WO2008130954A2 - Graft fixation - Google Patents
Graft fixation Download PDFInfo
- Publication number
- WO2008130954A2 WO2008130954A2 PCT/US2008/060401 US2008060401W WO2008130954A2 WO 2008130954 A2 WO2008130954 A2 WO 2008130954A2 US 2008060401 W US2008060401 W US 2008060401W WO 2008130954 A2 WO2008130954 A2 WO 2008130954A2
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- anchor
- bone
- hole
- tissue
- shape memory
- Prior art date
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/08—Muscles; Tendons; Ligaments
- A61F2/0811—Fixation devices for tendons or ligaments
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/14—Macromolecular materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00004—(bio)absorbable, (bio)resorbable, resorptive
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00831—Material properties
- A61B2017/00867—Material properties shape memory effect
- A61B2017/00871—Material properties shape memory effect polymeric
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/08—Muscles; Tendons; Ligaments
- A61F2/0811—Fixation devices for tendons or ligaments
- A61F2002/0847—Mode of fixation of anchor to tendon or ligament
- A61F2002/0852—Fixation of a loop or U-turn, e.g. eyelets, anchor having multiple holes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/08—Muscles; Tendons; Ligaments
- A61F2/0811—Fixation devices for tendons or ligaments
- A61F2002/0847—Mode of fixation of anchor to tendon or ligament
- A61F2002/0858—Fixation of tendon or ligament between anchor and bone, e.g. interference screws, wedges
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/08—Muscles; Tendons; Ligaments
- A61F2/0811—Fixation devices for tendons or ligaments
- A61F2002/0847—Mode of fixation of anchor to tendon or ligament
- A61F2002/0864—Fixation of tendon or ligament between anchor elements, e.g. by additional screws in the anchor, anchor crimped around tendon
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/08—Muscles; Tendons; Ligaments
- A61F2/0811—Fixation devices for tendons or ligaments
- A61F2002/0876—Position of anchor in respect to the bone
- A61F2002/0888—Anchor in or on a blind hole or on the bone surface without formation of a tunnel
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2210/0014—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2400/00—Materials characterised by their function or physical properties
- A61L2400/16—Materials with shape-memory or superelastic properties
Definitions
- the present disclosure relates generally to tissue graft fixation and, more particularly, to tissue graft fixation via the use of shape memory polymer material.
- a ligament such as an anterior cruciate ligament (ACL) that has ruptured and is non-repairable, is generally replaced arthroscopically by a tissue graft
- the tissue graft may be harvested from a portion of a patellar tendon having so called “bone blocks" at each end, and from the semitendonosis and gracilis.
- the tissue graft can be formed from synthetic materials or from a combination of synthetic and natural materials.
- the replacement tissue graft is implanted by securing one end of the tissue graft in a socket formed in a 1 passage within the femur, and passing the other end of the graft through a passage formed in the tibia.
- sutures are used to affix each end of the tissue graft to a fastener (e.g., an interference screw or a post), which is then secured to the bone.
- a fastener such as an interference screw
- a fastener may create complications for several reasons; the possibility of the screw threads damaging the grafts during screw installation if the screw is too big in relation to the graft and/or if the space between the passage and the grafts is too small, the graft rotating with the screw during screw installation so that the optimal position of the grafts is lost and/or the grafts are damaged, divergence of i the grafts and/or screw occurring, the requirement of a range of fastener sizes for different patients, and, if the screw is non-metal, the possibility of the screw breaking during insertion.
- the present disclosure relates to an anchor for fixating a tissue graft to bone.
- the anchor includes a through hole extending an entire length of the anchor.
- the anchor includes a polymer composition including shape memory qualities,
- the through hole is circular, star-shaped, or rectangular.
- the anchor further includes a component disposed within the through hole of the anchor, wherein the component includes a polymer composition having shape memory qualities.
- the through hole is divided into two sections. In a further embodiment, the through hole is divided into four sections.
- the present disclosure relates to an anchor for fixating a tissue graft to bone.
- the anchor includes a first groove extending an entire length of the anchor and a second groove extending an entire length of the anchor.
- the anchor includes a polymer composition having shape memory qualities.
- the first groove and the second groove both include barbs.
- the present disclosure relates to an anchor for fixating a tissue graft to bone.
- the anchor includes a cross-section in a shape of a cross and a polymer composition including shape memory qualities,
- the present disclosure relates to an anchor for fixating a tissue graft to bone.
- the anchor includes a body having a curved top portion, a curved bottom portion, and two sides located between the top portion and the bottom portion. In an embodiment, the sides are curved inward toward the body of the anchor.
- the present disclosure relates to a method of fixating a tissue graft to bone. The method includes providing an anchor having a through hole extending an entire length of the anchor.
- the anchor includes a polymer composition having shape memory qualities; inserting an end of a tissue graft into the through hole; inserting the anchor into a bone tunnel; providing the anchor with energy to deform the anchor and fixate the graft within the bone tunnel,
- the method further includes a component disposed within the through hole, the component including a polymer composition having shape memory qualities.
- the through hole is divided into two sections, wherein the method further includes inserting ends of a tissue graft into the sections.
- the through hole is divided into the four sections, wherein the method further includes inserting ends of multiple tissue grafts into the sections,
- the present disclosure relates to a method of fixating tissue grafts to bone.
- the method includes providing at least two tissue grafts; coupling the at least two tissue grafts; inserting the at least two tissue grafts into a bone tunnel; inserting an anchor into the bone tunnel such that the anchor is located between the at least two tissue grafts; and providing energy to the anchor to deform the anchor and fixate the at least two tissue grafts within the bone tunnel.
- Figs. IA and IB show a cross-sectional view of an end of a tissue graft disposed within an anchor of a first embodiment of the present disclosure both before and after deformation of the anchor.
- FIGs. 2A and 2B show cross-sectional views of an anchor of a second embodiment of the present disclosure before and after deformation of the anchor.
- FIGs. 2 C and 2D show cross-sectional views of an anchor of a third embodiment of the present disclosure before and after deformation of the anchor.
- Figs. 2E and 2F show cross-sectional views of an anchor of a fourth embodiment of the present disclosure before and after deformation of the anchor.
- Figs. 3A and 3B show cross-sectional views of an end of a tissue graft disposed within an anchor of a fifth embodiment of the present disclosure before and after deformation of the anchor.
- Figs. 4A and 4B show cross-sectional views of an anchor of a sixth embodiment of the present disclosure before and after deformation of the anchor.
- Figs. 5A and 5B show cross-sectional views of an anchor of a seventh embodiment of the present disclosure before and after deformation of the anchor.
- Figs, GA and 6B show cross-sectional views of an anchor of an eighth embodiment of the present disclosure before and after deformation of the anchor.
- Figs. 7A and 7B show cross-sectional views of a bone tunnel having surface features on walls of the tunnel .
- FIG. 8A shows a side view of an anchor of a ninth embodiment of the present disclosure
- Fig. 8B shows a cross-sectional view of the anchor of Fig. 8A.
- Fig. 8C shows a front view of the anchor of Fig. 8A.
- Fig. 9 shows a cross-sectional view of the anchor of Fig. 8 A in a bone tunnel and after deformation of the anchor.
- Fig. 10 shows mechanical testing data for the anchor of the present disclosure.
- Figs. 1 IA and 11 B show a method of fixating tissue grafts within a bone tunnel using an anchor of the present disclosure.
- Figs. IA and IB show cross-sectional views of a cylindrical anchor 10 with a central through hole H into which an end 12a of a tissue graft 12 is placed.
- the anchor 10 is then loosely press fit into a pre-formed passage 13a in bone 13, such as a femoral passage in a femur, as described above.
- the anchor 10 expands radially and shrinks axially, as shown by arrows in Fig. IB, thereby fixating the tissue graft 12 and anchor 10 to the bone 13.
- the through holes 11 include those shaped as a star (Fig. 2A), a slot (Fig. 2C), and a toothed slot (Fig. 2E).
- Figs. 2B, 2D, and 2F show the anchors 10 of Figs. 2A, 2C, and 2E, respectively, after the anchors 10 are provided with energy.
- Other shapes for the through holes 11 are also within the scope of this disclosure. It is believed that having a through hole with the shapes shown in Figs. 2A, 2C, and 2E would increase the fixation of the graft to the anchor due to an increase in the amount of surface area and points of contact engaging the graft.
- the number of holes 11 in the anchor 10 may vary.
- the anchor comprises polymeric shape memory material.
- Shape memory polymers which can be resorbable or non-resorbable, are known in the art and any biocompatible polymeric shape memory material can be used in the context of the present disclosure. Specific polymers that may be used include polyetheretherketone (PEEK), polymethyl methacrylate (PMMA), polyethyl methacrylate (PEMA), polyacrylate, poly- alpha-hydroxy acids, polycapro lactones, polydioxanones, polyesters, polyglycolic acid, polyglycols, polylactides, polyorthoesters, polyphosphates, polyoxaesters, polyphosphoesters, polyphosphonates, polysaccharides, polytyrosine carbonates, polyurethanes, and copolymers or polymer blends thereof.
- PEEK polyetheretherketone
- PMMA polymethyl methacrylate
- PEMA polyethyl methacrylate
- polyacrylate poly- alpha-hydroxy acids
- the anchor 10 may be formed by a process that would provide the anchor 10 with shape memory properties, such as, without limitation, zone drawing, hydrostatic extrusion, die drawing, compression flow molding, thermoforming, rolling, and roll drawing.
- the through hole 11 may be formed in the anchor 10 while it is being manufactured. Alternatively, the through hole 11 may be formed in the anchor 10 post processing by drilling or by any other method of forming the through hole 11.
- polymers that display shape memory qualities show a large change in modulus of elasticity at the glass transition temperature (T g ).
- the shape-memory function can be achieved by taking advantage of this characteristic. Namely, a molded article (primary molded article) to which a definite shape (the original shape) has been imparted by a common method for molding plastics, is softened by providing the article with energy and heating to a temperature (T f ) higher than the T 8 of the polymer, but lower than the melting temperature (T ra ) thereof so as to deform it into a different shape.
- the molded article is cooled to a temperature lower than the T g , while maintaining the thus deformed shape (secondary molded article), When it is heated again to a temperature higher than the secondary molding temperature T f , but lower than the T m , the shape of the secondary molded article disappears and thus the article is recovered to the original shape of the primary molded article.
- a molded article i.e. the above- mentioned anchor
- a definite shape original shape
- T m melting temperature
- the glass transition temperature of the polymer material will vary based on a variety of factors, such as molecular weight, composition, structure of the polymer, and other factors known to one of ordinary skill in the art.
- Examples of adding energy to the polymer material include electrical and thermal energy sources, the use of force, or mechanical energy, and/or a solvent.
- Examples of thermal energy sources include a heated liquid, such as water or saline. It is also within the scope of this disclosure that once the anchor 10 is placed in the bone, body heat would be transferred from blood and tissue, via thermal conduction, to provide the energy necessary to deform the shape memory polymer material. In this instance, body temperature would be used as the thermal energy source.
- Examples of electrical energy sources include heat generating devices such as a cauterizing device or insulated conductor, as more fully described in PCT Application No. PCT/US2008/056828, the disclosure of which is incorporated herein by reference in its entirety, or a heating probe, as more fully described in PCT Application No. PCT/US2008/056836, the disclosure of which is incorporated herein by reference in its entirety.
- the anchor 10 may include a hole in the body of the anchor 10 that a heating device, such as the heating probe described above, may be inserted into.
- Any suitable force that can be applied either preoperatively or intra- operatively can be used as a form of energy.
- One example includes the use of ultra sonic devices, which can relax the polymer material with minimal heat generation.
- Solvents that could be used as the form of energy include organic-based solvents and aqueous-based solvents, including body fluids. Care should be taken that the selected solvent is not contra indicated for the patient, particularly when the solvent is used intra-operatively. The choice of solvents will also be selected based upon the material to be relaxed. Examples of solvents that can be used to relax the polymer material include alcohols, glycols, glycol ethers, oils, fatty acids, acetates, acetylenes, ketones, aromatic hydrocarbon solvents, and chlorinated solvents,
- the anchor 20 includes a through hole 21 and a component 22 disposed within the through hole 21.
- Multiple grafts 23 can be placed into the through hole 21 along with the component 22, which, as shown in Fig. 3B, decreases in length and increases in diameter, similar to anchor 20, thereby providing further fixation of the grafts 23 to anchor 20 and therefore the bone 24,
- the anchor 20 and component 22 may be formed by a process that would provide the anchor 20 and component 22 with shape memory properties, such as, without limitation, zone drawing, hydrostatic extrusion, die drawing, compression flow molding, thermoforming, rolling, and roll drawing,
- the through hole 21 may be formed in the anchor 20 while it is being manufactured. Alternatively, the through hole 21 may be formed in the anchor 20 post processing by drilling or by any other method of forming the through hole 21.
- FIG. 4A-4B shows a through hole 31 that is divided into four separate openings 31a-31d allowing the possibility of up to four tissue graft ends being fixated to the anchor 30 when the anchor 30 is provided with energy, as shown in Fig. 4B.
- Figs. 5A-5B show an anchor 40 having two grooves 41, both of which may extend the entire length of the anchor 40 or a partial length. Surfaces 41a of the grooves 41 include features, such as barbs 41a', which may allow further fixation of the anchor 40 to the graft upon providing the anchor 40 with energy, as shown in Fig. 5B.
- anchor 50 in the shape of a cross. Similar to the anchor 30 of Figs. 4A-4B, anchor 50 allows for the possibility of four tissue graft ends being fixated to the anchor 50 when the anchor 50 is provided with energy, as shown in Fig. 6B.
- the anchors 40,50 of Figs. 5A and 6A expand to cause an interference fit against walls 42a,52a of the bone tunnels 42,52, thereby not only fixating the anchors 40,50 to the walls 42a,52a, but also fixating tissue graft ends to the bone 43,53, which allow direct osseointegration of the graft to the walls 42a,52a.
- the anchors 30, 40, 50 may be formed by a process that would provide the anchors 30, 40, 50 with shape memory properties, such as, without limitation, zone drawing, hydrostatic extrusion, die drawing, compression flow molding, thermoforming, rolling, and roll drawing.
- the through hole 31, openings 31a-31d, grooves 41, and barbs 41a' may be formed in the anchors 30, 40 while it is being manufactured. Alternatively, these features may be formed in the anchors 30,40 post processing by drilling or by any other method.
- the walls 61a may include surface features 62, such as barbs and/or spikes, which would allow more integration of the anchor 60 into the bone 63 upon providing the anchor 60 with energy, thereby increasing fixation of the anchor 60, and therefore a graft, to the bone 63.
- the surface features 62 may be made via the use of a mechanical tool or other devices known to one of skill in the art for making the features 62.
- an anchor 70 has been shaped to aid insertion into a bone tunnel containing ligaments or bone block, as will be further described below.
- the anchor 70 includes substantially rounded top and bottom portions 71,72 and two sides 73,74, located between the top and bottom portions 71,72, both of which are configured to house graft ends when the plug is disposed within a bone tunnel, as will be further described below.
- the anchor 70 also includes a tapered front portion 75, an angled back portion 76, and an opening 77 that partially extends a length of the anchor 70.
- the opening 77 is configured for engagement with a delivery device for delivery of the anchor 70 into a bone tunnel, as will be further described below.
- the anchor 70 is inserted into a bone tunnel 78, via the use of a delivery device, as mentioned above, such that the graft ends 79 extend along the sides 73,74 of the anchor 70.
- the anchor 70 is then provided with energy, via the use of one of the heating devices described above, by inserting the heating device into the opening 77 and activating it, thereby resulting in the anchor 70 expanding to compress the graft ends 79 against the bone tunnel wall 78a and fixate the plug 70 and the graft ends 79 within the bone tunnel 78.
- Other energy sources may also be used.
- the anchor 70 may be of various sizes to accommodate the size of the bone tunnel 78 and substantially increase the possibility of engagement of the anchor 70 and the graft ends 79 with the wall 78a upon deformation of the anchor 70.
- the anchor 70 may be formed by a process that would provide the anchor 70 with shape memory properties, such as, without limitation, zone drawing, hydrostatic extrusion, die drawing, compression flow molding, thermoforming, rolling, and roll drawing.
- the anchor 70 is processed via one of the methods described above and subsequently machined to include the shape of the sides 73,74 and the top and bottom portions 71,72.
- the opening 77 may be formed in the anchor 70 while it is being manufactured.
- the opening 71 may be formed in the anchor 70 post processing by drilling or by any other method of forming the opening 71.
- the plug was relaxed by immersion of the block, plug, and rope into hot water (approximately 8O 0 C for 5 min).
- the block containing the plug and rope had cooled to room temperature, it was inserted into an aluminum sleeve having similar dimensions to the sawbone block.
- Mechanical testing was carried out using an Instron 5566 with a 1OkN load cell. The aluminum sleeve housing the sawbone block was clamped in a first grip of the Instron and the nylon loops were clamped in a second grip, specifically, the loops were clamped to the crosshead of the Instron. The crosshead was extended until the loops were taut, which, as shown in Fig.
- FIG. HA and 1 IB A further embodiment is shown in Figs. HA and 1 IB.
- the ends 80a may be coupled at one point via a biocompatible connector 200 including, without limitation, a suture, a clip, or staple.
- the grafts 80 are placed into a previously drilled bone tunnel 100 and an anchor 90 is then inserted between the grafts 80 and deformed by providing the anchor 90 with energy, as shown in Fig. HB, to fixate the grafts 80 within the tunnel 100.
- the anchor 90 may be formed by a process that would provide the anchor 90 with shape memory properties, such as, without limitation, zone drawing, hydrostatic extrusion, die drawing, compression flow molding, thermofqrming, rolling, and roll drawing.
- the anchors described above may include a reinforced polymeric material.
- the reinforced polymeric material comprises a composite or matrix including reinforcing material or phases such as fibers, rods, platelets, and fillers.
- the polymeric material can include glass fibers, carbon fibers, polymeric fibers, ceramic fibers, or ceramic particulates. Other reinforcing material or phases known to one of ordinary skill in the art could also be used.
- One or more material from which the anchor is formed may be porous. Porosity can allow infiltration by cells from surrounding tissues, enhancing integration of the device by processes such as osseointegration.
- one or more actives/agents may be incorporated into the material of the anchor.
- Suitable actives/agents include bone morphogenic proteins, antibiotics, antiinflammatories, angiogenic factors, osteogenic factors, monobutyrin, thrombin, modified proteins, platelet rich plasma/solution, platelet poor plasma/solution, bone marrow aspirate, and any cells sourced from flora or fauna, such as living cells, preserved cells, dormant cells, and dead cells.
- the active agent is incorporated into the polymeric shape memory material, to be released during the relaxation or degradation of the polymer material.
- the incorporation of an active agent can act to combat infection at the site of implantation and/or to promote new tissue growth.
- the anchor described above may also include at least one feature, such as protrusions, that are coupled to a surface of the anchor via a variety of methods, such as an interference fit between the polymer and the protrusions, adhesion of the protrusion to the polymer, or any other method known to one of ordinary skill in the art.
- the number of protrusions present on the surface of the anchor may vary.
- the protrusions may provide multiple contact points to increase the friction between the anchor and the bone, thereby providing increased fixation between the tissue graft and the bone.
- the protrusions may be selected from a group that includes a metal material, a non-metal material, a polymer material, and combinations thereof and may be of any shape or size. If a polymer material is used for the protrusions, the polymer material may include a resorbable or non- resorbable polymer material.
- the particulate material may include a ceramic material, a crystalline polymer, or any other type of material that would provide the polymer material with multiple contact points to increase the friction between the polymer material and the bone,
- the anchors described above, and especially anchors 10,20 may be biaxially oriented to have an internal diameter that decreases and an external diameter that increases when the anchor is provided with energy. This allows for the internal diameter to further grip the anchor to the tissue graft(s) and the outer diameter to engage the surrounding bone, thereby locking the tissue graft(s) in place.
- a rod of shape memory polymer material may be die drawn over a mandrel. Further discussion of this process can be found in United States Patent Application Serial Number 60/912,740, the disclosure of which is incorporated herein by reference in its entirety,
- the shape memory anchors of the present disclosure may substantially reduce the need to thread/pre-tap the bone tunnel before insertion of the anchor into the bone tunnel, especially when a patellar tendon is used as the tissue graft. In addition, it is believed that the anchor would offer improved fixation over existing systems. Furthermore, the anchors may substantially reduce the possibility of making a range of fasteners to fit the patient, thereby possibly offering a 'one size fits all' approach.
Abstract
The present disclosure relates to an anchor for fixating a tissue graft to bone. The anchor includes a through hole extending an entire length of the anchor and a polymer composition having shape memory qualities. Other anchors and methods for fixating a tissue graft to bone are also disclosed.
Description
GRAFT FIXATION Cross-Reference to Related Applications
[0001] This application is a PCT International Application of United States Patent Application No, 60/912,828 filed on April 19, 2007, the disclosure of which is incorporated by reference in its entirety.
Background L Field of the Invention
[0002] The present disclosure relates generally to tissue graft fixation and, more particularly, to tissue graft fixation via the use of shape memory polymer material. 2. RelatedArt
[0003] A ligament, such as an anterior cruciate ligament (ACL), that has ruptured and is non-repairable, is generally replaced arthroscopically by a tissue graft, The tissue graft may be harvested from a portion of a patellar tendon having so called "bone blocks" at each end, and from the semitendonosis and gracilis. Alternatively, the tissue graft can be formed from synthetic materials or from a combination of synthetic and natural materials.
[0004] The replacement tissue graft is implanted by securing one end of the tissue graft in a socket formed in a1 passage within the femur, and passing the other end of the graft through a passage formed in the tibia. Generally, sutures are used to affix each end of the tissue graft to a fastener (e.g., an interference screw or a post), which is then secured to the bone. The use of a fastener, such as an interference screw, may create complications for several reasons; the possibility of the screw threads damaging the grafts during screw installation if the screw is too big in relation to the graft and/or if the space between the passage and the grafts is too small, the graft rotating with the screw during screw installation so that the optimal position of the grafts is lost and/or the grafts are damaged, divergence of i
the grafts and/or screw occurring, the requirement of a range of fastener sizes for different patients, and, if the screw is non-metal, the possibility of the screw breaking during insertion.
Summary [0005] In one aspect, the present disclosure relates to an anchor for fixating a tissue graft to bone. The anchor includes a through hole extending an entire length of the anchor. The anchor includes a polymer composition including shape memory qualities, In an embodiment, the through hole is circular, star-shaped, or rectangular. In another embodiment, the anchor further includes a component disposed within the through hole of the anchor, wherein the component includes a polymer composition having shape memory qualities. In yet another embodiment, the through hole is divided into two sections. In a further embodiment, the through hole is divided into four sections.
[0006] In another aspect, the present disclosure relates to an anchor for fixating a tissue graft to bone. The anchor includes a first groove extending an entire length of the anchor and a second groove extending an entire length of the anchor. The anchor includes a polymer composition having shape memory qualities. In an embodiment, the first groove and the second groove both include barbs.
[0007] In yet another aspect, the present disclosure relates to an anchor for fixating a tissue graft to bone. The anchor includes a cross-section in a shape of a cross and a polymer composition including shape memory qualities,
[0008] In a further embodiment, the present disclosure relates to an anchor for fixating a tissue graft to bone. The anchor includes a body having a curved top portion, a curved bottom portion, and two sides located between the top portion and the bottom portion. In an embodiment, the sides are curved inward toward the body of the anchor.
[0009] In yet a further embodiment, the present disclosure relates to a method of fixating a tissue graft to bone. The method includes providing an anchor having a through hole extending an entire length of the anchor. The anchor includes a polymer composition having shape memory qualities; inserting an end of a tissue graft into the through hole; inserting the anchor into a bone tunnel; providing the anchor with energy to deform the anchor and fixate the graft within the bone tunnel,
[0010] In an embodiment, the method further includes a component disposed within the through hole, the component including a polymer composition having shape memory qualities. In another embodiment, the through hole is divided into two sections, wherein the method further includes inserting ends of a tissue graft into the sections. In yet another embodiment, the through hole is divided into the four sections, wherein the method further includes inserting ends of multiple tissue grafts into the sections,
[0011] In an embodiment, the present disclosure relates to a method of fixating tissue grafts to bone. The method includes providing at least two tissue grafts; coupling the at least two tissue grafts; inserting the at least two tissue grafts into a bone tunnel; inserting an anchor into the bone tunnel such that the anchor is located between the at least two tissue grafts; and providing energy to the anchor to deform the anchor and fixate the at least two tissue grafts within the bone tunnel.
[0012] Further features, aspects, and advantages of the present disclosure, as well as the structure and operation of various embodiments of the present disclosure, are described in detail below with reference to the accompanying drawings.
Brief Description of the Drawings
[0013] The accompanying drawings, which are incorporated in and form a part of the specification, illustrate the embodiments of the present disclosure and together with the description, serve to explain the principles of the disclosure. In the drawings:
[0014] Figs. IA and IB show a cross-sectional view of an end of a tissue graft disposed within an anchor of a first embodiment of the present disclosure both before and after deformation of the anchor.
[0015] Figs. 2A and 2B show cross-sectional views of an anchor of a second embodiment of the present disclosure before and after deformation of the anchor.
[0016] Figs. 2 C and 2D show cross-sectional views of an anchor of a third embodiment of the present disclosure before and after deformation of the anchor.
[0017] Figs. 2E and 2F show cross-sectional views of an anchor of a fourth embodiment of the present disclosure before and after deformation of the anchor. [0018] Figs. 3A and 3B show cross-sectional views of an end of a tissue graft disposed within an anchor of a fifth embodiment of the present disclosure before and after deformation of the anchor.
[0019] Figs. 4A and 4B show cross-sectional views of an anchor of a sixth embodiment of the present disclosure before and after deformation of the anchor. [0020] Figs. 5A and 5B show cross-sectional views of an anchor of a seventh embodiment of the present disclosure before and after deformation of the anchor.
[0021] Figs, GA and 6B show cross-sectional views of an anchor of an eighth embodiment of the present disclosure before and after deformation of the anchor.
[0022] Figs. 7A and 7B show cross-sectional views of a bone tunnel having surface features on walls of the tunnel .
[0023] Fig. 8A shows a side view of an anchor of a ninth embodiment of the present disclosure
[0024] Fig. 8B shows a cross-sectional view of the anchor of Fig. 8A.
[0025] Fig. 8C shows a front view of the anchor of Fig. 8A.
[0026] Fig. 9 shows a cross-sectional view of the anchor of Fig. 8 A in a bone tunnel and after deformation of the anchor.
[0027] Fig. 10 shows mechanical testing data for the anchor of the present disclosure. [0028] Figs. 1 IA and 11 B show a method of fixating tissue grafts within a bone tunnel using an anchor of the present disclosure.
Detailed Description of the Embodiments
[0029] Figs. IA and IB show cross-sectional views of a cylindrical anchor 10 with a central through hole H into which an end 12a of a tissue graft 12 is placed. The anchor 10 is then loosely press fit into a pre-formed passage 13a in bone 13, such as a femoral passage in a femur, as described above. Upon providing the anchor 10 with energy, the anchor 10 expands radially and shrinks axially, as shown by arrows in Fig. IB, thereby fixating the tissue graft 12 and anchor 10 to the bone 13.
[0030] Alternative embodiments of the anchor 10 include those shown in Figs. 2A,
2C, and 2E, which are similar to the anchor described above except that the through holes 11 include those shaped as a star (Fig. 2A), a slot (Fig. 2C), and a toothed slot (Fig. 2E).
Figs. 2B, 2D, and 2F show the anchors 10 of Figs. 2A, 2C, and 2E, respectively, after the anchors 10 are provided with energy. Other shapes for the through holes 11 are also within the scope of this disclosure. It is believed that having a through hole with the shapes shown in Figs. 2A, 2C, and 2E would increase the fixation of the graft to the anchor due to an increase in the amount of surface area and points of contact engaging the graft. The number of holes 11 in the anchor 10 may vary.
[0031] The anchor comprises polymeric shape memory material. Shape memory polymers, which can be resorbable or non-resorbable, are known in the art and any biocompatible polymeric shape memory material can be used in the context of the present disclosure. Specific polymers that may be used include polyetheretherketone (PEEK),
polymethyl methacrylate (PMMA), polyethyl methacrylate (PEMA), polyacrylate, poly- alpha-hydroxy acids, polycapro lactones, polydioxanones, polyesters, polyglycolic acid, polyglycols, polylactides, polyorthoesters, polyphosphates, polyoxaesters, polyphosphoesters, polyphosphonates, polysaccharides, polytyrosine carbonates, polyurethanes, and copolymers or polymer blends thereof.
[0032] The anchor 10 may be formed by a process that would provide the anchor 10 with shape memory properties, such as, without limitation, zone drawing, hydrostatic extrusion, die drawing, compression flow molding, thermoforming, rolling, and roll drawing. The through hole 11 may be formed in the anchor 10 while it is being manufactured. Alternatively, the through hole 11 may be formed in the anchor 10 post processing by drilling or by any other method of forming the through hole 11.
[0033] Generally, polymers that display shape memory qualities show a large change in modulus of elasticity at the glass transition temperature (Tg). The shape-memory function can be achieved by taking advantage of this characteristic. Namely, a molded article (primary molded article) to which a definite shape (the original shape) has been imparted by a common method for molding plastics, is softened by providing the article with energy and heating to a temperature (Tf) higher than the T8 of the polymer, but lower than the melting temperature (Tra) thereof so as to deform it into a different shape. Next, the molded article is cooled to a temperature lower than the Tg, while maintaining the thus deformed shape (secondary molded article), When it is heated again to a temperature higher than the secondary molding temperature Tf, but lower than the Tm, the shape of the secondary molded article disappears and thus the article is recovered to the original shape of the primary molded article.
[0034] For the purposes of this disclosure, a molded article (i.e. the above- mentioned anchor), having a definite shape (original shape) is formed from polymer
material and is provided with energy to heat the article to a temperature above the glass transition temperature of the polymer, but lower than the melting temperature (Tm) thereof so as to deform it into a different shape and effectively wedge the article between the tissue graft and the bone. In this manner, the tissue graft becomes fixed to the bone. However, for the purposes of this disclosure, rather than cooling the anchor and heating it again until it recovers its original shape, the anchor is kept in this deformed shape so as to maintain fixation of the tissue graft to the bone. The glass transition temperature of the polymer material will vary based on a variety of factors, such as molecular weight, composition, structure of the polymer, and other factors known to one of ordinary skill in the art. [0035] Examples of adding energy to the polymer material include electrical and thermal energy sources, the use of force, or mechanical energy, and/or a solvent. Examples of thermal energy sources include a heated liquid, such as water or saline. It is also within the scope of this disclosure that once the anchor 10 is placed in the bone, body heat would be transferred from blood and tissue, via thermal conduction, to provide the energy necessary to deform the shape memory polymer material. In this instance, body temperature would be used as the thermal energy source. Examples of electrical energy sources include heat generating devices such as a cauterizing device or insulated conductor, as more fully described in PCT Application No. PCT/US2008/056828, the disclosure of which is incorporated herein by reference in its entirety, or a heating probe, as more fully described in PCT Application No. PCT/US2008/056836, the disclosure of which is incorporated herein by reference in its entirety. For instance, the anchor 10 may include a hole in the body of the anchor 10 that a heating device, such as the heating probe described above, may be inserted into.
[0036] Any suitable force that can be applied either preoperatively or intra- operatively can be used as a form of energy. One example includes the use of ultra sonic
devices, which can relax the polymer material with minimal heat generation. Solvents that could be used as the form of energy include organic-based solvents and aqueous-based solvents, including body fluids. Care should be taken that the selected solvent is not contra indicated for the patient, particularly when the solvent is used intra-operatively. The choice of solvents will also be selected based upon the material to be relaxed. Examples of solvents that can be used to relax the polymer material include alcohols, glycols, glycol ethers, oils, fatty acids, acetates, acetylenes, ketones, aromatic hydrocarbon solvents, and chlorinated solvents,
[0037] A further embodiment of the anchor is shown in Figs. 3A and 3B. The anchor 20 includes a through hole 21 and a component 22 disposed within the through hole 21. Multiple grafts 23 can be placed into the through hole 21 along with the component 22, which, as shown in Fig. 3B, decreases in length and increases in diameter, similar to anchor 20, thereby providing further fixation of the grafts 23 to anchor 20 and therefore the bone 24, The anchor 20 and component 22 may be formed by a process that would provide the anchor 20 and component 22 with shape memory properties, such as, without limitation, zone drawing, hydrostatic extrusion, die drawing, compression flow molding, thermoforming, rolling, and roll drawing, The through hole 21 may be formed in the anchor 20 while it is being manufactured. Alternatively, the through hole 21 may be formed in the anchor 20 post processing by drilling or by any other method of forming the through hole 21.
[0038] Another embodiment is shown in Figs. 4A-4B, 5A-5B, and 6A-6B. The anchor 30 of Fig. 4A includes a through hole 31 that is divided into four separate openings 31a-31d allowing the possibility of up to four tissue graft ends being fixated to the anchor 30 when the anchor 30 is provided with energy, as shown in Fig. 4B. Figs. 5A-5B show an anchor 40 having two grooves 41, both of which may extend the entire length of the anchor
40 or a partial length. Surfaces 41a of the grooves 41 include features, such as barbs 41a', which may allow further fixation of the anchor 40 to the graft upon providing the anchor 40 with energy, as shown in Fig. 5B. Figs. 6A-6B show an anchor 50 in the shape of a cross. Similar to the anchor 30 of Figs. 4A-4B, anchor 50 allows for the possibility of four tissue graft ends being fixated to the anchor 50 when the anchor 50 is provided with energy, as shown in Fig. 6B.
[0039] The anchors 40,50 of Figs. 5A and 6A expand to cause an interference fit against walls 42a,52a of the bone tunnels 42,52, thereby not only fixating the anchors 40,50 to the walls 42a,52a, but also fixating tissue graft ends to the bone 43,53, which allow direct osseointegration of the graft to the walls 42a,52a. The anchors 30, 40, 50 may be formed by a process that would provide the anchors 30, 40, 50 with shape memory properties, such as, without limitation, zone drawing, hydrostatic extrusion, die drawing, compression flow molding, thermoforming, rolling, and roll drawing. The through hole 31, openings 31a-31d, grooves 41, and barbs 41a' may be formed in the anchors 30, 40 while it is being manufactured. Alternatively, these features may be formed in the anchors 30,40 post processing by drilling or by any other method.
[0040] As shown in Figs. 7A and 7B, the walls 61a may include surface features 62, such as barbs and/or spikes, which would allow more integration of the anchor 60 into the bone 63 upon providing the anchor 60 with energy, thereby increasing fixation of the anchor 60, and therefore a graft, to the bone 63. The surface features 62 may be made via the use of a mechanical tool or other devices known to one of skill in the art for making the features 62.
[0041] In an embodiment shown in Figs. 8A-8C, an anchor 70 has been shaped to aid insertion into a bone tunnel containing ligaments or bone block, as will be further described below. The anchor 70 includes substantially rounded top and bottom portions
71,72 and two sides 73,74, located between the top and bottom portions 71,72, both of which are configured to house graft ends when the plug is disposed within a bone tunnel, as will be further described below. The anchor 70 also includes a tapered front portion 75, an angled back portion 76, and an opening 77 that partially extends a length of the anchor 70. The opening 77 is configured for engagement with a delivery device for delivery of the anchor 70 into a bone tunnel, as will be further described below.
[0042] In use, as shown in Fig. 9, the anchor 70 is inserted into a bone tunnel 78, via the use of a delivery device, as mentioned above, such that the graft ends 79 extend along the sides 73,74 of the anchor 70. The anchor 70 is then provided with energy, via the use of one of the heating devices described above, by inserting the heating device into the opening 77 and activating it, thereby resulting in the anchor 70 expanding to compress the graft ends 79 against the bone tunnel wall 78a and fixate the plug 70 and the graft ends 79 within the bone tunnel 78. Other energy sources may also be used. The anchor 70 may be of various sizes to accommodate the size of the bone tunnel 78 and substantially increase the possibility of engagement of the anchor 70 and the graft ends 79 with the wall 78a upon deformation of the anchor 70.
[0043] The anchor 70 may be formed by a process that would provide the anchor 70 with shape memory properties, such as, without limitation, zone drawing, hydrostatic extrusion, die drawing, compression flow molding, thermoforming, rolling, and roll drawing. Alternatively, the anchor 70 is processed via one of the methods described above and subsequently machined to include the shape of the sides 73,74 and the top and bottom portions 71,72. The opening 77 may be formed in the anchor 70 while it is being manufactured. Alternatively, the opening 71 may be formed in the anchor 70 post processing by drilling or by any other method of forming the opening 71.
EXAMPLE
[0044] An 8.5mm hole was drilled through the centre of a block of 20 pcf sawbone having the following dimensions: 42 mm long, 31mm wide, and 31 mm thick.
[0045] Two pieces of 7 inch long 125 Ib braided nylon rope were doubled over and inserted into the hole so that the four ends of rope passed all the way through the hole in the sawbone. An anchor including Poly (D3L lactide-co-glycolide) and calcium carbonate was inserted into the hole ensuring that the strands of nylon rope passing through the hole did not cross over one another and each of the four ends of nylon had its own quadrant of the hole. The anchor was processed via a die drawing process to include shape memory qualities. The ratio of lactide : glyco lide was 85:15 and the calcium carbonate was present at between about 35.5% by weight of the polymer composition. Once in place, the plug was relaxed by immersion of the block, plug, and rope into hot water (approximately 8O0C for 5 min). When the block containing the plug and rope had cooled to room temperature, it was inserted into an aluminum sleeve having similar dimensions to the sawbone block. [0046] Mechanical testing was carried out using an Instron 5566 with a 1OkN load cell. The aluminum sleeve housing the sawbone block was clamped in a first grip of the Instron and the nylon loops were clamped in a second grip, specifically, the loops were clamped to the crosshead of the Instron. The crosshead was extended until the loops were taut, which, as shown in Fig. 10, occurred when the crosshead was extended 21 mm, and then testing began. Testing was carried out with a crosshead speed of 25 mm/min and a preload of 22.3N. As shown in Fig. 10, the plug was found to have a maximum fixation strength of 532 N.
[0047] A further embodiment is shown in Figs. HA and 1 IB. In order to substantially reduce the graft ends 80a from slipping between an anchor 90 and the bone tunnel wall 100a, the ends 80a may be coupled at one point via a biocompatible connector
200 including, without limitation, a suture, a clip, or staple. The grafts 80 are placed into a previously drilled bone tunnel 100 and an anchor 90 is then inserted between the grafts 80 and deformed by providing the anchor 90 with energy, as shown in Fig. HB, to fixate the grafts 80 within the tunnel 100. [0048] The anchor 90 may be formed by a process that would provide the anchor 90 with shape memory properties, such as, without limitation, zone drawing, hydrostatic extrusion, die drawing, compression flow molding, thermofqrming, rolling, and roll drawing.
[0049] The anchors described above may include a reinforced polymeric material. Preferably, the reinforced polymeric material comprises a composite or matrix including reinforcing material or phases such as fibers, rods, platelets, and fillers. More preferably, the polymeric material can include glass fibers, carbon fibers, polymeric fibers, ceramic fibers, or ceramic particulates. Other reinforcing material or phases known to one of ordinary skill in the art could also be used. One or more material from which the anchor is formed may be porous. Porosity can allow infiltration by cells from surrounding tissues, enhancing integration of the device by processes such as osseointegration.
[0050] In addition, one or more actives/agents may be incorporated into the material of the anchor. Suitable actives/agents include bone morphogenic proteins, antibiotics, antiinflammatories, angiogenic factors, osteogenic factors, monobutyrin, thrombin, modified proteins, platelet rich plasma/solution, platelet poor plasma/solution, bone marrow aspirate, and any cells sourced from flora or fauna, such as living cells, preserved cells, dormant cells, and dead cells. It will be appreciated that other bioactive agents known to one of ordinary skill in the art may also be used. Preferably, the active agent is incorporated into the polymeric shape memory material, to be released during the relaxation or degradation of
the polymer material. Advantageously, the incorporation of an active agent can act to combat infection at the site of implantation and/or to promote new tissue growth.
[0051] The anchor described above may also include at least one feature, such as protrusions, that are coupled to a surface of the anchor via a variety of methods, such as an interference fit between the polymer and the protrusions, adhesion of the protrusion to the polymer, or any other method known to one of ordinary skill in the art. In addition, the number of protrusions present on the surface of the anchor may vary. The protrusions may provide multiple contact points to increase the friction between the anchor and the bone, thereby providing increased fixation between the tissue graft and the bone. The protrusions may be selected from a group that includes a metal material, a non-metal material, a polymer material, and combinations thereof and may be of any shape or size. If a polymer material is used for the protrusions, the polymer material may include a resorbable or non- resorbable polymer material.
[0052] Use of the protrusions may be eliminated by including a particulate material within or on an outer surface of the anchor. The particulate material may include a ceramic material, a crystalline polymer, or any other type of material that would provide the polymer material with multiple contact points to increase the friction between the polymer material and the bone,
[0053] The anchors described above, and especially anchors 10,20, may be biaxially oriented to have an internal diameter that decreases and an external diameter that increases when the anchor is provided with energy. This allows for the internal diameter to further grip the anchor to the tissue graft(s) and the outer diameter to engage the surrounding bone, thereby locking the tissue graft(s) in place. In order to make an anchor of biaxially oriented shape memory polymer material, a rod of shape memory polymer material may be die drawn over a mandrel. Further discussion of this process can be found
in United States Patent Application Serial Number 60/912,740, the disclosure of which is incorporated herein by reference in its entirety,
[0054] The shape memory anchors of the present disclosure may substantially reduce the need to thread/pre-tap the bone tunnel before insertion of the anchor into the bone tunnel, especially when a patellar tendon is used as the tissue graft. In addition, it is believed that the anchor would offer improved fixation over existing systems. Furthermore, the anchors may substantially reduce the possibility of making a range of fasteners to fit the patient, thereby possibly offering a 'one size fits all' approach.
[0055] In view of the foregoing, it will be seen that the several advantages of the invention are achieved and attained.
[0056] The embodiments were chosen and described in order to best explain the principles of the disclosure and its practical application to thereby enable others skilled in the art to best utilize the disclosure in various embodiments and with various modifications as are suited to the particular use contemplated. [0057] As various modifications could be made in the constructions and methods herein described and illustrated without departing from the scope of the disclosure, it is intended that all matter contained in the foregoing description or 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
1. An anchor for fixating a tissue graft to bone, the anchor comprising: a through hole extending an entire length of the anchor, wherein the anchor includes a polymer composition having shape memory qualities.
2. The anchor of claim 1 wherein the through hole is circular, star-shaped, or rectangular.
3. The anchor of claim 1 further comprising a component disposed within the through hole of the anchor, the component including a polymer composition having shape memory qualities.
4. The anchor of claim 3 wherein the through hole is divided into two sections.
5. The anchor of claim 1 wherein the through hole is divided into four sections,
6. An anchor for fixating a tissue graft to bone, the anchor comprising; a first groove extending an entire length of the anchor and a second groove extending an entire length of the anchor, wherein the anchor includes a polymer composition having shape memory qualities.
7. The anchor of claim 6 wherein the first groove and the second groove both include barbs.
8. An anchor for fixating a tissue graft to bone, the anchor comprising a cross-section in a shape of a cross, the anchor including a polymer composition having shape memory qualities.
9. An anchor for fixating a tissue graft to bone, the anchor comprising a body having a curved top portion, a curved bottom portion, and two sides located between the top portion and the bottom portion.
10. The anchor of claim 9 wherein the sides are curved inward toward the body of the anchor.
11. A method of fixating a tissue graft to bone comprising: providing an anchor including a through hole extending an entire length of the anchor, the anchor including a polymer composition including shape memory polymer qualities; inserting an end of a tissue graft into the through hole; 5 inserting the anchor into a bone tunnel; providing the anchor with energy to deform the anchor and fixate the graft within the bone tunnel.
12. The method of claim 11 wherein the method further comprises a component disposed within the through hole of the anchor, the component including a polymer composition 0 having shape memory qualities.
13. The method of claim 12 wherein the through hole is divided into two sections, the method further comprising inserting ends of a tissue graft into the sections.
14. The method of claim 11 wherein the through hole is divided into four sections, the method further comprising inserting ends of multiple tissue grafts into the sections. 5 15. A method of fixating tissue grafts to bone comprising; providing at least two tissue grafts; coupling the at least two tissue grafts; inserting the at least two tissue grafts into a bone tunnel; inserting an anchor into the bone tunnel such that the anchor is located between the at O least two tissue grafts; and providing energy to the anchor to deform the anchor and fixate the at least two tissue grafts within the bone tunnel.
5
Priority Applications (6)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AU2008243035A AU2008243035B2 (en) | 2007-04-19 | 2008-04-16 | Graft fixation |
EP08745909A EP2150288B1 (en) | 2007-04-19 | 2008-04-16 | Graft fixation |
DE602008006181T DE602008006181D1 (en) | 2007-04-19 | 2008-04-16 | GRAFT FIXATION |
JP2010504201A JP5680957B2 (en) | 2007-04-19 | 2008-04-16 | Graft fixation |
US12/595,114 US9770534B2 (en) | 2007-04-19 | 2008-04-16 | Graft fixation |
AT08745909T ATE505220T1 (en) | 2007-04-19 | 2008-04-16 | GRAFT FIXATION |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US91282807P | 2007-04-19 | 2007-04-19 | |
US60/912,828 | 2007-04-19 |
Publications (2)
Publication Number | Publication Date |
---|---|
WO2008130954A2 true WO2008130954A2 (en) | 2008-10-30 |
WO2008130954A3 WO2008130954A3 (en) | 2009-10-22 |
Family
ID=39817075
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US2008/060401 WO2008130954A2 (en) | 2007-04-19 | 2008-04-16 | Graft fixation |
Country Status (7)
Country | Link |
---|---|
US (1) | US9770534B2 (en) |
EP (1) | EP2150288B1 (en) |
JP (1) | JP5680957B2 (en) |
AT (1) | ATE505220T1 (en) |
AU (1) | AU2008243035B2 (en) |
DE (1) | DE602008006181D1 (en) |
WO (1) | WO2008130954A2 (en) |
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2010117982A1 (en) * | 2009-04-06 | 2010-10-14 | Smith & Nephew, Inc. | Tissue graft anchor |
CH702937A1 (en) * | 2010-04-13 | 2011-10-14 | Synergy Biosurgical Ag C O Confidas Treuhand Ag | Fixation implant. |
EP2221014B1 (en) | 2009-02-23 | 2015-05-20 | Inion Oy | Implant, implantation tool and kit |
Families Citing this family (20)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7195642B2 (en) | 2001-03-13 | 2007-03-27 | Mckernan Daniel J | Method and apparatus for fixing a graft in a bone tunnel |
US8512376B2 (en) | 2002-08-30 | 2013-08-20 | Arthrex, Inc. | Method and apparatus for internal fixation of an acromioclavicular joint dislocation of the shoulder |
US8460379B2 (en) | 2009-03-31 | 2013-06-11 | Arthrex, Inc. | Adjustable suture button construct and methods of tissue reconstruction |
US8439976B2 (en) * | 2009-03-31 | 2013-05-14 | Arthrex, Inc. | Integrated adjustable button-suture-graft construct with two fixation devices |
US8449612B2 (en) * | 2009-11-16 | 2013-05-28 | Arthrocare Corporation | Graft pulley and methods of use |
EP2455001B1 (en) | 2010-11-17 | 2020-07-22 | Arthrex, Inc. | Adjustable suture-button constructs for ligament reconstruction |
EP2455040B1 (en) | 2010-11-17 | 2015-03-04 | Arthrex, Inc. | Adjustable suture-button construct for knotless stabilization of cranial cruciate deficient ligament stifle |
EP2455002B1 (en) | 2010-11-17 | 2019-04-03 | Arthrex, Inc. | Adjustable suture-button construct for ankle syndesmosis repair |
US9301745B2 (en) | 2011-07-21 | 2016-04-05 | Arthrex, Inc. | Knotless suture constructs |
US9332979B2 (en) | 2011-07-22 | 2016-05-10 | Arthrex, Inc. | Tensionable knotless acromioclavicular repairs and constructs |
WO2013033634A1 (en) * | 2011-09-01 | 2013-03-07 | Toby Orthopaedics, Llc | Tendon crimp for passage into a bone tunnel and method for use thereof |
US9107653B2 (en) | 2011-09-22 | 2015-08-18 | Arthrex, Inc. | Tensionable knotless anchors with splice and methods of tissue repair |
US10245016B2 (en) | 2011-10-12 | 2019-04-02 | Arthrex, Inc. | Adjustable self-locking loop constructs for tissue repairs and reconstructions |
US9615821B2 (en) | 2011-12-09 | 2017-04-11 | Arthrex, Inc. | Tensionable knotless anchor systems and methods of tissue repair |
US9737292B2 (en) | 2012-06-22 | 2017-08-22 | Arthrex, Inc. | Knotless suture anchors and methods of tissue repair |
CN105705173A (en) * | 2013-05-24 | 2016-06-22 | 东北大学 | Nanomaterials for the integration of soft into hard tissue |
US9301832B2 (en) | 2013-08-01 | 2016-04-05 | Christopher Sterling Pallia | Tendon anchor and method of using same |
US10335136B2 (en) | 2015-08-20 | 2019-07-02 | Arthrex, Inc. | Tensionable constructs with multi-limb locking mechanism through single splice and methods of tissue repair |
US10265060B2 (en) | 2015-08-20 | 2019-04-23 | Arthrex, Inc. | Tensionable constructs with multi-limb locking mechanism through single splice and methods of tissue repair |
DE102016109684A1 (en) * | 2016-05-25 | 2017-11-30 | Gerd Seitlinger | Fixation element and fixation system |
Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5078607A (en) | 1987-01-08 | 1992-01-07 | Core-Vent Corporation | Dental implant including plural anchoring means |
WO2000056376A1 (en) | 1999-03-25 | 2000-09-28 | Metabolix, Inc. | Medical devices and applications of polyhydroxyalkanoate polymers |
Family Cites Families (399)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
NL109080C (en) | 1955-11-30 | |||
US3531561A (en) * | 1965-04-20 | 1970-09-29 | Ethicon Inc | Suture preparation |
FR1441623A (en) | 1965-04-26 | 1966-06-10 | Device and method for the manufacture of shrink sleeves in plastics, in particular in polyethylene crosslinked by irradiation | |
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 |
GB1416575A (en) | 1973-04-18 | 1975-12-03 | Sakai Kasei Kogyo Kk | Apparatus for continuous production of biaxially shrinkable thermoplastic synthetic resin tube |
US3856905A (en) * | 1972-09-22 | 1974-12-24 | Dow Chemical Co | Oriented plastic tube |
FR2215123A5 (en) * | 1972-12-22 | 1974-08-19 | Pontigny Jacques | |
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 |
DE3036611A1 (en) | 1980-09-29 | 1982-06-09 | Kabel- und Metallwerke Gutehoffnungshütte AG, 3000 Hannover | Sealed connection esp. between cable and duct - produced using hot-shrink thermoplastics tube which shrinks at one end and expands at the other |
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 |
US4643734A (en) | 1983-05-05 | 1987-02-17 | Hexcel Corporation | Lactide/caprolactone polymer, method of making the same, composites thereof, and prostheses produced therefrom |
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 |
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 |
JPS62199429A (en) | 1986-02-28 | 1987-09-03 | Furukawa Electric Co Ltd:The | Manufacture of thermally recoverable article |
US5061181A (en) * | 1987-01-08 | 1991-10-29 | Core-Vent Corporation | Dental implant including plural anchoring means |
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 |
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, 1000 Berlin, De | |
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 |
US5502158A (en) * | 1988-08-08 | 1996-03-26 | Ecopol, Llc | Degradable polymer composition |
US5444113A (en) * | 1988-08-08 | 1995-08-22 | Ecopol, Llc | End use applications of biodegradable polymers |
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 |
JPH0796597B2 (en) | 1988-12-23 | 1995-10-18 | 旭化成工業株式会社 | Method for manufacturing shape memory resin molded body |
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 |
JPH02270519A (en) | 1989-04-12 | 1990-11-05 | Yamaha Corp | Forming method |
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 |
JPH0321613A (en) | 1989-06-19 | 1991-01-30 | Nippon Unicar Co Ltd | Shape-memorizing elastomer |
US5294395A (en) * | 1989-09-01 | 1994-03-15 | Ethicon, Inc. | Thermal treatment of theraplastic filaments for the preparation of surgical sutures |
US5201771A (en) * | 1989-09-15 | 1993-04-13 | Belykh Sergei I | Endoprosthesis 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 |
DE69120177T2 (en) * | 1990-09-10 | 1996-10-10 | Synthes Ag | Bone regeneration membrane |
CA2062012C (en) * | 1991-03-05 | 2003-04-29 | Randall D. Ross | Bioabsorbable interference bone fixation screw |
FR2673843B1 (en) * | 1991-03-14 | 1995-01-13 | Centre Nat Rech Scient | IMPLANTABLE, BIORESORBABLE PHARMACEUTICAL COMPOSITION BASED ON POLY (LACTIC ACID), INTENDED TO IMPLEMENT A LOCAL INTERNAL ANTIBOTHERAPY. |
DE4110316A1 (en) | 1991-03-28 | 1992-10-01 | Uwe Storch | USE OF A MIXTURE FOR THE PRODUCTION OF MEDICAL IMPLANTS |
US5108289A (en) * | 1991-04-10 | 1992-04-28 | Sekio Fukuyo | Dental endosseous implant |
ATE131373T1 (en) * | 1991-05-24 | 1995-12-15 | Synthes Ag | ABSORBABLE TENDON AND BONE REINFORCEMENT 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 |
JPH05147105A (en) | 1991-11-29 | 1993-06-15 | Dainippon Ink & Chem Inc | Article molded out of shape-memorizing polymer material composition, shape-memorizable polymer material and usage thereof |
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 |
JP3485320B2 (en) * | 1992-02-14 | 2004-01-13 | スミス アンド ネフュー インコーポレーテッド | Surgical polymer screws and coatings |
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 |
US5208305A (en) * | 1992-04-17 | 1993-05-04 | Minnesota Mining And Manufacturing Company | Fluorine-containing polymers and preparation and use thereof |
WO1993022987A2 (en) * | 1992-05-20 | 1993-11-25 | Cytrx Corporation | Gel composition for implant and method |
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 |
JP3128981B2 (en) | 1992-08-21 | 2001-01-29 | 東ソー株式会社 | Shape memory resin material |
US5319003A (en) | 1992-09-30 | 1994-06-07 | Union Carbide Chemicals & Plastics Technology Corporation | Method for improving the mechanical performance of composite articles |
DK0615555T3 (en) * | 1992-10-02 | 2001-07-09 | Cargill Inc | Textile material of melt-stable lactide polymer and process for preparation 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 |
JPH06234157A (en) | 1993-02-08 | 1994-08-23 | Sumitomo Electric Ind Ltd | Manufacture of molded material of thermal recovery properties |
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 |
CA2127636C (en) | 1993-07-21 | 2009-10-20 | Cheng-Kung Liu | Plasticizers for fibers used to form surgical devices |
EP0725598A1 (en) * | 1993-10-28 | 1996-08-14 | Javin Pierce | A suture anchor |
US5324308A (en) * | 1993-10-28 | 1994-06-28 | Javin Pierce | Suture anchor |
US5545180A (en) * | 1993-12-13 | 1996-08-13 | Ethicon, Inc. | Umbrella-shaped suture anchor device with actuating ring member |
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 |
WO1995034331A1 (en) | 1994-06-10 | 1995-12-21 | Ao-Forschungsinstitut Davos | Self-expanding, adaptable cavity plug for use in implantation of endo-joint prosthesis |
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 |
ATE196486T1 (en) * | 1994-08-10 | 2000-10-15 | 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 |
US5766009A (en) | 1995-01-20 | 1998-06-16 | Jeffcoat; Robert L. | Elastically stabilized endosseous dental implant |
US5634936A (en) * | 1995-02-06 | 1997-06-03 | Scimed Life Systems, Inc. | Device for closing a septal defect |
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 |
IT1277799B1 (en) | 1995-07-28 | 1997-11-12 | Sanitaria Scaligera Spa | PROCEDURE FOR THE SURFACE FUNCTIONALIZATION OF BIOCOMPATIBLE AND BIOABSORBABLE ALIPHATIC POLYESTERS AND POLYESTERS SO ACTIVATED |
JP4020441B2 (en) | 1995-07-28 | 2007-12-12 | トヨタ自動車株式会社 | Polylactic acid block copolymer, production method thereof and molded product thereof |
JP2912923B2 (en) | 1995-09-25 | 1999-06-28 | タキロン株式会社 | Biodegradable and absorbable surgical material and method for producing the same |
FI98136C (en) | 1995-09-27 | 1997-04-25 | Biocon Oy | A tissue-soluble material and process for its manufacture |
JP3398268B2 (en) | 1995-09-29 | 2003-04-21 | 信越化学工業株式会社 | Biodegradable polymer composition |
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 |
US5817328A (en) * | 1996-01-17 | 1998-10-06 | Cambridge Scientific, Inc. | Material for buffered resorbable internal fixation devices and method for making same |
WO1997025936A1 (en) | 1996-01-17 | 1997-07-24 | Cambridge Scientific, Inc. | Buffered resorbable internal fixation devices for repair of bone fractures |
JPH09221539A (en) | 1996-02-14 | 1997-08-26 | Shimadzu Corp | Biodegradable resin for constituting shaper memory resin molding and molding formed therefrom |
WO1997029673A1 (en) | 1996-02-14 | 1997-08-21 | Pressalit A/S | A toilet cover assembly with damper |
US5902599A (en) * | 1996-02-20 | 1999-05-11 | Massachusetts Institute Of Technology | Biodegradable polymer networks for use in orthopedic and dental applications |
JPH09234241A (en) | 1996-02-29 | 1997-09-09 | Shimadzu Corp | Orthosis having thermally deforming property |
JP3645647B2 (en) | 1996-04-05 | 2005-05-11 | トヨタ自動車株式会社 | Polylactic acid polymer composition and molded product thereof |
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 |
DE69725208T2 (en) | 1996-05-09 | 2004-07-15 | Kureha Kagaku Kogyo K.K. | Stretch blow molded container and process for its manufacture |
US6143948A (en) | 1996-05-10 | 2000-11-07 | Isotis B.V. | Device for incorporation and release of biologically active agents |
CA2252860C (en) | 1996-05-28 | 2011-03-22 | 1218122 Ontario Inc. | Resorbable implant biomaterial made of condensed calcium phosphate particles |
US5670161A (en) * | 1996-05-28 | 1997-09-23 | Healy; Kevin E. | Biodegradable stent |
US5935172A (en) * | 1996-06-28 | 1999-08-10 | Johnson & Johnson Professional, Inc. | Prosthesis with variable fit and strain distribution |
US6063792A (en) | 1996-07-01 | 2000-05-16 | Sepracor Inc. | Methods and compositions for treating urinary incontinence using enantiomerically enriched (S)-trihexyphenidyl |
US5756651A (en) * | 1996-07-17 | 1998-05-26 | Chronopol, Inc. | Impact modified polylactide |
CA2264869C (en) * | 1996-08-23 | 2006-01-03 | Osteobiologics, Inc. | Handheld materials tester |
KR0180858B1 (en) | 1996-09-19 | 1999-04-01 | 김경환 | Novel ice nucleation microorganism |
JP3747563B2 (en) | 1996-10-18 | 2006-02-22 | 東レ株式会社 | POLYLACTIC ACID COMPOSITION, PROCESS FOR PRODUCING THE SAME, AND MOLDED ARTICLE OF THE COMPOSITION |
US7351421B2 (en) | 1996-11-05 | 2008-04-01 | Hsing-Wen Sung | Drug-eluting stent having collagen drug carrier chemically treated with genipin |
US6258351B1 (en) | 1996-11-06 | 2001-07-10 | Shearwater Corporation | Delivery of poly(ethylene glycol)-modified molecules from degradable hydrogels |
US5893850A (en) * | 1996-11-12 | 1999-04-13 | Cachia; Victor V. | Bone fixation device |
AU5596898A (en) | 1996-12-03 | 1998-06-29 | Osteobiologics, Inc. | Biodegradable polymeric film |
FI965067A0 (en) | 1996-12-17 | 1996-12-17 | Jvs Polymers Oy | Implantmaterial som kan plastiseras |
US6083522A (en) | 1997-01-09 | 2000-07-04 | Neucoll, Inc. | Devices for tissue repair and methods for preparation and use thereof |
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 |
JP3503045B2 (en) | 1997-05-13 | 2004-03-02 | タキロン株式会社 | Shape memory biodegradable absorbent material |
AU738334B2 (en) | 1997-05-30 | 2001-09-13 | 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 |
KR20010014384A (en) | 1997-07-02 | 2001-02-26 | 모리타 다카카즈 | Polylactic acid scleral plugs |
US5980564A (en) | 1997-08-01 | 1999-11-09 | Schneider (Usa) Inc. | Bioabsorbable implantable endoprosthesis with reservoir |
GB9717433D0 (en) | 1997-08-19 | 1997-10-22 | Univ Nottingham | Biodegradable composites |
US6001100A (en) | 1997-08-19 | 1999-12-14 | Bionx Implants Oy | Bone block fixation implant |
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 |
US6135987A (en) | 1997-12-22 | 2000-10-24 | Kimberly-Clark Worldwide, Inc. | Synthetic fiber |
US6150497A (en) | 1998-01-14 | 2000-11-21 | Sherwood Services Ag | Method for the production of polyglycolic acid |
JP2972913B2 (en) | 1998-01-20 | 1999-11-08 | 工業技術院長 | Shape memory method and shape restoration method for biodegradable shape memory polymer molded article |
US6547792B1 (en) | 1998-02-13 | 2003-04-15 | Gunze Limited | Bone fixing pin |
PL342996A1 (en) | 1998-02-23 | 2001-07-16 | Mnemoscience Gmbh | Shape memory polymers |
HU222543B1 (en) | 1998-02-23 | 2003-08-28 | Massachusetts Institute Of Technology | Biodegradable shape memory polymers |
ID26886A (en) | 1998-03-11 | 2001-02-15 | Dow Chemical Co | ARRANGING MATERIALS AND ARTIFICIAL MATERIALS WHICH HAVE MEMORI FORMS MADE FROM α-OLEFIN / VINYL INTERIN OR VOLUTIONS AND AROMATIC VINILIDENTS AND / OR VINILS OR ALIFATIC VINILIDENTS AVOIDED |
US5997582A (en) * | 1998-05-01 | 1999-12-07 | Weiss; James M. | Hip replacement methods and apparatus |
AU3851799A (en) | 1998-05-28 | 1999-12-13 | Gunze Limited | 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 |
US5951288A (en) * | 1998-07-03 | 1999-09-14 | Sawa; Shlaimon T. | Self expanding dental implant and method for using the same |
GB9814609D0 (en) | 1998-07-07 | 1998-09-02 | Smith & Nephew | Polymers |
US6248430B1 (en) | 1998-08-11 | 2001-06-19 | Dainippon Ink And Chemicals, Inc. | Lactic acid-based polymer laminated product and molded product |
US6406498B1 (en) | 1998-09-04 | 2002-06-18 | Bionx Implants Oy | Bioactive, bioabsorbable surgical composite material |
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 |
EP0995449A1 (en) | 1998-10-21 | 2000-04-26 | Sulzer Orthopädie AG | UHMW-polyethylene for implants |
US6162225A (en) | 1998-10-26 | 2000-12-19 | Musculoskeletal Transplant Foundation | Allograft bone fixation screw method and apparatus |
DE69822470T2 (en) | 1998-11-12 | 2005-01-20 | Takiron Co. Ltd. | Biodegradable absorbable shape memory 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 |
EP1148830A1 (en) | 1999-02-04 | 2001-10-31 | Synthes Ag Chur | 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 |
WO2000054821A1 (en) | 1999-03-16 | 2000-09-21 | 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 |
US6296645B1 (en) | 1999-04-09 | 2001-10-02 | Depuy Orthopaedics, Inc. | Intramedullary nail with non-metal spacers |
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 |
US7462162B2 (en) | 2001-09-04 | 2008-12-09 | Broncus Technologies, Inc. | Antiproliferative 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 |
GB9930390D0 (en) | 1999-12-22 | 2000-02-16 | Univ Brunel | Releasable fasteners |
DE59901090D1 (en) | 1999-12-23 | 2002-05-02 | Storz Karl Gmbh & Co Kg | Decentralized drive screw |
US6908624B2 (en) | 1999-12-23 | 2005-06-21 | Advanced Cardiovascular Systems, Inc. | Coating for implantable devices and a method of forming the same |
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 |
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 |
AU2001263223A1 (en) | 2000-06-15 | 2001-12-24 | Owens Corning | Moldable matrix polymer material, molded composite product and method for makingsame |
US6447515B1 (en) | 2000-06-21 | 2002-09-10 | Russell Meldrum | Bioresorbable implant for fracture fixation |
JP2004511431A (en) | 2000-06-28 | 2004-04-15 | アトゥル・ジェイ・シュクラ | Biodegradable vehicles and delivery systems containing bioactive agents |
JP5244279B2 (en) | 2000-07-27 | 2013-07-24 | ラトガーズ,ザ ステイト ユニバーシティ | Therapeutic polyesters and polyamides |
WO2002013701A1 (en) | 2000-08-17 | 2002-02-21 | Tyco Healthcare Group Lp | Sutures and coatings made from therapeutic absorbable glass |
AU2001288829A1 (en) | 2000-09-06 | 2002-03-22 | Ap Pharma, Inc. | Degradable polyacetal polymers |
CA2426784A1 (en) | 2000-10-25 | 2002-05-02 | Sdgi Holdings, Inc. | Self-forming orthopedic implants |
AU2002243270B2 (en) | 2000-10-25 | 2006-03-09 | Warsaw Orthopedic, Inc. | Vertically expanding intervertebral body fusion device |
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 |
EP1545705A4 (en) | 2000-11-16 | 2010-04-28 | 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 |
JP2004531292A (en) | 2001-01-02 | 2004-10-14 | アドヴァンスト セラミックス リサーチ インコーポレイテッド | Biomedically applied compositions and methods |
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 |
US7267288B2 (en) | 2001-03-22 | 2007-09-11 | Nevada Supply Corporation | Polyurethane in intimate contact with fibrous 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 |
US6508830B2 (en) * | 2001-04-30 | 2003-01-21 | Musculoskeletal Transplant Foundation | Suture anchor |
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 |
US20030093105A1 (en) * | 2001-07-13 | 2003-05-15 | Scimed Life Systems, Inc. | Guide catheter for introduction into the subarachnoid space and methods of use thereof |
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 |
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 |
US20050137611A1 (en) | 2001-09-04 | 2005-06-23 | Broncus Technologies, Inc. | Methods and devices for maintaining surgically created channels in a body organ |
JP4763944B2 (en) | 2001-09-26 | 2011-08-31 | 株式会社クラレ | Method for producing stretched molded article |
US6916321B2 (en) | 2001-09-28 | 2005-07-12 | Ethicon, Inc. | Self-tapping resorbable two-piece bone screw |
US20030125508A1 (en) * | 2001-10-31 | 2003-07-03 | Kazuyuki Yamane | Crystalline polyglycolic acid, polyglycolic acid composition and production process thereof |
US20030125745A1 (en) | 2001-11-05 | 2003-07-03 | Bio One Tech Inc. | Bone-fixing device |
CN1301757C (en) | 2001-11-27 | 2007-02-28 | 多喜兰株式会社 | Implant material and process for producing the same |
HUP0402135A3 (en) | 2001-11-30 | 2008-04-28 | Pfizer | Controlled release implant forming polymeric compositions of bone growth promoting compounds and process for their preparation |
US7713272B2 (en) | 2001-12-20 | 2010-05-11 | Ethicon, Inc. | Bioabsorbable coatings of surgical devices |
WO2003059203A1 (en) | 2001-12-21 | 2003-07-24 | Smith & Nephew, Inc. | Hinged 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 |
ATE462378T1 (en) | 2001-12-28 | 2010-04-15 | Edwards Lifesciences Ag | DELAYED MEMORY DEVICE |
GB0202233D0 (en) | 2002-01-31 | 2002-03-20 | Smith & Nephew | Bioresorbable polymers |
EP1499267A4 (en) | 2002-02-05 | 2008-10-29 | Depuy Mitek 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 |
AU2003225516A1 (en) | 2002-03-26 | 2003-10-08 | Yissum Research Development Company Of The Hebrew University Of Jerusalem | Responsive biomedical composites |
US8303625B2 (en) | 2002-04-18 | 2012-11-06 | Helmholtz-Zentrum Geesthacht Zentrum Fuer Material- Und Kuestenforschung 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 |
US7166133B2 (en) | 2002-06-13 | 2007-01-23 | Kensey Nash Corporation | Devices and methods for treating defects in the tissue of a living being |
US20030236533A1 (en) * | 2002-06-20 | 2003-12-25 | The Regents Of The University Of California | Shape memory polymer actuator and catheter |
US7044977B2 (en) | 2002-06-27 | 2006-05-16 | Ferree Bret A | Expanding arthroplasty devices |
US20040002770A1 (en) | 2002-06-28 | 2004-01-01 | King Richard S. | Polymer-bioceramic composite for orthopaedic applications and method of manufacture thereof |
CA2494400A1 (en) | 2002-07-31 | 2004-02-05 | Alza Corporation | Injectable multimodal polymer depot compositions and uses thereof |
US20050019404A1 (en) | 2003-06-30 | 2005-01-27 | Hsing-Wen Sung | Drug-eluting biodegradable stent |
CA2497973C (en) | 2002-09-05 | 2012-11-06 | Catherine G. Ambrose | Antibiotic microspheres for treatment of infections and osteomyelitis |
AU2003270802A1 (en) | 2002-09-20 | 2004-04-08 | The Children's Hospital Of Philadelphia | Engineering of material surfaces |
WO2004032988A2 (en) | 2002-10-08 | 2004-04-22 | 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 |
US7308738B2 (en) * | 2002-10-19 | 2007-12-18 | General Motors Corporation | Releasable fastener systems and processes |
US6908264B1 (en) * | 2002-11-06 | 2005-06-21 | William P. Gundy | Quick change drill bit |
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 |
EP1578957B1 (en) | 2002-12-12 | 2015-04-15 | Warsaw Orthopedic, Inc. | Formable and settable polymer bone composite and method of production thereof |
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 |
WO2004065450A2 (en) | 2003-01-16 | 2004-08-05 | Carnegie Mellon University | Biodegradable polyurethanes and use thereof |
WO2004071356A2 (en) | 2003-02-10 | 2004-08-26 | 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 |
EP1601320A4 (en) | 2003-02-21 | 2012-02-22 | 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 |
WO2004082524A2 (en) | 2003-03-13 | 2004-09-30 | William 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 |
JP4357478B2 (en) | 2003-06-12 | 2009-11-04 | ジンテーズ ゲゼルシャフト ミト ベシュレンクテル ハフツング | Surgical nail |
EP1633281A1 (en) | 2003-06-13 | 2006-03-15 | 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 |
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 |
US7481839B2 (en) * | 2003-12-02 | 2009-01-27 | Kyphon Sarl | Bioresorbable interspinous process implant for use with intervertebral disk remediation or replacement implants and procedures |
US8157855B2 (en) | 2003-12-05 | 2012-04-17 | Boston Scientific Scimed, Inc. | Detachable segment stent |
FR2863478A1 (en) | 2003-12-10 | 2005-06-17 | Pierre Luc Reynaud | Dental restoration prosthesis comprises a rigid core surrounded by a sheath made of a material that loses its mechanical bonding characteristics when subjected to a stimulus |
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 |
JP2007517635A (en) | 2004-01-16 | 2007-07-05 | オステオバイオロジックス, インコーポレイテッド | Bone-tendon-bone implant |
WO2005077039A2 (en) | 2004-02-05 | 2005-08-25 | Osteobiologics, Inc. | 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 |
WO2005085313A1 (en) | 2004-03-03 | 2005-09-15 | Commonwealth Scientific And Industrial Research Organisation | Polymer compositions for dual or multi staged curing |
TW200533385A (en) | 2004-03-03 | 2005-10-16 | Commw Scient Ind Res Org | Biocompatible polymer compositions for dual or multi staged curing |
WO2005086849A2 (en) | 2004-03-09 | 2005-09-22 | Osteobiologics, Inc. | Implant scaffold combined with autologous or allogenic tissue |
CN1950098B (en) | 2004-03-24 | 2013-02-27 | 宝利诺沃生物材料有限公司 | Biodegradable polyurethane and polyurethane ureas |
US7285130B2 (en) | 2004-04-27 | 2007-10-23 | Boston Scientific Scimed, Inc. | Stent delivery system |
EP1753354B1 (en) | 2004-05-21 | 2010-09-15 | Myers Surgical Solutions, LLC | Fracture fixation and site 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 |
US20060095138A1 (en) * | 2004-06-09 | 2006-05-04 | Csaba Truckai | Composites and methods for treating bone |
US7285087B2 (en) | 2004-07-15 | 2007-10-23 | Micardia Corporation | Shape memory devices and methods for reshaping heart anatomy |
US8460378B2 (en) | 2004-07-26 | 2013-06-11 | DePuy Sythes Products, LLC | Biocompatible, biodegradable polyurethane materials with controlled hydrophobic to hydrophilic ratio |
US20080200638A1 (en) | 2004-07-30 | 2008-08-21 | Jody Redepenning | Bioresorbable Composites and Method of Formation Thereof |
US20060067971A1 (en) | 2004-09-27 | 2006-03-30 | Story Brooks J | Bone void filler |
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 |
WO2006060416A2 (en) | 2004-11-30 | 2006-06-08 | Osteobiologics, Inc. | Implants and delivery system for treating defects in articulating surfaces |
US20060121087A1 (en) | 2004-12-06 | 2006-06-08 | Williams Michael S | Polymeric endoprostheses with modified erosion rates and methods of manufacture |
WO2006062518A2 (en) | 2004-12-08 | 2006-06-15 | Interpore Spine Ltd. | Continuous phase composite for musculoskeletal repair |
ITPD20040312A1 (en) | 2004-12-15 | 2005-03-15 | Fidia Advanced Biopolymers Srl | PROSTHESIS AND SUPPORT FOR REPLACEMENT, REPAIR, REGENERATION OF THE MENISCUS |
US7772352B2 (en) | 2005-01-28 | 2010-08-10 | Bezwada Biomedical Llc | Bioabsorbable and biocompatible polyurethanes and polyamides for medical devices |
WO2006083946A2 (en) | 2005-02-01 | 2006-08-10 | Osteobiologics, Inc. | Method and device for selective addition of a bioactive agent to a multi-phase implant |
WO2006083991A2 (en) | 2005-02-04 | 2006-08-10 | Poly-Med, Inc. | Fiber-reinforced composite absorbable endoureteral stent |
US20060207612A1 (en) * | 2005-02-08 | 2006-09-21 | Jasper Jackson | Tissue anchoring system for percutaneous glossoplasty |
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 |
WO2006095138A1 (en) | 2005-03-07 | 2006-09-14 | H Young (Operations) Limited | Security system |
DE112006000699T5 (en) | 2005-03-25 | 2008-02-07 | Sumitomo Electric Fine Polymer, Inc. | Polylactic acid complex and process for producing the same |
AU2006232116A1 (en) * | 2005-04-01 | 2006-10-12 | The Regents Of The University Of Colorado | A graft fixation device and method |
RU2007140909A (en) | 2005-04-04 | 2009-05-20 | Синексус, Инк. (Us) | DEVICE AND METHODS FOR TREATING DISEASES OF THE NANOLAIN SINUS |
US7357815B2 (en) | 2005-04-21 | 2008-04-15 | Micardia Corporation | Dynamically adjustable implants and methods for reshaping tissue |
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 |
EP1909704A2 (en) | 2005-06-02 | 2008-04-16 | Zimmer Spine, Inc. | Interbody fusion ring and method of using the same |
DE102005032005B4 (en) | 2005-07-08 | 2007-05-31 | Adolf Pfaff Dr. Karl-Friedrich Reichenbach Gbr (Vertretungsberechtigter Gesellschafter: Adolf Pfaff, 79183 Waldkirch) | filling material pin |
US20070014831A1 (en) | 2005-07-12 | 2007-01-18 | Hsing-Wen Sung | Biodegradable occlusive device with moisture memory |
JP4899152B2 (en) | 2005-07-15 | 2012-03-21 | 独立行政法人産業技術総合研究所 | MEDICAL RESIN COMPOSITION, PROCESS FOR PRODUCING THE SAME, AND MOLDED ARTICLE |
FI122342B (en) | 2005-07-18 | 2011-12-15 | Bioretec Oy | Bioabsorbable tape system, bioabsorbable tape and method of forming a bioabsorbable tape. |
US20070038292A1 (en) | 2005-08-09 | 2007-02-15 | Moise Danielpour | Bio-absorbable stent |
US20090274742A1 (en) | 2005-08-18 | 2009-11-05 | Brown Malcolm Nmi | Multimodal high strength devices and composites |
WO2007020432A2 (en) | 2005-08-18 | 2007-02-22 | Smith & Nephew, Plc | High strength devices and composites |
US20070048383A1 (en) | 2005-08-25 | 2007-03-01 | Helmus Michael N | Self-assembled endovascular structures |
EP1940481B1 (en) | 2005-08-25 | 2015-01-14 | Medtronic Vascular, Inc. | Medical devices and coatings therefore comprising biodegradable polymers with enhanced functionality |
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 |
US7691105B2 (en) | 2005-09-26 | 2010-04-06 | Depuy Spine, Inc. | Tissue augmentation, stabilization and regeneration technique |
US20070100449A1 (en) | 2005-10-31 | 2007-05-03 | O'neil Michael | Injectable soft tissue fixation technique |
CA2630661A1 (en) | 2005-11-29 | 2007-06-07 | Indiana University Research And Technology Corporation | Biodegradable implant ploymers and composites |
JP2009518129A (en) | 2005-12-06 | 2009-05-07 | タイコ ヘルスケア グループ リミテッド パートナーシップ | Bioabsorbable surgical composition |
US9446226B2 (en) | 2005-12-07 | 2016-09-20 | Ramot At Tel-Aviv University Ltd. | Drug-delivering composite structures |
CN101346105A (en) | 2005-12-21 | 2009-01-14 | 新特斯有限责任公司 | Resorbable anterior cervical plating system with screw retention mechanism |
JP2009527261A (en) | 2006-01-13 | 2009-07-30 | バイオダイナミクス・リミテッド・ライアビリティ・カンパニー | Surgical fasteners having bioabsorbable components and associated implant devices |
EP1976460A4 (en) | 2006-01-19 | 2012-06-20 | Warsaw Orthopedic Inc | Injectable and moldable bone substitute materials |
CA2637606C (en) | 2006-01-19 | 2013-03-19 | Osteotech, Inc. | Porous osteoimplant |
JP5508720B2 (en) | 2006-02-07 | 2014-06-04 | テファ, インコーポレイテッド | Polymer degradable drug eluting stent and coating |
US20070224234A1 (en) | 2006-03-22 | 2007-09-27 | Mark Steckel | Medical devices having biodegradable polymeric regions |
EP2007288A4 (en) * | 2006-03-30 | 2011-03-16 | Univ Colorado Regents | Shape memory polymer medical devices |
EP2007317A2 (en) | 2006-04-05 | 2008-12-31 | University Of Nebraska | Bioresorbable polymer reconstituted bone and methods of formation thereof |
WO2007130648A2 (en) | 2006-05-05 | 2007-11-15 | Ceramatec, Inc. | Fully or partially bioresorbable orthopedic implant |
FI119177B (en) | 2006-05-05 | 2008-08-29 | Bioretec Oy | Bioabsorbable, deformable fixation material and implants |
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 |
NZ573125A (en) | 2006-06-28 | 2011-12-22 | Gunze Kk | Method for preparing biodegradable lactide caprolactone copolymers having a low metal catalyst impurity by subsequent washing with acetic acid and isopropanol |
HRPK20060238B3 (en) | 2006-07-04 | 2009-06-30 | Štimac Boris | Polyurethane toilet seat and cover with reinforcement |
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 |
GB2442706A (en) | 2006-10-09 | 2008-04-16 | Mohamed Khalid | An intramedullary rod for the fixation of bone fractures |
US20080109037A1 (en) * | 2006-11-03 | 2008-05-08 | Musculoskeletal Transplant Foundation | Press fit suture anchor and inserter assembly |
CA2679365C (en) | 2006-11-30 | 2016-05-03 | Smith & Nephew, Inc. | Fiber reinforced composite material |
US20090144999A1 (en) | 2006-11-30 | 2009-06-11 | Lau Kam C | Interior contour measurement probe |
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 |
CN101677957A (en) | 2007-02-05 | 2010-03-24 | 卡比兰生物外科公司 | The polymer formulations that is used for delivery of bioactive agents |
EP1961433A1 (en) | 2007-02-20 | 2008-08-27 | National University of Ireland Galway | Porous substrates for implantation |
WO2008106625A2 (en) | 2007-02-28 | 2008-09-04 | University Of Notre Dame Du Lac | Porous composite biomaterials and related methods |
US20080234762A1 (en) | 2007-03-06 | 2008-09-25 | Zimmer Technology, Inc. | Self-tapping screw with resorbable tip |
WO2008112875A2 (en) | 2007-03-13 | 2008-09-18 | Smith & Nephew, Inc. | Internal fixation devices |
EP2139532A2 (en) | 2007-03-13 | 2010-01-06 | Smith & Nephew, Inc. | Systems and methods for installing and removing an expandable polymer |
EP2131879B1 (en) | 2007-03-13 | 2019-10-09 | Smith & Nephew, Inc. | Internal fixation devices |
EP1972352B1 (en) | 2007-03-23 | 2011-08-10 | Stryker Trauma GmbH | Implantation device, method for producing and for applying the same |
WO2008119053A1 (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 |
JP5416090B2 (en) | 2007-04-18 | 2014-02-12 | スミス アンド ネフュー ピーエルシー | Expansion molding of shape memory polymer |
EP2142227B1 (en) | 2007-04-19 | 2012-02-29 | Smith & Nephew, Inc. | Multi-modal shape memory polymers |
EP2142122A1 (en) | 2007-04-27 | 2010-01-13 | Synthes GmbH | Implant devices constructed with metallic and polymeric components |
AU2008307139B2 (en) | 2007-10-03 | 2012-12-20 | Polynovo Biomaterials Pty 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 |
-
2008
- 2008-04-16 US US12/595,114 patent/US9770534B2/en not_active Expired - Fee Related
- 2008-04-16 JP JP2010504201A patent/JP5680957B2/en not_active Expired - Fee Related
- 2008-04-16 WO PCT/US2008/060401 patent/WO2008130954A2/en active Application Filing
- 2008-04-16 AT AT08745909T patent/ATE505220T1/en not_active IP Right Cessation
- 2008-04-16 AU AU2008243035A patent/AU2008243035B2/en not_active Ceased
- 2008-04-16 EP EP08745909A patent/EP2150288B1/en not_active Not-in-force
- 2008-04-16 DE DE602008006181T patent/DE602008006181D1/en active Active
Patent Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5078607A (en) | 1987-01-08 | 1992-01-07 | Core-Vent Corporation | Dental implant including plural anchoring means |
WO2000056376A1 (en) | 1999-03-25 | 2000-09-28 | Metabolix, Inc. | Medical devices and applications of polyhydroxyalkanoate polymers |
Cited By (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP2221014B1 (en) | 2009-02-23 | 2015-05-20 | Inion Oy | Implant, implantation tool and kit |
US10010351B2 (en) | 2009-02-23 | 2018-07-03 | Inion Oy | Implant, implantation tool, kit and method |
WO2010117982A1 (en) * | 2009-04-06 | 2010-10-14 | Smith & Nephew, Inc. | Tissue graft anchor |
CN102596099A (en) * | 2009-04-06 | 2012-07-18 | 史密夫和内修有限公司 | Tissue graft anchor |
AU2010234613B2 (en) * | 2009-04-06 | 2015-12-17 | Smith & Nephew, Inc. | Tissue graft anchor |
CH702937A1 (en) * | 2010-04-13 | 2011-10-14 | Synergy Biosurgical Ag C O Confidas Treuhand Ag | Fixation implant. |
WO2011127614A1 (en) * | 2010-04-13 | 2011-10-20 | Synergy Biosurgical Ag | Fixation implant |
CN102905629A (en) * | 2010-04-13 | 2013-01-30 | 协同生物外科股份公司 | Fixation implant |
Also Published As
Publication number | Publication date |
---|---|
DE602008006181D1 (en) | 2011-05-26 |
WO2008130954A3 (en) | 2009-10-22 |
AU2008243035B2 (en) | 2013-09-12 |
EP2150288A2 (en) | 2010-02-10 |
US9770534B2 (en) | 2017-09-26 |
JP5680957B2 (en) | 2015-03-04 |
JP2010539998A (en) | 2010-12-24 |
AU2008243035A1 (en) | 2008-10-30 |
ATE505220T1 (en) | 2011-04-15 |
US20100145448A1 (en) | 2010-06-10 |
EP2150288B1 (en) | 2011-04-13 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
AU2008243035B2 (en) | Graft fixation | |
AU2012320238B2 (en) | Medical devices containing shape memory polymer compositions | |
AU2018327272B2 (en) | Fiber reinforced biocomposite threaded implants | |
AU736616B2 (en) | Improved bioabsorbable bone block fixation implant | |
EP1332730B1 (en) | Bone block fixation implant | |
US9308293B2 (en) | Multi-modal shape memory polymers | |
US20100318085A1 (en) | Internal fixation devices | |
EP2416735B1 (en) | Tissue graft anchor | |
WO2008112875A2 (en) | Internal fixation devices | |
EP1119317A1 (en) | Chute for endosteal ligament fixation |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
WWE | Wipo information: entry into national phase |
Ref document number: 12595114 Country of ref document: US |
|
WWE | Wipo information: entry into national phase |
Ref document number: 2008243035 Country of ref document: AU Ref document number: 2010504201 Country of ref document: JP |
|
NENP | Non-entry into the national phase |
Ref country code: DE |
|
WWE | Wipo information: entry into national phase |
Ref document number: 2008745909 Country of ref document: EP |