05-16 Metabolix, Inc. Medical devices and applications of polyhydroxyalkanoate polymers
US6296645B1 (en) 1999-04-09 2001-10-02 Depuy Orthopaedics, Inc. Intramedullary nail with non-metal spacers
US7462162B2 (en) 2001-09-04 2008-12-09 Broncus Technologies, Inc. Antiproliferative devices for maintaining patency of surgically created channels in a body organ
US20050177144A1 (en) 1999-08-05 2005-08-11 Broncus Technologies, Inc. Methods and devices for maintaining patency of surgically created channels in a body organ
US20050137715A1 (en) 1999-08-05 2005-06-23 Broncus Technologies, Inc. Methods and devices for maintaining patency of surgically created channels in a body organ
US7033603B2 (en) * 1999-08-06 2006-04-25 Board Of Regents The University Of Texas Drug releasing biodegradable fiber for delivery of therapeutics
CA2319969A1 (en) 1999-09-24 2001-03-24 Isotis B.V. Composites
DE59901812D1 (en) 1999-10-21 2002-07-25 Storz Karl Gmbh & Co Kg interference screw
US6579533B1 (en) 1999-11-30 2003-06-17 Bioasborbable Concepts, Ltd. Bioabsorbable drug delivery system for local treatment and prevention of infections
CN1215231C (en) * 1999-12-17 2005-08-17 三井化学株式会社 Road reinforcing sheet, structure of asphalt reinforced pavement and method for paving road
EP1110510B1 (en) 1999-12-23 2002-03-27 Karl Storz GmbH & Co. KG Screw driven non-centrally
US6630153B2 (en) 2001-02-23 2003-10-07 Smith & Nephew, Inc. Manufacture of bone graft substitutes
US6425923B1 (en) 2000-03-07 2002-07-30 Zimmer, Inc. Contourable polymer filled implant
US20040052992A1 (en) 2000-03-16 2004-03-18 Adele Boone Biodegradeable shrink wrap
AU2815001A (en) 2000-03-24 2001-09-27 Ethicon Inc. Thermoforming of absorbable medical devices
US6468277B1 (en) 2000-04-04 2002-10-22 Ethicon, Inc. Orthopedic screw and method
JP2001303387A (en) * 2000-04-26 2001-10-31 Kyowa Co Ltd Sheet for construction work having biodegradability
US6869445B1 (en) 2000-05-04 2005-03-22 Phillips Plastics Corp. Packable ceramic beads for bone repair
CA2410637C (en) 2000-05-31 2007-04-10 Mnemoscience Gmbh Shape memory polymers seeded with dissociated cells for tissue engineering
US6447515B1 (en) 2000-06-21 2002-09-10 Russell Meldrum Bioresorbable implant for fracture fixation
CA2771263A1 (en) 2000-07-27 2002-02-07 Rutgers, The State University Therapeutic polyesters and polyamides
CA2418380A1 (en) 2000-08-17 2002-02-21 Tyco Healthcare Group Lp Sutures and coatings made from therapeutic absorbable glass
ATE377048T1 (en) 2000-09-06 2007-11-15 Ap Pharma Inc DEGRADABLE POLYACETAL POLYMERS
JP2002078790A (en) * 2000-09-06 2002-03-19 Gunze Ltd Medical material for osteosynthesis and method of manufacturing for the same
US6605090B1 (en) 2000-10-25 2003-08-12 Sdgi Holdings, Inc. Non-metallic implant devices and intra-operative methods for assembly and fixation
US6613089B1 (en) 2000-10-25 2003-09-02 Sdgi Holdings, Inc. Laterally expanding intervertebral fusion device
AU2002243270B2 (en) 2000-10-25 2006-03-09 Warsaw Orthopedic, Inc. Vertically expanding intervertebral body fusion device
US7776310B2 (en) 2000-11-16 2010-08-17 Microspherix Llc Flexible and/or elastic brachytherapy seed or strand
US6599323B2 (en) 2000-12-21 2003-07-29 Ethicon, Inc. Reinforced tissue implants and methods of manufacture and use
JP2004517187A (en) * 2000-12-29 2004-06-10 チバ スペシャルティ ケミカルズ ホールディング インコーポレーテッド Polyester composition with low residual aldehyde content
US6719935B2 (en) 2001-01-05 2004-04-13 Howmedica Osteonics Corp. Process for forming bioabsorbable implants
US6623487B1 (en) 2001-02-13 2003-09-23 Biomet, Inc. Temperature sensitive surgical fastener
US6827743B2 (en) 2001-02-28 2004-12-07 Sdgi Holdings, Inc. Woven orthopedic implants
JP4412901B2 (en) 2001-03-02 2010-02-10 ウッドウェルディング・アクチェンゲゼルシャフト Implants for making connections to tissue parts, in particular skeletal parts, and devices and methods for implantation of implants
US6913765B2 (en) 2001-03-21 2005-07-05 Scimed Life Systems, Inc. Controlling resorption of bioresorbable medical implant material
AUPR408001A0 (en) 2001-03-29 2001-04-26 Cochlear Limited Laminated electrode for a cochlear implant
US20040265385A1 (en) 2001-04-12 2004-12-30 Therics, Inc. Porous biostructure partially occupied by interpenetrant and method for making same
US6726696B1 (en) 2001-04-24 2004-04-27 Advanced Catheter Engineering, Inc. Patches and collars for medical applications and methods of use
TWI267378B (en) * 2001-06-08 2006-12-01 Wyeth Corp Calcium phosphate delivery vehicles for osteoinductive proteins
GB0115320D0 (en) 2001-06-22 2001-08-15 Univ Nottingham Matrix
GB0116341D0 (en) * 2001-07-04 2001-08-29 Smith & Nephew Biodegradable polymer systems
AUPR626401A0 (en) 2001-07-10 2001-08-02 Australian Surgical Design And Manufacture Pty Limited Surgical fixation device
US6494916B1 (en) 2001-07-30 2002-12-17 Biomed Solutions, Llc Apparatus for replacing musculo-skeletal parts
US6749639B2 (en) 2001-08-27 2004-06-15 Mayo Foundation For Medical Education And Research Coated prosthetic implant
US6841111B2 (en) 2001-08-31 2005-01-11 Basf Corporation Method for making a polyurea-polyurethane composite structure substantially free of volatile organic compounds
US20050137611A1 (en) 2001-09-04 2005-06-23 Broncus Technologies, Inc. Methods and devices for maintaining surgically created channels in a body organ
US7708712B2 (en) 2001-09-04 2010-05-04 Broncus Technologies, Inc. Methods and devices for maintaining patency of surgically created channels in a body organ
US6916321B2 (en) 2001-09-28 2005-07-12 Ethicon, Inc. Self-tapping resorbable two-piece bone screw
JP2003126238A (en) * 2001-10-22 2003-05-07 Gunze Ltd Base material for regenerating bone and osteochondro- bone
US20030125745A1 (en) 2001-11-05 2003-07-03 Bio One Tech Inc. Bone-fixing device
WO2003045460A1 (en) 2001-11-27 2003-06-05 Takiron Co., Ltd. Implant material and process for producing the same
JP3631994B2 (en) * 2001-11-29 2005-03-23 旭ファイバーグラス株式会社 Long fiber reinforced thermoplastic resin sheet and composite molded body reinforced by the sheet
EP1448166A1 (en) 2001-11-30 2004-08-25 Pfizer Inc. Controlled release polymeric compositions of bone growth promoting compounds
US7713272B2 (en) 2001-12-20 2010-05-11 Ethicon, Inc. Bioabsorbable coatings of surgical devices
ATE337760T1 (en) 2001-12-21 2006-09-15 Smith & Nephew Inc ROTATING JOINT SYSTEM
SE524709C2 (en) 2002-01-11 2004-09-21 Edwards Lifesciences Ag Device for delayed reshaping of a heart vessel and a heart valve
EP2181670A3 (en) 2001-12-28 2011-05-25 Edwards Lifesciences AG Device for reshaping a cardiac valve
GB0202233D0 (en) 2002-01-31 2002-03-20 Smith & Nephew Bioresorbable polymers
WO2003065996A2 (en) 2002-02-05 2003-08-14 Cambridge Scientific, Inc. Bioresorbable osteoconductive compositions for bone regeneration
US20030153971A1 (en) 2002-02-14 2003-08-14 Chandru Chandrasekaran Metal reinforced biodegradable intraluminal stents
US20030153972A1 (en) 2002-02-14 2003-08-14 Michael Helmus Biodegradable implantable or insertable medical devices with controlled change of physical properties leading to biomechanical compatibility
US6758862B2 (en) 2002-03-21 2004-07-06 Sdgi Holdings, Inc. Vertebral body and disc space replacement devices
US6843799B2 (en) 2002-03-25 2005-01-18 Edwin C. Bartlett Suture anchor system and associated method
WO2003080119A1 (en) 2002-03-26 2003-10-02 Yissum Research Development Company Of The Hebrew University Of Jerusalem Responsive biomedical composites
EP1501424B1 (en) 2002-04-18 2018-06-06 Helmholtz-Zentrum Geesthacht Zentrum für Material- und Küstenforschung GmbH Biodegradable shape memory polymeric sutures
DE10217350C1 (en) 2002-04-18 2003-12-18 Mnemoscience Gmbh polyesterurethanes
US7261734B2 (en) 2002-04-23 2007-08-28 Boston Scientific Scimed, Inc. Resorption-controllable medical implants
US6830575B2 (en) 2002-05-08 2004-12-14 Scimed Life Systems, Inc. Method and device for providing full protection to a stent
US6869985B2 (en) * 2002-05-10 2005-03-22 Awi Licensing Company Environmentally friendly polylactide-based composite formulations
US7166133B2 (en) 2002-06-13 2007-01-23 Kensey Nash Corporation Devices and methods for treating defects in the tissue of a living being
US7192448B2 (en) 2002-06-27 2007-03-20 Ferree Bret A Arthroplasty devices with resorbable component
US20040002770A1 (en) 2002-06-28 2004-01-01 King Richard S. Polymer-bioceramic composite for orthopaedic applications and method of manufacture thereof
US20050019404A1 (en) 2003-06-30 2005-01-27 Hsing-Wen Sung Drug-eluting biodegradable stent
ES2388623T3 (en) 2002-09-05 2012-10-17 Catherine G. Ambrose Antibiotic microspheres for the treatment of infections and osteomyelitis
AU2003270802A1 (en) 2002-09-20 2004-04-08 The Children's Hospital Of Philadelphia Engineering of material surfaces
EP1549359A2 (en) 2002-10-08 2005-07-06 Osteotech, Inc. Coupling agents for orthopedic biomaterials
AU2003300377B2 (en) 2002-10-11 2009-04-02 University Of Connecticut Blends of amorphous and semicrystalline polymers having shape memory properties
US20040078090A1 (en) * 2002-10-18 2004-04-22 Francois Binette Biocompatible scaffolds with tissue fragments
JP4467059B2 (en) 2002-11-12 2010-05-26 カーモン ベン−ジオン Expansion device and method for tissue expansion, regeneration and fixation
JP2006509539A (en) 2002-12-12 2006-03-23 オステオテック,インコーポレイテッド Formable and curable polymer bone composite and method for producing the same
US20050251267A1 (en) * 2004-05-04 2005-11-10 John Winterbottom Cell permeable structural implant
EP1433489A1 (en) 2002-12-23 2004-06-30 Degradable Solutions AG Biodegradable porous bone implant with a barrier membrane sealed thereto
US20040143221A1 (en) 2002-12-27 2004-07-22 Shadduck John H. Biomedical implant for sustained agent release
US20050013793A1 (en) 2003-01-16 2005-01-20 Beckman Eric J. Biodegradable polyurethanes and use thereof
EP1596765A2 (en) 2003-02-10 2005-11-23 Smith & Nephew, Inc. Resorbable devices
US20040156878A1 (en) 2003-02-11 2004-08-12 Alireza Rezania Implantable medical device seeded with mammalian cells and methods of treatment
US20070043376A1 (en) 2003-02-21 2007-02-22 Osteobiologics, Inc. Bone and cartilage implant delivery device
US20040193154A1 (en) 2003-02-21 2004-09-30 Osteobiologics, Inc. Bone and cartilage implant delivery device
US7314480B2 (en) 2003-02-27 2008-01-01 Boston Scientific Scimed, Inc. Rotating balloon expandable sheath bifurcation delivery
US20070065652A1 (en) 2003-03-13 2007-03-22 Willaim Marsh Rice University Composite injectable and pre-fabricated bone replacement material and method for the production of such bone replacement material
GB0307011D0 (en) 2003-03-27 2003-04-30 Regentec Ltd Porous matrix
US7012106B2 (en) 2003-03-28 2006-03-14 Ethicon, Inc. Reinforced implantable medical devices
NZ544074A (en) 2003-06-12 2007-10-26 Synthes Gmbh Intramedullary surgical pin with transverse hole and insert
CA2527976C (en) 2003-06-13 2011-11-22 Mnemoscience Gmbh Stents
US6974862B2 (en) 2003-06-20 2005-12-13 Kensey Nash Corporation High density fibrous polymers suitable for implant
US7300439B2 (en) 2003-06-24 2007-11-27 Depuy Mitek, Inc. Porous resorbable graft fixation pin
GB0317192D0 (en) 2003-07-19 2003-08-27 Smith & Nephew High strength bioresorbable co-polymers
US7794476B2 (en) 2003-08-08 2010-09-14 Warsaw Orthopedic, Inc. Implants formed of shape memory polymeric material for spinal fixation
FI120333B (en) 2003-08-20 2009-09-30 Bioretec Oy A porous medical device and a method of making it
DE10340392A1 (en) 2003-09-02 2005-04-07 Mnemoscience Gmbh Amorphous polyester urethane networks with shape-memory properties
CA2539751C (en) * 2003-09-05 2016-04-26 Norian Corporation Bone cement compositions having fiber-reinforcement and/or increased flowability
US7648504B2 (en) 2003-09-09 2010-01-19 Bioretec Ltd Bioabsorbable band system
JP4251061B2 (en) 2003-10-03 2009-04-08 ブリヂストンスポーツ株式会社 Golf club head
US20050085814A1 (en) * 2003-10-21 2005-04-21 Sherman Michael C. Dynamizable orthopedic implants and their use in treating bone defects
US7699879B2 (en) 2003-10-21 2010-04-20 Warsaw Orthopedic, Inc. Apparatus and method for providing dynamizable translations to orthopedic implants
US7645292B2 (en) 2003-10-27 2010-01-12 Boston Scientific Scimed, Inc. Vaso-occlusive devices with in-situ stiffening elements
US7689260B2 (en) 2003-11-06 2010-03-30 The Regents Of The University Of Colorado Shape-memory polymer coated electrodes
US8157855B2 (en) 2003-12-05 2012-04-17 Boston Scientific Scimed, Inc. Detachable segment stent
US20050136764A1 (en) 2003-12-18 2005-06-23 Sherman Michael C. Designed composite degradation for spinal implants
GB0329654D0 (en) * 2003-12-23 2004-01-28 Smith & Nephew Tunable segmented polyacetal
WO2005069884A2 (en) 2004-01-16 2005-08-04 Osteobiologics, Inc. Bone-tendon-bone implant
US20050177245A1 (en) 2004-02-05 2005-08-11 Leatherbury Neil C. Absorbable orthopedic implants
US7378144B2 (en) 2004-02-17 2008-05-27 Kensey Nash Corporation Oriented polymer implantable device and process for making same
US8882786B2 (en) 2004-02-17 2014-11-11 Lawrence Livermore National Security, Llc. System for closure of a physical anomaly
US7744619B2 (en) 2004-02-24 2010-06-29 Boston Scientific Scimed, Inc. Rotatable catheter assembly
US8729202B2 (en) 2004-03-03 2014-05-20 Polynovo Biomaterials Pty Limited Biocompatible polymer compositions for dual or multi staged curing
CN1942498A (en) 2004-03-03 2007-04-04 联邦科学和工业研究组织 Polymer compositions for dual or multi staged curing
CA2555586A1 (en) 2004-03-09 2005-09-22 Osteobiologics, Inc. Implant scaffold combined with autologous or allogenic tissue
CN1263519C (en) * 2004-03-17 2006-07-12 武汉理工大学 Method for preparing artificial head bones made from composite material and for modifying surface
JP5496457B2 (en) 2004-03-24 2014-05-21 ポリィノボ バイオマテリアルズ ピーティワイ リミテッド Biodegradable polyurethane and polyurethaneurea
CN100471912C (en) * 2004-04-06 2009-03-25 石宗利 Phosphate fibrous reinforced polylactic composite material with controllable degradable absorbing biological activity and preparation thereof
US7285130B2 (en) 2004-04-27 2007-10-23 Boston Scientific Scimed, Inc. Stent delivery system
ATE481044T1 (en) 2004-05-21 2010-10-15 Myers Surgical Solutions Llc FRACTURE FIXATION AND SITUS STABILIZATION SYSTEM
US7824434B2 (en) 2004-06-07 2010-11-02 Degima Gmbh Self foreshortening fastener
US20080249633A1 (en) 2006-08-22 2008-10-09 Tim Wu Biodegradable Materials and Methods of Use
EP1604693A1 (en) 2004-06-09 2005-12-14 Scil Technology GmbH In situ forming scaffold, its manufacturing and use
US7285087B2 (en) 2004-07-15 2007-10-23 Micardia Corporation Shape memory devices and methods for reshaping heart anatomy
CA2574933C (en) 2004-07-26 2015-05-19 Synthes (U.S.A.) Biocompatible, biodegradable polyurethane materials with controlled hydrophobic to hydrophilic ratio
CA2576007A1 (en) 2004-07-30 2006-02-09 University Of Nebraska Bioresorbable composites and method of formation thereof
CN101018512B (en) * 2004-08-13 2011-05-18 马斯特生物外科股份公司 Surgical prosthesis having biodegradable and nonbiodegradable regions
US20060067971A1 (en) 2004-09-27 2006-03-30 Story Brooks J Bone void filler
US20060120994A1 (en) * 2004-10-29 2006-06-08 Cotton Nicholas J Bioabsorbable polymers
US20080267963A1 (en) * 2004-11-02 2008-10-30 Biomedical Research Model, Inc. Methods of Cancer Treatment/Prevention Using Cancer Cell-Specific Surface Antigens
WO2006055261A2 (en) 2004-11-05 2006-05-26 Carnegie Mellon University Degradable polyurethane foams
FI122108B (en) 2004-11-17 2011-08-31 Jvs Polymers Oy Crosslinking biopolymer
JP2008521560A (en) 2004-11-30 2008-06-26 オステオバイオロジクス・インコーポレーテッド Implant and its delivery system for treating joint surface defects
US20060121087A1 (en) 2004-12-06 2006-06-08 Williams Michael S Polymeric endoprostheses with modified erosion rates and methods of manufacture
EP1819375A2 (en) 2004-12-08 2007-08-22 Interpore Spine Ltd. Continuous phase composite for musculoskeletal repair
US7772352B2 (en) 2005-01-28 2010-08-10 Bezwada Biomedical Llc Bioabsorbable and biocompatible polyurethanes and polyamides for medical devices
AU2006210847A1 (en) 2005-02-01 2006-08-10 Osteobiologics, Inc. Method and device for selective addition of a bioactive agent to a multi-phase implant
US20060177480A1 (en) 2005-02-10 2006-08-10 Hsing-Wen Sung Drug-eluting biodegradable stent
US20060200150A1 (en) * 2005-03-01 2006-09-07 Jouko Ilomaki Bone screw and driver system
CA2603081C (en) 2005-04-04 2013-09-03 Sinexus, Inc. Device and methods for treating paranasal sinus conditions
FI20055194A (en) * 2005-04-27 2006-10-28 Bioretec Oy Bioabsorbent and bioactive composite material and process for manufacturing composite
US7963287B2 (en) 2005-04-28 2011-06-21 Boston Scientific Scimed, Inc. Tissue-treatment methods
CN100400114C (en) 2005-04-30 2008-07-09 中国科学院金属研究所 Biomedicine implant material with controllable degrading rate and its application
US7824433B2 (en) 2005-05-03 2010-11-02 Williams Lytton A Bone anchored surgical mesh
WO2006130796A2 (en) 2005-06-02 2006-12-07 Zimmer Spine, Inc. Interbody fusion ring and method of using the same
US20070014831A1 (en) 2005-07-12 2007-01-18 Hsing-Wen Sung Biodegradable occlusive device with moisture memory
FI122342B (en) 2005-07-18 2011-12-15 Bioretec Oy Bioabsorbable tape system, bioabsorbable tape and method of forming a bioabsorbable tape.
CA2619552A1 (en) 2005-08-18 2007-02-22 Smith & Nephew, Plc Multimodal high strength devices and composites
JP2009504929A (en) 2005-08-18 2009-02-05 スミス アンド ネフュー ピーエルシー High-strength devices and composite materials
US20070048383A1 (en) 2005-08-25 2007-03-01 Helmus Michael N Self-assembled endovascular structures
GB0517499D0 (en) 2005-08-26 2005-10-05 West Hertfordshire Hospitals N Surgical scaffold
US20070050018A1 (en) 2005-09-01 2007-03-01 John Wainwright Biodegradable stents
US20070067043A1 (en) 2005-09-19 2007-03-22 Dericks Gerard H "Cement and bone graft absorbable & implantable detachable sac," a delivery system
JP4499013B2 (en) * 2005-09-30 2010-07-07 トヨタ紡織株式会社 Manufacturing method of wood-based fiber molded body
US20070100449A1 (en) 2005-10-31 2007-05-03 O'neil Michael Injectable soft tissue fixation technique
US7858078B2 (en) 2005-12-06 2010-12-28 Tyco Healthcare Group Lp Bioabsorbable surgical composition
EP1957695B1 (en) 2005-12-07 2011-02-09 Ramot at Tel-Aviv University Ltd. Drug-delivering composite structures
BRPI0620047A2 (en) 2005-12-21 2011-11-01 Synthes Gmbh bone plate set
EP1976460A4 (en) 2006-01-19 2012-06-20 Warsaw Orthopedic Inc Injectable and moldable bone substitute materials
AU2007212501B2 (en) 2006-02-07 2011-03-31 Tepha, Inc. Polymeric, degradable drug-eluting stents and coatings
JP5538881B2 (en) * 2006-04-25 2014-07-02 テレフレックス・メディカル・インコーポレイテッド Calcium phosphate polymer composites and methods
US20070260324A1 (en) 2006-05-05 2007-11-08 Joshi Ashok V Fully or Partially Bioresorbable Orthopedic Implant
FI119177B (en) 2006-05-05 2008-08-29 Bioretec Oy Bioabsorbable, deformable fixation material and implants
JP2007302718A (en) * 2006-05-08 2007-11-22 Osaka Univ Fiber-reinforced composite material
US8221468B2 (en) 2006-05-11 2012-07-17 Gaines Jr Robert W Use of bioabsorbable materials for anterior extradiscal correction of thoracolumbar pathologies
US7914806B2 (en) 2006-06-01 2011-03-29 Boston Scientific Scimed, Inc. Medical devices having improved performance
FI20065385L (en) 2006-06-06 2007-12-27 Bioretec Oy Bone fixation device
US20090171064A1 (en) 2006-06-28 2009-07-02 Gunze Limited Bio-degradable/ absorbable polymer having reduced metal catalyst content, and process for production thereof
FI124017B (en) 2006-06-30 2014-01-31 Stick Tech Oy Curing Fiber Reinforced Composites and Methods for Making Application Oriented Fiber Reinforced Composites
US20080015578A1 (en) 2006-07-12 2008-01-17 Dave Erickson Orthopedic implants comprising bioabsorbable metal
WO2008039476A1 (en) 2006-09-27 2008-04-03 Osman Said G Biologic intramedullary fixation device and methods of use
US8828419B2 (en) 2006-10-06 2014-09-09 Cordis Corporation Bioabsorbable device having encapsulated additives for accelerating degradation
US8394488B2 (en) 2006-10-06 2013-03-12 Cordis Corporation Bioabsorbable device having composite structure for accelerating degradation
US7771476B2 (en) 2006-12-21 2010-08-10 Warsaw Orthopedic Inc. Curable orthopedic implant devices configured to harden after placement in vivo by application of a cure-initiating energy before insertion
US8480718B2 (en) 2006-12-21 2013-07-09 Warsaw Orthopedic, Inc. Curable orthopedic implant devices configured to be hardened after placement in vivo
US8870871B2 (en) 2007-01-17 2014-10-28 University Of Massachusetts Lowell Biodegradable bone plates and bonding systems
US20080206297A1 (en) 2007-02-28 2008-08-28 Roeder Ryan K Porous composite biomaterials and related methods
US20080234762A1 (en) 2007-03-06 2008-09-25 Zimmer Technology, Inc. Self-tapping screw with resorbable tip
CA2681940A1 (en) 2007-03-27 2008-10-02 University Of Southern California Device which enhances the biological activity of locally applied growth factors with particular emphasis on those used for bone repair
AU2008242737B2 (en) 2007-04-19 2013-09-26 Smith & Nephew, Inc. Multi-modal shape memory polymers
ZA200905442B (en) 2007-04-27 2010-10-27 Synthes Gmbh Implant devices constructed with metallic and polymeric components
EP2195361B1 (en) 2007-10-03 2014-11-26 Polynovo Biomaterials Limited High modulus polyurethane and polyurethane/urea compositions
US8323322B2 (en) 2007-10-05 2012-12-04 Zimmer Spine, Inc. Medical implant formed from porous metal and method
FI124190B (en) 2007-12-05 2014-04-30 Bioretec Oy Medical agent and preparation thereof
US8507614B2 (en) 2008-02-07 2013-08-13 Poly-Med, Inc. Multiphasic absorbable compositions of segmented l-lactide copolymers

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
None

Cited By (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9120919B2 (en) 2003-12-23 2015-09-01 Smith & Nephew, Inc. Tunable segmented polyacetal
US9815240B2 (en) 2007-04-18 2017-11-14 Smith & Nephew, Inc. Expansion moulding of shape memory polymers
US9770534B2 (en) 2007-04-19 2017-09-26 Smith & Nephew, Inc. Graft fixation
WO2010122098A2 (en) 2009-04-23 2010-10-28 Vivoxid Oy Biocompatible composite and its use
US10857261B2 (en) 2010-10-20 2020-12-08 206 Ortho, Inc. Implantable polymer for bone and vascular lesions
US11207109B2 (en) 2010-10-20 2021-12-28 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants, and novel composite structures which may be used for medical and non-medical applications
US10028776B2 (en) 2010-10-20 2018-07-24 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants
US10517654B2 (en) 2010-10-20 2019-12-31 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants
US10525169B2 (en) 2010-10-20 2020-01-07 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants, and novel composite structures which may be used for medical and non-medical applications
US10525168B2 (en) 2010-10-20 2020-01-07 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants, and novel composite structures which may be used for medical and non-medical applications
US11850323B2 (en) 2010-10-20 2023-12-26 206 Ortho, Inc. Implantable polymer for bone and vascular lesions
US11484627B2 (en) 2010-10-20 2022-11-01 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants, and novel composite structures which may be used for medical and non-medical applications
US11058796B2 (en) 2010-10-20 2021-07-13 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants, and novel composite structures which may be used for medical and non-medical applications
US11351261B2 (en) 2010-10-20 2022-06-07 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants
US11291483B2 (en) 2010-10-20 2022-04-05 206 Ortho, Inc. Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants
CN102677304A (en) * 2012-05-29 2012-09-19 蔡紫林 Yarn-dyed fabric
CN104857577A (en) * 2015-05-28 2015-08-26 上海益生源药业有限公司 Absorbable bone fixation material and preparation method thereof
US11352491B2 (en) 2016-09-08 2022-06-07 Schaefer Kalk Gmbh & Co. Kg Calcium-salt-containing composite powder having microstructured particles
US11441008B2 (en) 2016-09-08 2022-09-13 Schaefer Kalk Gmbh & Co. Kg Composite powder containing calcium carbonate and having microstructured particles
US11548998B2 (en) 2016-09-08 2023-01-10 Schaefer Kalk Gmbh & Co. Kg Inhibiting calcium carbonate additive
US11760874B2 (en) 2016-09-08 2023-09-19 Schaefer Kalk Gmbh & Co. Kg Composite powder containing calcium carbonate and having microstructured particles having inhibiting calcium carbonate
EP3470097B1 (en) 2017-10-16 2021-03-31 Arctic Biomaterials Oy Orthopedic bioabsorbable implants
US11813007B2 (en) 2017-10-16 2023-11-14 Arctic Biomaterials Oy Orthopedic bioabsorbable implants

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