US20080269745A1 - Thermo-chemically activated intramedullary bone stent - Google Patents
Thermo-chemically activated intramedullary bone stent Download PDFInfo
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- US20080269745A1 US20080269745A1 US11/777,846 US77784607A US2008269745A1 US 20080269745 A1 US20080269745 A1 US 20080269745A1 US 77784607 A US77784607 A US 77784607A US 2008269745 A1 US2008269745 A1 US 2008269745A1
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- thermo
- chemically activated
- bone
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Abstract
Description
- This application claims the benefit of the following, which is incorporated herein by reference:
- Pending prior U.S. Provisional Patent Application No. 60/913,696, filed Apr. 24, 2007, which carries Applicants' docket no. OST-1 PROV, and is entitled THERMO-CHEMICALLY ACTIVATED INTRAMEDULLARY BONE STENT.
- 1. The Field of the Invention
- The present invention relates generally to orthopedic devices for the surgical treatment of bone fractures and, more particularly, to the fixation and stabilization of fracture sites with an intramedullary device that is deformable and conforms to the shape of the intramedullary canal.
- 2. The Relevant Technology
- Orthopedic medicine provides a wide array of implants that can be attached to bone to repair fractures. External fixation involves the attachment of a device that protrudes out of the skin, and therefore carries significant risk of infection. May fractures in long bones can be repaired through the use of bone plates, which are implanted and attached to lie directly on the bone surface. The bone plate then remains in the body long enough to allow the fractured bone to heal properly. Unfortunately, such bone plates often require the surgical exposure of substantially the entire length of bone to which the plate is to be attached. Such exposure typically results in a lengthy and painful healing process, which must often be repeated when the implantation site is again exposed to allow removal of the plate. There is a need in the art for implants and related instruments that do not require such broad exposure of the fractured bone, while minimizing the probability of infection by avoiding elements that must protrude through the skin as the bone heals.
- Various embodiments of the present invention will now be discussed with reference to the appended drawings. It is appreciated that these drawings depict only typical embodiments of the invention and are therefore not to be considered limiting of its scope. The drawings may not be to scale.
-
FIG. 1 is a perspective view of an intramedullary bone fixation device according to one embodiment of the invention, comprising a support structure which includes a cage and a plurality of rods, and a thermo-chemically activated thermoplastic matrix; -
FIG. 2 is a perspective view of the cage ofFIG. 1 ; -
FIGS. 3A-3I are perspective views of various embodiments of stent portions suitable for incorporation into the support structure ofFIG. 2 ; -
FIG. 4 is an enlarged perspective view of a first end of the cage ofFIG. 2 ; -
FIG. 5 is a perspective view of the rods ofFIG. 1 ; -
FIG. 6 is a perspective view of the thermoplastic matrix ofFIG. 1 ; -
FIG. 7 is a longitudinal cross-sectional view of a bone with an alternative embodiment of an intramedullary bone fixation device partially inserted into the intramedullary canal; -
FIG. 8 is a longitudinal cross-sectional view of a bone with the intramedullary bone fixation device ofFIG. 7 implanted inside a second intramedullary bone fixation device; -
FIG. 9A is an enlarged cross-sectional view of one section of the bone and intramedullary bone fixation devices ofFIG. 8 ; -
FIG. 9B is an enlarged cross-sectional view of another section of the bone and intramedullary bone fixation devices ofFIG. 8 ; -
FIG. 9C is an enlarged cross-sectional view of another section of the bone and intramedullary bone fixation devices ofFIG. 8 ; -
FIG. 10 is a perspective cutaway view of an alternative embodiment of an intramedullary bone fixation device comprising a cage, rods, sutures and a thermoplastic matrix; -
FIGS. 11A-11E are cross-sectional views of the intramedullary bone fixation device ofFIG. 10 , illustrating radial expansion of the device from a contracted state inFIG. 11A to a fully expanded state inFIG. 11E . -
FIGS. 12A-12E are cross-sectional views of an alternative embodiment of an intramedullary bone fixation device, illustrating radial expansion of the device from a contracted state inFIG. 12A to a fully expanded state inFIG. 12E . -
FIG. 13A is a perspective view of a support structure in a contracted state according to one alternative embodiment of the invention; -
FIG. 13B is a perspective view of the support structure ofFIG. 13A in an expanded state; -
FIG. 14A is a perspective view of a cage in a contracted state; -
FIG. 14B is an end view of the cage of 14A in a contracted state; -
FIG. 14C is a perspective view of a cage in an expanded state; -
FIG. 14D is an end view of the cage of 14C in an expanded state; -
FIG. 15 is a perspective view of a slotted support structure; -
FIG. 16A is a perspective view of a shaft portion of a mechanical expansion apparatus suitable for use with the device ofFIG. 1 ; -
FIG. 16B is a perspective view of the complete mechanical expansion apparatus ofFIG. 16A ; -
FIG. 17 is a longitudinal cross-sectional view of a bone with an intramedullary bone fixation device in a contracted state and a balloon expansion apparatus in the intramedullary canal of the bone, and a regulator apparatus; -
FIG. 18 is a longitudinal cross-sectional view of a portion of the bone ofFIG. 17 , with the intramedullary bone fixation device in a contracted state and a balloon expansion apparatus ofFIG. 17 ; -
FIG. 19 is a longitudinal cross-sectional view of the bone, intramedullary bone fixation device and balloon expansion apparatus ofFIG. 17 , with the balloon in an inflated state and the intramedullary bone fixation device in an expanded state; -
FIG. 20A is an enlarged cross-sectional view of one section of the bone and intramedullary bone fixation device ofFIG. 19 ; -
FIG. 20B is an enlarged cross-sectional view of another section of the bone and intramedullary bone fixation device ofFIG. 19 ; -
FIG. 20C is an enlarged cross-sectional view of another section of the bone and intramedullary bone fixation device ofFIG. 19 ; -
FIG. 21 is a longitudinal cross-sectional view of the bone, intramedullary bone fixation device and balloon expansion apparatus ofFIG. 17 , with the balloon in a deflated state and the and intramedullary bone fixation device in an expanded state, with the balloon expansion apparatus partially removed from the intramedullary bone fixation device; -
FIG. 22A is a perspective view of a telescoping bone fixation device in an extended state according to one alternative embodiment of the invention; -
FIG. 22B is a longitudinal cross-sectional view of a connection between two nesting components of the telescoping bone fixation device ofFIG. 22A ; -
FIG. 23 is a perspective view of a telescoping bone fixation device with mesh-like components and a thermoplastic matrix according to another alternative embodiment of the invention, in an extended state; -
FIG. 24 is a perspective view of a helically threaded telescoping bone fixation device according to yet another alternative embodiment of the invention, in a partially extended state; -
FIG. 25A is a perspective view of one nesting component of the helically threaded telescoping bone fixation device ofFIG. 24 ; and -
FIG. 25B is a perspective view of another nesting component of the helically threaded telescoping bone fixation device ofFIG. 24 . - Referring to
FIG. 1 , a perspective view illustrates an embodiment of an intramedullary bonefixation composite device 10. Thecomposite device 10 comprises a support structure II and a thermo-chemically activatedthermoplastic matrix 16. Thesupport structure 11 comprises acage 12, and at least onestiffening rod 14. Thecomposite device 10 is generally tubular in form and has alongitudinal axis 24 and atransverse axis 26. A hollowcentral core 18 extends the length of thedevice 10, surrounded by thecage 12 androds 14, which are embedded in thethermoplastic matrix 16. Anouter perimeter 22 bounds the outer surface of thecomposite device 10. Thecomposite device 10 is an implant which is able to transition from a contracted and flexible state for introduction into the intramedullary canal, to an expanded and hardened state providing rigid support and alignment for fixation of the surrounding bone, once implanted and allowed to expand to the perimeter of the canal. The thermoplasticity of thematrix 16 allows thecomposite device 10 to conform to the shape of the surrounding intramedullary canal at a first state, and harden in its conformed shape at a second state providing torsional, axial, and bending reinforcement of the bone fragments during bone healing. When contracted for insertion (or removal), adiameter 20 along thetransverse axis 26 of the device is reduced, and the length along thelongitudinal axis 24 of the device may be constant or increased. When expanded within the intramedullary canal, thediameter 20 is increased, and the length may be constant or decreased. - As seen in
FIG. 2 , thecage 12 is an elongated, generally web-like tube which allows radial expansion and contraction over at least part and preferably all of its length, and bending flexibility as bending loads are applied. Thecage 12 has afirst end 30, asecond end 32 and asleeve 34 which extends between the ends. Thesleeve 34 has anattachment portion 36 and a web-like stent portion 38. The cage is hollow and generally circular in cross-sectional shape, although the web-like construction allows the cross-sectional shape to vary to conform to the contours of the surrounding intramedullary canal. The shape of the intramedullary canal varies along its length, and its cross-sectional shape may be substantially circular, generally triangular or another shape. Thecage 12 may comprise a tubular woven or braided cage, a laser cut tubing cage, a machined cage, or a chemically etched tubing cage made from materials such as Nitinol, stainless steel, Co—Cr, Titanium alloys, Tantalum, plastic, polymer or other biocompatible materials, among others. In the embodiment depicted, thestent portion 38 comprises a majority of thesleeve 34. However, in other embodiments the stent portion may be a smaller proportion of the sleeve, or comprise the entire sleeve.Attachment portions 36 may be located at one, both, or neither of the ends of the sleeve, or intermittently along the sleeve length. - Referring to
FIG. 3 , possible configurations of the web-like structure of thestent portion 38 are shown, comprising examples of commercially available stent shapes. These figures show the approximate pattern of the web-like structure. These patterns are adaptable to a variety of lengths, diameters, density of repeatable patterns, wire thicknesses, web areas, and other structural characteristics such that the general stent shape can be configured to a particular bone morphology and size.FIG. 3A is representative of a Johnson and Johnson Palmaz-Schatz™ Version 2 stent.FIG. 3B represents a Medtronic Wiktor™ stent.FIG. 3C represents the general shape of a Schneider “Magic” Wallstent™ stent.FIG. 3D represents a Scimed NIR™ stent.FIG. 3E represents an Arterial Vascular Engineering (AVE™) Microstent.FIG. 3F is representative of a Biotronik Stent™.FIG. 3G is meant to represent the general shape and construct of a Johnson and Johnson Palmaz-Schatz™ stent.FIG. 3H represents a Global Therapeutics Freedom™ stent.FIG. 3I is drawn to represent the adaptable structure of a Scimed Radius™ stent which like all the previously presented representative figures can be configured to the length, diameter and size needed to conform to the intramedullary shape of a particular bone. The stent portion may also be configured with more than one pattern along its length or diameter if needed to better conform to the desired geometry. The stent portion need not be a commercially available stent; it may also have a unique configuration which is constructed from wire, woven, machined, laser cut, or chemically etched. -
FIG. 4 is an enlarged view of thefirst end 30, theattachment portion 36 and part of thestent portion 38 of thecage 12. Theattachment portion 36 comprisesstruts 40 which extend from thestent portion 38 and terminate atloops 42, which allow for the attachment of instruments for device placement, adjustment and removal. Other fasteners such as holes or hooks, among others, may be used instead of loops. Between thestruts 40 at thefirst end 30,linkages 44 connect each strut to the adjacent strut. The linkages allow for radial and longitudinal contraction and expansion of thestruts 40 and therefore thefirst end 30, as the device is contracted and expanded during implantation and removal. The web-like configuration of thestent portion 38 allows for radial and longitudinal contraction and expansion of the remainder of thecage 12. - Referring to
FIG. 5 , at least one, and optionally, a plurality, of stiffeningrods 14 are oriented parallel to the longitudinal axis of thecage 12 and are contained by the cage in such a way as to allow the stiffening rod(s) to move radially with the cage as the cage contracts and expands. Eachrod 14 has afirst end 50, asecond end 52 and ashaft 56. Eachrod 14 may have loops, holes, hooks or other attachment structures at thesecond end 52 to connect to second end ofcage 12. Therods 14 may be threaded loosely or otherwise linked into thestent portion 38 of thecage 12. Holes (not shown) may extend transversely through the rods, and individual webs of the stent portion may pass through the holes to retain the rods. Therods 14 may extend the full length of thecage 12, or preferably from thesecond end 32 of the cage to the upper end of thestent portion 38. The stiffeningrods 14 can be made from any biocompatible material such as stainless steel, cobalt chromium alloys, tantalum, zirconium alloys, titanium or titanium alloys, particularly beta titanium alloys. The stiffeningrods 14 can also be made from non-metal biocompatible materials such as PEEK, Acetal, bioabsorbable materials, ceramics and biocomposites. Each stiffeningrod 14 is sufficiently flexible to temporarily bend as the device (in a contracted state) is introduced into the intramedullary canal. Additionally, the rods may be knurled, threaded or otherwise treated to provide adhesion and interdigitation of the matrix and cage. Once thedevice 10 is inserted and expanded radially, therods 14 are aligned parallel to the longitudinal axis of the bone and line the inner surface of the canal, within the cage and matrix of the device. - The ratio of longitudinal contraction to radial expansion of the
composite device 10 varies depending upon the configuration of the stent portion of the cage, the length of the linkages, and the length and placement of the rods. Some embodiments have a low ratio, in which a small decrease in the length of the cage results in a large increase in the radial expansion (as measured by change in the core diameter 20). Other embodiments have a 1:1 ratio (a contraction in cage length results in an equal measurement of radial expansion), or a higher ratio, in which a large decrease in longitudinal contraction produces a small increase in radial expansion. The choice of embodiment will depend upon factors such as the length and diameter of the particular bone to be fixed, accessibility to the bone, and severity of the fracture, among others. - Referring to
FIG. 6 , thethermoplastic matrix 16 may be thermo-chemically activated, and may surround thesupport structure 11 ofFIG. 2 , or the support structure of any of the embodiments described below. Thematrix 16 comprises a material which has physical properties that change between a first and second state. For example, the material may be flexible and deformable at a first state and hard and more rigid at a second state. This can be accomplished by changing factors such as the molecular structure of chemical components of thematrix 16 from one state to another. Methods of changing the molecular structure of a material, and thus the physical properties of the material, include changing the temperature of the material, exposing the material to gamma radiation and altering the crosslinking bonds between molecular chains in the material, exposing the material to ultraviolet radiation causing the material to cure and harden, exposing the material to a second material allowing cross-linking and molecular bonding, allowing the material to harden over time by increasing the crystallinity within the molecular structure, and other methods that alter the bonding between the molecules in thematrix 16 material and correspondingly alter its material properties. - The
matrix 16 may comprise a thermoplastic biocompatible polymer or polymer blend comprising polymers such as polylactic acid (PLA), poly ε-caprolactone (PCL), trimethylene carbonate (TMC), polyglycolic acid (PGA), poly l-lactic acid (PLLA), poly d-l-lactide (PDLLA), poly-D,L-lactic acid-polyethyleneglycol (PLA-PEG) or other biocompatible polymers. Each of these polymers has a glass transition temperature Tg such that when raised to a temperature above its Tg, the polymer is rubbery, flexible and deformable. When lowered to a temperature below its Tg, the polymer is crystallized and substantially rigid. Each of these polymers or blends is capable of being transformed by the application of energy to a first thermo-chemical state, in which it is at a temperature above its glass transition temperature Tg. When, through dissipation of energy, the temperature is reduced to below Tg, the polymer or blend is at a second thermo-chemical state. These thermoplastic properties of the polymers allow them to be repetitively heated to above Tg, and subsequently cooled to below Tg, moving repeatedly between the first and second thermo-chemical states. - Preferred polymers have a glass transition temperature Tg that is above body temperature, but below the temperature known to cause thermal necrosis of tissues. A preferred blend is crystallized and substantially rigid at human body temperature, and has a Tg which ranges from about 10° C. above body temperature to about 35° C. above body temperature. This acceptable Tg range is between about 50° C. and about 80° C., and preferably between about 55° and about 65° C. Preferably, the
thermoplastic matrix 16 comprises a blend of polymers such as PCL and PLA, or PCL and PGA. Table 1 displays the melting points (Tm), glass transition temperatures (Tg) and thermal decomposition temperatures (Tdec) of selected synthetic absorable polymers. -
TABLE 1 Melting, glass transition and thermal decomposition temperatures of selected synthetic absorbable polymers. Polymer Tm (° C.) Tg (° C.) Tdec (° C.) PGA 230 36 260 PLLA 170 56 240 PLA — 57 — PCL 60 −62 — Polyglactin910 200 40 250 Polydioxanone 106 <20 190 Polyglyconate 213 <20 260 - Additional biocompatible polymers which may be included in the
matrix 16, individually or in a blend, comprise aliphatic polyesters including polyglycolide, poly(dl-lactide), poly(l-lactide), poly(δ-valerolactone), polyhydroxybutyrate; polyanhydrides including poly[bis(p-carboxyphenoxy)propane anhydride], poly(carboxy phenoxyacetic acid), poly(carboxy pheoxyvaleric acid); polyphosphazenes including aryloxyphosphazene polymer and amino acid esters; poly (ortho esters); poly(p-dioxane); poly(amino acids) including poly(glutamic acid-co-glutamate); erodable hydrogels; and natural polymers including collagen (protein) and chitosan (polysaccharide). - The
thermoplastic matrix 16 may further include at least one bioactive material to promote growth of bone material and accelerate healing of fractures. These bioactive materials include but are not limited to hydroxylapatite, tetracalcium phosphate, β-tricalcium phosphate, fluorapatite, magnesium whitlockite, β-whitlockite, apatite/wollastonite glass ceramic, calcium phosphate particle reinforced polyethylene, bioactive glasses, bioactive glass ceramics, polycrystalline glass ceramics, and polyethylene hydroxylapatite. - The
support structure 11 may be embedded in thethermoplastic matrix 16 through insert molding, pulltrusion, by dipping the support structure into the thermoplastic matrix material while it is at a temperature above Tg, or by other coating methods. A variety of different methods may alternatively be used to assemble thethermoplastic matrix 16 and thesupport structure 11. - Referring to
FIG. 7 , a longitudinal cross-section of a bone illustrates implantation of an intramedullary bonefixation composite device 710. The method illustrated inFIG. 7 may also be used for implantation ofcomposite device 10 and other devices according to alternative embodiments.Composite device 710 comprises asupport structure 711 and a thermo-chemically activatedthermoplastic matrix 716. Thesupport structure 711 comprises a stent-like cage 712 (not shown) and a plurality of rods 714 (not shown). - A
percutaneous portal 60 is created into theintramedullary canal 2, preferably in the proximal or distal metaphysial region of the bone. The opening may not be parallel to the longitudinal axis of the bone; it may be transverse or at an acute angle relative to the longitudinal axis of the bone. If necessary to open the canal space and prepare it for the implant, the canal is evacuated using a sequence of pulse lavage, brushing, and suction. Adelivery tube 62 may be advanced into thepercutaneous portal 60. Thecomposite device 710, in a lengthened and contracted state, is heated immediately prior to implantation to a first thermo-chemical state, so that thethermoplastic matrix 716 is above its glass transition temperature and is therefore plastic and rubbery enough to be flexed as it is introduced through the percutaneous portal and into the intramedullary canal. Heating of thecomposite device 710 to reach the first thermo-chemical state may be accomplished by means including soaking the implant in a hot saline bath, application of ultrasonic vibratory energy, application of radiant heat energy, use of a local radiation emitter (including ultraviolet, visible light, and/or microwave energy), use of a laser energy emitter, use of inductive heat energy, electrical resistive heating of the cage or the delivery instrument, or heating of an expansion apparatus, among others. - The
composite device 710 is inserted into thedelivery tube 62, pushed through the tube and advanced into theintramedullary canal 2 until thecomposite device 710 is contained within the confines of the canal. Optionally, thecomposite device 710 may be inserted directly through thepercutaneous portal 60 without passing through adelivery tube 62. A portion of thecomposite device 710 may be surrounded by aprotective sheath 749, which is positioned so that it covers thedevice 710 at the point of the bone fracture. Thedevice 710 is then expanded radially. As thesupport structure 711 expands, the stiffeningrods 714, thecage 712 andthermoplastic matrix 716 move radially outward and are eventually aligned along the wall of the intramedullary canal, parallel to the longitudinal axis of the bone. Thecomposite device 710 is allowed to cool to below the low glass transition temperature Tg, thus attaining the second thermo-chemical state, and thematrix 716 crystallizes. As the matrix crystallizes it conforms to the shape of the surrounding intramedullary canal, and thecage 712 and stiffeningrods 714 are fixed in thethermoplastic matrix 716 along the wall of the canal. The shape of the intramedullary canal can vary along the length of the bone, with the canal being generally circular in the diaphysial region near the midpoint of the bone and irregular in the metaphysial regions near the ends of the bone. Although thethermoplastic matrix 716 is in a generally tubular shape as thecomposite device 710 is inserted, the thermoplastic qualities of the matrix allow it to conform to the shape of the intramedullary canal around it, and it crystallizes in that shape, thus providing torsional strength and support to the surrounding bone. The ability of thethermoplastic matrix 716 to conform to the irregularities in the intramedullary canal allows thedevice 710, and the stabilized bone, to withstand greater torsional forces than would a device with a constant circular shape which did not conform to the canal. - Deformation and/or radial expansion and of the
composite device 710 to conform to the intramedullary canal can be accomplished in several ways. A deformation apparatus (such as those shown inFIGS. 16 and 17 ) may be introduced into the central core of thecomposite device 710 before or after it has been inserted into the intramedullary canal. The deformation apparatus is expanded, and forces expansion of thecomposite device 710 until it fills the confines of the canal. The deformation apparatus may comprise a heat source to raise the temperature of thethermoplastic matrix 716. Alternatively, thecage 712 may be constructed with an outward spring bias, introduced into the intramedullary canal and allowed to expand. In another embodiment which is described in detail below, a balloon apparatus (such as that shown inFIG. 17 ) is introduced into the central core of thecomposite device 710. As the balloon is inflated with heated gas or liquid, it expands, and consequently induces expansion of thecomposite device 710. Once the device is expanded, the balloon can be deflated and removed. It is appreciated that these deformation and expansion techniques and apparatuses may also be employed withcomposite device 10 and other embodiments of intramedullary bone fixation devices disclosed herein. - Referring to
FIG. 8 , a longitudinal cross-section shows twocomposite devices -
Composite device 750 comprises athermoplastic matrix 756, which surrounds a support structure which includes acage 752 and a plurality ofrods 754. The configuration ofmatrix 756,cage 752 androds 754 may be identical to that ofcomposite device 710. Prior to implantation, thecomposite device 750 is partially radially expanded. Thecomposite device 710 is contracted, and slid into a hollowcentral core 758 of thecomposite device 750. Together, the twodevices thermoplastic matrices devices composite device 710 is expanded using one of the techniques previously described. As the innercomposite device 710 expands, it pushes radially against the outer disposedcomposite device 750, forcing it to expand radially until it contacts and conforms to the wall of the surrounding intramedullary canal. - Alternatively,
composite devices Composite device 750 may be introduced first, heated and expanded.Composite device 710 is then introduced into the hollowcentral core 758 ofcomposite device 750 after is it in the intramedullary canal. After bothdevices composite device 710 is heated and expanded, pushing radially against the outercomposite device 750. - The
thermoplastic matrix 716 surrounding thecomposite device 710 may contact and conform to thethermoplastic matrix 758 of thecomposite device 750. The twodevices - Referring to
FIGS. 9A-9C , three cross-sectional views along different parts of the bone depicted inFIG. 8 are shown, withdevices FIG. 9A , theintramedullary canal 2 is relatively wide and circular in shape, resulting in a wide circular centralhollow core 718. Also, thethermoplastic matrices rods devices FIG. 9B , at this point along the bone the intramedullary canal is smaller in diameter and more irregular in shape. The thermoplasticity of thematrices devices FIG. 9C , at this point along the bone the intramedullary canal is narrow in cross-section and substantially triangular in shape. According, thethermoplastic matrices rods devices - Referring to
FIG. 10 , an alternative embodiment of an intramedullary bone fixation composite device is shown in a cutaway view.Composite device 810 comprisessupport structure 811 and a thermo-chemically activatedthermoplastic matrix 816.Support structure 811 comprises acage 812, a plurality ofrods 814, and a plurality ofsutures 815 which connect the cage to the rods. The thermo-chemically activatedmatrix 816 surrounds thecage 812,rods 814 andsutures 815 such that they are embedded in the matrix. Thesutures 815 are interwoven around and between thecage 812 and therods 814 to connect thecage 812 to therods 814 in a manner that allows regulated movement of thecage 812 and therods 814 relative to one another. - Alternately, the sutures may be knit into a sleeve that holds the array of rods and surrounds the cage. The interweaving may be constructed in such a way as to allow radial expansion of the
cage 812 and therods 814 from a contracted position in which thecage 812 is lengthened and therods 814 are tightly packed together, to an expanded position in which thecage 812 is shortened, radially expanded and therods 814 are arrayed around the cage with relatively more space between each rod. Thecage 812 may comprise web-like stent material similar to stents depicted inFIGS. 3A-31 , or may comprise another woven or laser cut stent-like material. Therods 814 may be similar to therods 14 depicted inFIG. 5 . The thermo-chemically activatedthermoplastic matrix 816 may be similar to the thermo-chemically activatedthermoplastic matrix 16 described previously and depicted inFIG. 6 . The sutures may comprise any of several commercially available sutures, including Dyneema Purity® Ultra High Molecular Weight Polyethylene (UHMWPE), or bioabsorbable multifilament polylactic acid (PLA) sutures such as PANACRL™, among others. -
Composite device 810 may be introduced into the intramedullary canal in the same manner as previously described forcomposite device 710. Energy is applied tocomposite device 810, heating it until the thermo-chemically activatedmatrix 816 reaches the first thermo-chemical state and is flexible and rubbery. Thecomposite device 810 is contracted so that it is sufficiently flexible to be inserted into the intramedullary canal through an opening in the bone, an opening which may not be parallel to the intramedullary canal. Thecomposite device 810 is inserted into the canal and expanded by one of the expansion methods previously described. When the device is expanded within the intramedullary canal, the thermo-chemically activatedmatrix 816 contacts and is conformed to the walls of the intramedullary canal. Thedevice 810 is allowed to cool and the thermo-chemically activatedmatrix 816 attains the second thermo-chemical state, and hardens sufficiently to fix thesupport structure 811 in its expanded position within the intramedullary canal. - Referring to
FIGS. 11A-11E , a series of five cross-sectional views illustrate the expansion ofcomposite device 810 from a contracted position to a fully expanded position. Beginning withFIG. 11A , a hollowcentral core 818 ofcomposite device 810 is substantially circular. Ascomposite device 810 expands, thecage 812 and the hollowcentral core 818 increase in diameter and thethermoplastic matrix 816 stretches to fit around thecage 812. At the most expanded state illustrated inFIG. 11E , thethermoplastic matrix 816 is substantially thinner than at the most contracted state. InFIG. 11A , the array ofrods 814 are relatively closely packed near one another; inFIG. 11E they are spread apart and are substantially equidistantly arrayed about the hollowcentral core 818. -
FIGS. 12A-12E illustrate an alternative embodiment of a composite device in five cross-sectional views. Similar tocomposite device 810,composite device 910 comprises a support structure 911 with acage 912, a plurality ofrods 914, and a plurality ofsutures 915 which connect the cage to the rods. A thermo-chemically activatedthermoplastic matrix 916 surrounds thecage 912,rods 914 andsutures 915 such that they are embedded in the matrix. As most clearly seen inFIG. 12C , in this embodiment, thethermoplastic matrix 916 is configured in a series offolds 917, as compared to the circular configuration seen forthermoplastic matrix 816 inFIG. 11C . The folded configuration of thethermoplastic matrix 916 results in a star-shaped hollowcentral core 918. The star-shaped hollowcentral core 918 is smaller in terms of cross-sectional open space, as much of the space is taken up by the folds of thethermoplastic matrix 916. Therefore, thethermoplastic matrix 916 is thicker in this embodiment than in other embodiments such asdevice 810. Thus, as seen inFIG. 12E , the fully expandedcomposite device 910 has a thicker thermoplastic matrix, which may result in additional support for the surrounding bone during the healing process. -
Composite device 910 may be introduced into the intramedullary canal in the same manner as previously described forcomposite devices composite device 910, heating it until the thermo-chemically activatedmatrix 916 reaches the first thermo-chemical state, and is flexible and rubbery. Thecomposite device 910 is contracted into the deeply folded position seen inFIG. 12A , so that it is sufficiently flexible to be inserted into the intramedullary canal through an opening in the bone. Thecomposite device 910 is inserted into the canal and expanded by one of the expansion methods previously described. A specifically configured implant expander such as a star-shaped balloon expansion device (not shown) may be used to expand thedevice 910. When the device is expanded within the intramedullary canal, the thermo-chemically activatedmatrix 916 contacts and is conformed to the walls of the intramedullary canal. Thedevice 910 is allowed to cool and the thermo-chemically activatedmatrix 916 attains the second thermo-chemical state, and hardens sufficiently to fix thecage 912 androds 914 in their expanded positions within the intramedullary canal. In the case of a larger bone, twocomposite devices 910 may be deployed, one inside the other, to provide additional support to the bone. - Referring to
FIGS. 13A and 13B , one alternative embodiment of asupport structure 71 suitable for use in an intramedullary bone fixation device has an hourglass shape. In the context of the present invention, an hourglass shape is a generally longitudinal, columnar shape in which the two end portions of the column are wider in diameter than a middle portion of the column. Thesupport structure 71 comprises acage 72 androds 14. In this embodiment, the diameters of cage ends 74, 76 are greater than the diameter of acage sleeve 78. In order to clearly view the configuration of cage and rods, a thermoplastic matrix is not shown. A matrix similar to that of thethermoplastic matrix 16 of FIG. I may be used in conjunction withsupport structure 71, or it may have a different configuration. The hourglass shape enables thetubular support structure 71 to conform to the contours of the intramedullary canal of a long bone, in which the metaphysial regions at the ends of the bone are irregular and may be greater in diameter than the diaphysial region near the midpoint of the bone. In the embodiment depicted, the hourglass shape is achieved by the particular threading of the rods within the stent portion of the cage. At the first 74 and second 76 ends, therods 14 are contained within the confines of thecage 72; toward the center of thesleeve 78, the cage is contained within the circle of therods 14. InFIG. 13A , thesupport structure 71 is shown in the contracted state (for insertion or removal); inFIG. 13B , the expanded state is shown. Thesupport structure 71 may be inserted in the same manner as described previous forsupport structure 11, and the same expansion methods described previously may be used to expand thesupport structure 71. - One alternative embodiment of an intramedullary bone fixation device (not shown) comprises a laser-cut cage which is constructed with an outward spring bias. In this embodiment, the device is compressed prior to implantation by holding the rods steady and pulling longitudinally on the cage. The web-like configuration of the cage permits the cage to lengthen while simultaneously its core diameter contracts, enabling the device to be narrow and flexible enough for insertion. The device is introduced into the intramedullary canal and the cage is released. Upon release, the outward spring bias of the cage causes the cage to expand radially and simultaneously shorten. Radial expansion continues until the outer perimeter of the device contacts the inner wall of the intramedullary canal. The web-like configuration of the cage also allows it to conform to variations in the geometry of the intramedullary canal. This embodiment may also include the thermoplastic matrix, wherein prior to the compression step described above, the thermoplastic matrix is heated to the first thermo-chemical state, so it is flexible as the device is compressed, inserted and expanded. After insertion and radial expansion, the energy is allowed to dissipate and the thermoplastic matrix attains the hardened second thermo-chemical state.
- Referring to
FIGS. 14A through 14D , another alternative embodiment of the invention comprises a cage with an outward spring bias, which may be used in conjunction with a thermoplastic matrix such as that depicted inFIGS. 1 and 6 .FIG. 14A is a perspective view of acage 112, cut with a plurality of accordion-type folds 114 which unfold as the cage expands radially. Alternating with thefolds 114 arelongitudinal ribs 116, and a hollowcentral core 115 extends the length of thecage 112. Eachrib 116 has a longitudinal channel I 18 which may hold a stiffening rod. The cage may be laser-cut or machined from metal, or may comprise a plastic material or a thermo-chemically activated thermoplastic matrix material, as described above. Thecage 112 may have a straight shape with a constant diameter, or may have an hourglass shape in which the two ends are wider than the central section. Other shapes may alternatively be used for different bone morphologies. -
FIG. 14B is an end view of thecage 112 in a compressed state, showing the tight compaction of the folds 1 4 andribs 116.FIG. 14C is a perspective view of thecage 112 after radial expansion, andFIG. 14D is an end view of the expandedcage 112. In this embodiment, the support structure can be compressed for implantation by a binding material which is wrapped or tied around the compressed cage. After insertion into the intramedullary canal, the cage is released by cutting or removal of the binding material. Once released, the outward spring bias of thecage 112 causes thecage 112 to expand radially in the same manner as described for the previous embodiment. - In another embodiment the support structure may be monolithic; that is, formed as a single unit. The cage and rods are formed together, such as by a machining process and remain connected together. Referring to
FIG. 15 , an embodiment of amonolithic support structure 111 is shown in an expanded state. This embodiment has no channels for rods, but consequently hasribs 117 between the accordion folds 114 which are solid and comprise more material, thus providing rigidity similar to the rods of other embodiments. Between theribs 117, the accordion folds 114 have a plurality ofslots 119. Theslots 119 allow for less material and thus more flexibility of the support structure when compressed. Additionally, when compressed, the tight packing of theribs 117 between the accordion folds 114 allows thesupport structure 111 to flex sufficiently for insertion into the intramedullary canal. Themonolithic support structure 111 may be used in conjunction with a thermoplastic matrix. Contraction, insertion and expansion of themonolithic support structure 111 may be in the same manner as described previously for thecage 112. - In another embodiment of the invention, at least two support structures and/or cages such as those depicted in
FIGS. 14 and 15 can be nested, one within the other. Afirst support structure 111 orcage 112 embedded in thethermoplastic matrix 16 is heated to the first thermo-chemical state, compressed, inserted into the intramedullary canal, and expanded. Asecond support structure 111 orcage 112 embedded in thethermoplastic matrix 16 is similarly compressed and inserted into thecentral core 115 of the first support structure. When thesecond structure 111 orcage 112 expands, it pushes radially against thefirst structure 111 orcage 112. As described previously for other embodiments, thethermoplastic matrix 16 surrounding the first support structure conforms to the contours of the intramedullary canal. Within the first support structure, thethermoplastic matrix 16 surrounding the second support structure conforms to the surrounding first support structure. The matrix material surrounding both the first and second structures cools to the second thermo-chemical state and crystallizes. This double layer of matrix material and support structures provides enhanced support and rigidity to the surrounding bone. - The
cage 112 andsupport structure 111 embodiments depicted inFIGS. 14 and 15 can alternatively be constructed without an outward spring bias. Thecompressed cage 112 orsupport structure 111 may be surrounded by thethermoplastic matrix 16. As described previously, the device is heated so the thermo-plastic matrix 16 reaches the first thermo-chemical state and the device is flexed and inserted into the intramedullary canal. In this case, an expansion apparatus or balloon mechanism as previously described, or other expansion mechanism is inserted into thecentral core 115 and used to expand the device after it is implanted. Once the device is expanded, energy dissipates into the surrounding tissue, the matrix attains the second thermo-chemical state, and thecage 112 or support structure 1 is fixed within the cooled, crystallizedmatrix 16. The expansion apparatus, balloon mechanism, or other expansion mechanism may then be removed from thecentral core 115. - One alternative embodiment of an intramedullary bone fixation composite device (not shown) comprises a thermoplastic matrix which is not continuous along the entire length of the corresponding cage or support structure. In this embodiment, the matrix comprises at least two separate tube-like portions, each of which surrounds one end of the cage or support structure and extends partway along the sleeve. This discontinuous configuration of the matrix contributes to an hourglass shape and allows less matrix material to be used. This matrix configuration can be used with either a cage with an outward spring bias, or with a cage with no outward spring bias.
- Another alternative embodiment of an intramedullary bone fixation composite device (not shown) comprises a support structure which comprises at least one rod, and no cage. Prior to implantation, the matrix is heated to the first thermo-chemical state and formed into a tubular shape around the rods, which are subsequently embedded in the matrix. The device is flexed and inserted into the patient. While the matrix is still in the first thermo-chemical state, an expansion apparatus or balloon is inserted into the center of the tubular device and used to expand the device within the intramedullary canal. As the device expands, the rods and the matrix material are pushed radially to the inner wall of the intramedullary canal. After expansion, the device is allowed to cool to the second thermo-chemical state, and the matrix hardens, fixing the rods in their positions around the inner wall of the canal.
- Another alternative embodiment of an intramedullary bone fixation device (not shown) comprises a support structure which comprises a cage manufactured of the thermoplastic matrix material, and rods. During manufacture the matrix material is heated above its Tg and extruded into a cage-like form. During or after extrusion the rods are interwoven, braided in, or otherwise attached as described previously. To implant the device, the device is heated above the Tg of the matrix to attain the first thermo-chemical state, contracted, flexed, inserted and expanded as described previously.
-
FIGS. 16A and 16B illustrate an implant expansion device which may be used to deform and expand several of the intramedullary bone fixation devices described previously, such ascomposite device 10,composite devices support structure 71, or other devices which incorporate a cage or support structure without an outward spring bias. Amechanical expansion apparatus 500 is longitudinally insertable into the central core of the intramedullary bone fixation device. As seen inFIG. 16A , themechanical expansion apparatus 500 has ashaft 514, which extends from afirst end 510 to asecond end 512. Anadjustment nut 516 is threaded onto a threadedportion 515 of theshaft 514, adjacent thefirst end 510. A cone-shapedfirst expander guide 518 is also threaded onto the threadedportion 515 of theshaft 514, on the opposite side of theadjustment nut 516 from thefirst end 510. Thesecond end 512 of theshaft 514 terminates in a cone-shapedsecond expander guide 519. Theshaft 514 comprises a metallic material, and is sufficiently thin and flexible to be inserted into the central core of an intramedullary bone fixation while the device is in the intramedullary canal of a bone in a patient. - Referring to
FIG. 16B , strung on thecentral shaft 514 and listed in their order of occurrence from thefirst expander guide 518 to thesecond expander guide 519 are: afirst expander segment 520, a plurality ofcore segments 522, acentral segment 524, another plurality ofcore segments 522, and asecond expander segment 526. Thecore segments 522 and thecentral segment 524 comprise a relatively rigid material, while theexpander segments first expander segment 520 surrounds a portion of thefirst expander guide 518 in a sleeve-like manner, and thesecond expander segment 526 similarly surrounds a portion of thesecond expander guide 519 in a sleeve-like manner. Thecore segments 522,central segment 524, andexpander segments shaft 514 with space between each segment, so that the apparatus can flex while being inserted into the central core of the intramedullary bone fixation device. - After the intramedullary bone fixation device with a thermoplastic matrix (not shown) is placed in the intramedullary canal, the
mechanical expansion apparatus 500 may be inserted through the delivery tube 62 (not shown) into the central core of the intramedullary bone fixation device. Then theadjustment nut 516 is turned, forcing thefirst expander guide 518 to advance along theshaft 514 toward thesecond expander guide 519 at thesecond end 512. Thefirst expander segment 520,core segments 522,central segment 524, andsecond expander segment 526 are compressed together as they are held between the first and second expander guides 518, 519. The rubbery,flexible expander segments expander segments expansion apparatus 500 may be kept in the central core of the intramedullary bone fixation device until the thermoplastic matrix cools to the second thermo-chemical state. Theexpansion apparatus 500 is contracted by turning theadjustment nut 516 in the opposite direction, and theapparatus 500 is then removed from the central core. - The
expansion apparatus 500 may optionally include a heating element. In this configuration, it can heat the thermoplastic matrix of an intramedullary bone fixation device while in a patient, in order to adjust the conformity of the matrix within the intramedullary canal. - Referring to
FIGS. 17-21 , an alternative method to deform and expand an intramedullary bone fixation device comprises an implant deformer which is a balloon expansion apparatus. As seen inFIG. 17 , aballoon expansion apparatus 600 configured to fit within acomposite device 10 in the intramedullary canal of a bone comprises anelastic bladder 602 with anopening 604. A set of flexible hoses comprising aninput hose 606 and anoutput hose 608 are configured to extend from aregulator apparatus 610, through theopening 604 and into theelastic bladder 602. Theregulator apparatus 610 is external to the patient, and comprises a pump to regulate flow, and a temperature regulator to regulate the temperature, of liquid which can flow into and out of theelastic bladder 602.FIG. 17 depicts the hoses adjacent and parallel to one another; however they may be configured in alternative arrangements, including a concentric arrangement in which one hose surrounds the other. Thehoses bladder 602. - Referring to
FIG. 18 , acomposite device 710 with aballoon expansion apparatus 600 already inserted into thecentral core 718 is introduced into the intramedullary canal of a bone. Introduction into the bone can be through the method described previously, in which the composite device (with the balloon apparatus in the central core) is heated so that the matrix attains the first thermo-chemical state. Thecomposite device 710 plusballoon apparatus 600 are flexed and introduced into the intramedullary canal through thepercutaneous portal 60. A delivery tube 62 (not shown) may optionally be used during the introduction and expansion procedures. Theinput 606 andoutput 608 hoses are inserted through theballoon opening 604 ideally before thecomposite device 710 plusballoon apparatus 600 are introduced into the intramedullary canal, but can optionally be inserted into theballoon opening 604 after introduction into the intramedullary canal. Aprotective sheath 49 may surround thecomposite device 710 at the location of the bone fracture. - Referring to
FIG. 19 , after thecomposite device 10 plusballoon apparatus 600 are within the intramedullary canal, inflation of thebladder 602 may begin. The external regulator apparatus 610 (not shown) pumps heated liquid such as water or saline solution, among others, through theinput hose 606 into theelastic bladder 602. The heat of the liquid maintains thethermoplastic matrix 716 of thecomposite device 710 at the deformable first thermo-chemical state. As the heated liquid fills thebladder 602, the bladder expands. Contained within thecomposite device 710, thebladder 602 eventually pushes outward, inducing radial expansion of thecomposite device 710. As described previously, cage and rod components of thesupport structure 711 are connected in a web-like construction which allows them to expand radially. Thethermoplastic matrix 716 surrounding thesupport structure 711 is at the heated first thermo-chemical state and is pushed radially by the expanding support structure, conforming to the surrounding intramedullary canal walls. The flexible, rubbery character of the matrix allows it to fit into the natural morphological variations in the wall of the intramedullary canal. A mesh-like end cap 746 on asecond end 732 of thecomposite device 710 prevents theelastic bladder 602 from escaping or ballooning out of thesecond end 732. Theoutput hose 608, which terminates at a location different from that of theinput hose 606, allows liquid to flow out of theballoon apparatus 600. Theregulator apparatus 610 maintains the flow, temperature and pressure of the liquid. -
FIGS. 20A-20C display cross-sections of the bone and thecomposite device 710 at three different locations along the length of the bone shown inFIG. 19 . At cross-section A-A inFIG. 20A , the cross-sectional shape of the intramedullary canal is relatively circular. Thedevice 710 has expanded to the wall of the canal, thematrix 716 is relatively thin, and therods 714 are spaced relatively far apart. At cross-section B-B inFIG. 20B , the canal is smaller and more rectangular in shape than at cross-section A-A. However, the deformable nature of thematrix 716 allows the matrix and the entirecomposite device 710 to expand differentially and conform to this variation in shape of the intramedullary canal. At cross-section C-C inFIG. 20C , the cross-sectional shape of the intramedullary canal is relatively smaller, and has a triangle-like shape. Again, thematrix 716 and thecomposite device 710 can conform to this irregular shape. Therods 714 are relatively closer together and thematrix 716 is relatively thicker. The ability of thecomposite device 710 to closely conform to the confines of the intramedullary canal allows the device to withstand greater torsional forces than would a device with a constant circular shape which did not conform to the canal. - Referring to
FIG. 21 , theballoon expansion apparatus 600 is depicted being withdrawn from thecomposite device 710. After expansion of theelastic bladder 602 is accomplished as described previously, the liquid in theelastic bladder 602 may be cooled by pumping cool liquid in throughinput hose 606 and withdrawing warmer liquid throughoutput hose 608 until a consistently cooler liquid is in thebladder 602. The cooler liquid in the bladder absorbs thermal energy from thematrix 716, allowing it to cool and transform from the flexible first thermo-chemical state to the hardened second thermo-chemical state. Once thecomposite device 710 has thus cooled and hardened, the remaining liquid may be pumped out of theelastic bladder 602, and theballoon expansion device 600 is pulled out ofcomposite device 710 through thepercutaneous portal 60. - A protective, tubular insertion sheath (not pictured) may surround all or a portion of any of the above-described intramedullary bone fixation devices during the implantation procedure, and may optionally be removed following implantation. The insertion sheath may be very thin, and may prevent portions of the support structure or matrix from snagging on or scratching the intramedullary canal, or portions of the fractured bone. Once the device is inserted, the sheath may be removed by being pulling the sheath out through the delivery tube, while leaving the device behind.
- With any embodiment of the device, after insertion of the device but before conclusion of the implantation procedure, x-ray, fluoroscopy, or other radiographic methods may be implemented to assess the alignment of the device relative to the bone. If alignment is unsatisfactory, a heating element (not shown) or a heatable expansion device such as the
balloon apparatus 600 ormechanical expansion apparatus 500 as described previously may be introduced into the central core. The device is heated so the thermoplastic matrix again reaches first thermo-chemical state, and the device may then be removed and reinserted or otherwise adjusted until a satisfactory alignment is achieved. The device is allowed to cool, so the thermoplastic matrix returns to the second thermo-chemical state through the natural dissipation of energy into the surrounding tissue. - Post-implantation, the device may be removed if desired. The method of removal will vary, depending on the state of the decomposition of the biocompatible thermoplastic matrix. If the thermoplastic matrix is still intact, a percutaneous portal may be opened and a tube may be inserted. The tube may be the same as or similar to the
delivery tube 62 described previously. A heating element or heatable expansion apparatus such as themechanical expansion apparatus 500 orballoon expansion apparatus 600 is introduced into the central core, and the device is heated until the matrix reaches the first thermo-chemical state, above the glass transition temperature. The heat source is removed; the device may be contracted by holding the rods steady and pulling longitudinally on the cage. The device may be removed through the delivery tube, or directly through the percutaneous portal. If the thermoplastic matrix has been sufficiently absorbed so that it is no longer intact, no heating is required; the device is contracted and removed. - Another embodiment of the invention (not shown) comprises a support structure and an alternative form of the thermoplastic matrix, comprising an injectable form of a synthetic biodegradable polymer, poly-D,L-lactic acid-polyethyleneglycol (PLA-PEG). This biodegradable composite is temperature-sensitive so that when it is heated it takes on a liquid, semi-solid form and following injection, cools and becomes semi-solid. A structure such as
support structure delivery tube 62 into the central core. The liquid PLA-PEG flows through the web-like support structure, filling the canal and surrounding the support structure. The protective sheath prevents the PLA-PEG from contacting the fractured area of the bone. The PLA-PEG is allowed to cool and harden, and provides rigid support around the structure. - Referring to
FIG. 22A , a perspective view shows another embodiment of the invention, comprising a telescopingintramedullary fixation device 210. This device comprises acentral wire 212 surrounded by a series of five tubular nesting components 213-217. Each tubular nesting component is substantially the length of theentire device 210 when all components are nested together, and each successive nesting component is slightly wider in diameter than the component it surrounds. Other embodiments of the telescopingintramedullary fixation device 210 may have fewer, or more, than five nesting components. Thecentral wire 212 may have a solid core and may not be tubular, but is slender and thus sufficiently flexible to be inserted into the intramedullary canal. The nesting components 213-217 may comprise metal, a biocompatible polymer material, or a mesh-like stent material (such as those depicted inFIG. 3 ), and may be embedded in a thermoplastic matrix material.FIG. 22A displays thetelescoping device 210 in a fully extended or telescoped position; however when completely implanted in a patient thedevice 210 is in a collapsed position in which the nesting components are concentrically nested together. - The
first nesting component 213 surrounding thecentral wire 212 is slightly wider in diameter than thecentral wire 212. Each successive nesting component 214-217 is slightly wider than the preceding one, and as the nesting components increase in diameter, the width of the wall of the component may decrease so that each nesting component is still flexible enough to be inserted into the canal. The wall thickness of each of the nesting components 213-217 may advantageously be selected such that the nesting components 213-217 are all nearly equally flexible. According to one alternative embodiment (not shown), the nesting components do not have solid walls but have slots in the walls to increase flexibility. - In a patient, the
central wire 212 may first be inserted into the intramedullary canal. Then, successive nesting components 213-217 with increasing diameters are introduced into the intramedullary canal. Thenesting component 213 with the smallest diameter is slid in around thecentral wire 212; thenesting component 214 with the next largest diameter is slid in surrounding thefirst nesting component 213, and the remaining nesting components 215-217 are inserted in a similar fashion. Thelargest nesting component 217 fits just inside the walls of the canal. After the components are inserted and collapsed together, an injectable, hardenable polymer such as bone cement or a biocompatible polymer such as PLA-PEG may be introduced into the canal to fill any spaces between thelargest nesting component 217 and the wall of the canal. Thelargest nesting component 217 may have asheath 219 which prevents the polymer from accessing the fractured area of the bone, as described previously. The nested set of nesting components 213-217 has a combined strength and rigidity which exceeds that of any of the individual nesting components, and thedevice 210 provides strength and support during bone healing. -
FIG. 22B is an enlarged, stylized cross-sectional view of the connection betweennesting components Nesting component 217 has afirst end 230 with an inward-projectingfirst lip 234. The nextsmallest nesting component 216 has asecond end 232 with an outward-projectingsecond lip 236. The projectinglips largest nesting component 217 away from the bone cement.Nesting component 217 is pulled out first, and its inwardly-projectinglip 234 hooks the outwardly-projectinglip 236 of the nextlargest nesting component 216, and causes it to be pulled out next, followed by the nextlargest nesting component 215, until all the nesting components 213-217 are pulled out. Thecentral wire 212 is removed separately after all the nesting components are removed. - Referring to
FIG. 23 , another embodiment of a telescoping fixation device is shown in an extended state. In this embodiment,telescoping fixation device 310 comprises a series of nesting components 313-317, each of which comprises a mesh-like stent portion embedded inthermoplastic matrix material 318 similar to that of thethermoplastic matrix 16 ofFIGS. 1 and 6 . Each nesting component 313-317 is substantially the length of theentire device 310 when all components are nested together. Prior to implantation, thedevice 310 is heated as described previously so that thethermoplastic matrix material 318 reaches the first thermo-chemical state, and is rubbery and flexible. Thedevice 310 is telescoped out into an extended configuration, and introduced into the intramedullary canal through an opening transverse to the longitudinal axis of the bone. Thecentral wire 312 is introduced first, and the adjacent and smallest nestedcomponent 313 is inserted so it nests around the central wire. The next smallest nestedcomponent 314 is nested about the smallest nestedcomponent 313, and so on until all the remaining nested components 315-317 are introduced into the intramedullary canal and nested together. Thedevice 310 is allowed to cool so that energy dissipates into the surrounding tissue, and thethermoplastic matrix material 318 of each nesting component 313-317 reaches the second thermo-chemical state, and hardens. - Referring to
FIG. 24 , another alternate embodiment of a telescoping fixation device is shown in a partially extended state. In this embodiment,telescoping fixation device 410 comprises a series of nesting components 413-417, which are helically threaded so that during implantation each nesting component is threaded onto the preceding smaller component. The direction of the threading on each nesting component may alternate, so that each nesting component is threaded onto the next nesting component in the opposite direction from the previous one. Each nesting component 413-417 is substantially the length of theentire device 410 when all components are nested together. As withdevices - Similar to the
telescoping fixation devices device 410 has acentral wire 412 which is initially inserted into the intramedullary canal through adelivery tube 62 or similar interface. The first nesting component 413 is slid in around the central wire. The first nesting component 413 is tubular in form has a clockwisehelical protrusion 420 which protrudes on the outside of the tube, winding in a clockwise direction along the length of the nesting component 413. - Referring to
FIGS. 25A-25B , two adjacent helically threaded nesting components have threading configurations which wind in opposite directions. As seen inFIG. 25A , thesecond nesting component 414 has a clockwisehelical slot 422 which winds clockwise along its length, and a counter-clockwisehelical protrusion 421 which winds counter-clockwise along its length. Asnesting component 414 is inserted into the intramedullary canal, it is twisted clockwise so that its clockwisehelical slot 422 fits over the clockwisehelical protrusion 420 on the first nesting component 413. As seen inFIG. 25B , thethird nesting component 415 has a counter-clockwisehelical slot 423, and a clockwisehelical protrusion 420. It is inserted and threaded onto thesecond nesting component 414 in a counter-clockwise fashion, so that its counter-clockwisehelical slot 423 engages with the counter-clockwisehelical protrusion 421 on thesecond nesting component 414. Each remaining nesting component is threaded clockwise or counter-clockwise to engage with the smaller component nested inside of it. Theoutermost nesting component 417 may or may not have a helical protrusion. - The helical threading system varies in direction so that the entire device will not be loosened when the
outermost component 417 is turned in one direction. In addition, this bi-directional threading system adds overall torsional strength to thetelescoping fixation device 410, since a twisting force in one direction will not disengage all the threading on the nesting components. - The
telescoping fixation device 410 may be used in conjunction with an injectable hardenable polymer, such as bone cement or a biocompatible polymer such as PLA-PEG, among others. Thefixation device 410 may be implanted as described previously, and the injectable polymer may then be injected into the intramedullary canal around the periphery of the device, to fix the device in place. Theoutermost nesting component 417 may have aprotective sheath 419 which prevents the polymer from accessing the fractured area of the bone, as described previously. Removal of thedevice 410 is accomplished by breaking the device away from the polymer as described previously, then unthreading and removing each component 413-417 in a clockwise or counter-clockwise direction, beginning with theoutermost component 417 and proceeding inward. - The present invention may be embodied in other specific forms without departing from its spirit or essential characteristics. It is appreciated that various features of the above-described examples can be mixed and matched to form a variety of other alternatives. For example, support structure and matrix materials and configuration features can vary, as can the method used to expand the device. As such, the described embodiments are to be considered in all respects only as illustrative and not restrictive. The scope of the invention is, therefore, indicated by the appended claims rather than by the foregoing description. All changes which come within the meaning and range of equivalency of the claims are to be embraced within their scope.
Claims (44)
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US12/027,629 US20080269749A1 (en) | 2007-04-24 | 2008-02-07 | Thermo-Chemically Activated Implantable Apparatus and Method |
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US13/423,914 US8834468B2 (en) | 2007-04-24 | 2012-03-19 | Bone stabilization device and method |
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US11/777,872 Abandoned US20080269746A1 (en) | 2007-04-24 | 2007-07-13 | Conformable intramedullary implant with nestable components |
US12/027,629 Abandoned US20080269749A1 (en) | 2007-04-24 | 2008-02-07 | Thermo-Chemically Activated Implantable Apparatus and Method |
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US14/220,132 Expired - Fee Related US9421045B2 (en) | 2007-04-24 | 2014-03-20 | Bone stabilization device and method |
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Cited By (48)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20080269776A1 (en) * | 2007-04-24 | 2008-10-30 | Osteolign | System and Method for Guidance and Implantation of Implantable Devices |
US20100179549A1 (en) * | 2007-02-23 | 2010-07-15 | Zimmer, Gmbh | Implant for fracture treatment |
US20100241229A1 (en) * | 2007-07-03 | 2010-09-23 | Synergy Biosurgical Ag | Medical implant |
US20100286775A1 (en) * | 2007-10-11 | 2010-11-11 | Tavor [I.T.N] Ltd., | Ligament and Tendon Prosthesis |
WO2010094032A3 (en) * | 2009-02-16 | 2010-11-11 | Aoi Medical Inc. | Trauma nail accumulator |
US20110160870A1 (en) * | 2009-11-30 | 2011-06-30 | Adrian Baumgartner | Expandable implant |
US8287538B2 (en) | 2008-01-14 | 2012-10-16 | Conventus Orthopaedics, Inc. | Apparatus and methods for fracture repair |
US20130012942A1 (en) * | 2005-05-18 | 2013-01-10 | Sonoma Orthopedic Products, Inc. | Segmented intramedullary fracture fixation devices and methods |
WO2012083051A3 (en) * | 2010-12-16 | 2013-03-07 | Lawrence Livermore National Security, Llc | Expandable implant and implant system |
WO2013071432A1 (en) | 2011-11-14 | 2013-05-23 | The University Of British Columbia | Intramedullary fixation system for management of pelvic and acetabular fractures |
US8546456B2 (en) | 2008-07-25 | 2013-10-01 | Smith & Nephew, Inc. | Fracture fixation systems |
US20140058391A1 (en) * | 2012-08-23 | 2014-02-27 | Andreas Appenzeller | Intramedullary Fixation System |
US20140067073A1 (en) * | 2012-08-12 | 2014-03-06 | Brian Albert Hauck | Memory material implant system and methods of use |
WO2014043794A1 (en) * | 2012-09-23 | 2014-03-27 | Impetus Innovations, Inc. | A segmental reconstructive intramedullary nail and delivery system |
EP2734133A1 (en) * | 2011-07-19 | 2014-05-28 | Illuminoss Medical, Inc. | Combination photodynamic devices |
US8777618B2 (en) | 2007-09-17 | 2014-07-15 | Synergy Biosurgical Ag | Medical implant II |
US8906022B2 (en) | 2010-03-08 | 2014-12-09 | Conventus Orthopaedics, Inc. | Apparatus and methods for securing a bone implant |
CN104207867A (en) * | 2014-08-13 | 2014-12-17 | 中国科学院福建物质结构研究所 | Low-modulus medical implant porous scaffold structure |
US8961518B2 (en) | 2010-01-20 | 2015-02-24 | Conventus Orthopaedics, Inc. | Apparatus and methods for bone access and cavity preparation |
US8961516B2 (en) | 2005-05-18 | 2015-02-24 | Sonoma Orthopedic Products, Inc. | Straight intramedullary fracture fixation devices and methods |
US9259250B2 (en) | 2006-11-22 | 2016-02-16 | Sonoma Orthopedic Products, Inc. | Fracture fixation device, tools and methods |
US9265616B2 (en) | 2010-08-10 | 2016-02-23 | DePuy Synthes Products, Inc. | Expandable implant |
US9283006B2 (en) | 2011-09-22 | 2016-03-15 | Mx Orthopedics, Corp. | Osteosynthetic shape memory material intramedullary bone stent and method for treating a bone fracture using the same |
US20160166291A1 (en) * | 2013-06-24 | 2016-06-16 | The University Of Toledo | Bioactive Fusion Device |
US9452005B2 (en) | 2012-08-23 | 2016-09-27 | DePuy Synthes Products, Inc. | Bone fixation system |
WO2016160180A1 (en) * | 2015-03-31 | 2016-10-06 | DePuy Synthes Products, Inc. | Bone graft cage |
US20160346018A1 (en) * | 2015-06-01 | 2016-12-01 | The Texas A &M University System | Defect fixation device |
US20170027624A1 (en) * | 2014-04-11 | 2017-02-02 | Smith & Nephew, Inc. | Dmls orthopedic intramedullary device and method of manufacture |
EP2523614A4 (en) * | 2010-01-15 | 2017-02-15 | Conventus Orthopaedics, Inc. | Rotary-rigid orthopaedic rod |
US20170156766A1 (en) * | 2015-12-03 | 2017-06-08 | David M. Anderson | Hammertoe implant promoting bony in-growth |
CN106943210A (en) * | 2017-04-21 | 2017-07-14 | 无锡市第九人民医院 | A kind of titanium cage for being used to wrap up long bone cortex bone ectonexine bone grafting |
US9724138B2 (en) | 2011-09-22 | 2017-08-08 | Arthrex, Inc. | Intermedullary devices for generating and applying compression within a body |
US20170238977A1 (en) * | 2014-10-14 | 2017-08-24 | Empire Technology Development Llc | Systems and methods for intermedullary bone fixation |
DE102016003838A1 (en) * | 2016-03-29 | 2017-10-05 | Merete Holding Gmbh | Implantable compensating cuff for an endoprosthesis |
US9925046B2 (en) | 2015-03-31 | 2018-03-27 | DePuy Synthes Products, Inc. | Bone graft cage |
US10004603B2 (en) | 2012-08-23 | 2018-06-26 | DePuy Synthes Products, Inc. | Bone implant |
US10022132B2 (en) | 2013-12-12 | 2018-07-17 | Conventus Orthopaedics, Inc. | Tissue displacement tools and methods |
US10307188B2 (en) | 2014-03-06 | 2019-06-04 | The University Of British Columbia | Shape adaptable intramedullary fixation device |
US10500076B2 (en) * | 2012-07-23 | 2019-12-10 | Abbott Cardiovascular Systems Inc. | Shape memory bioresorbable polymer peripheral scaffolds |
US10507110B2 (en) | 2016-06-13 | 2019-12-17 | DePuy Synthes Products, Inc. | Bone graft cage |
US10561765B2 (en) | 2015-07-27 | 2020-02-18 | The Texas A&M University System | Medical devices coated with shape memory polymer foams |
US10568671B2 (en) | 2016-03-29 | 2020-02-25 | Merete Holding Gmbh | Implantable compensating sleeve for an endoprosthesis |
US10695181B2 (en) | 2016-02-16 | 2020-06-30 | DePuy Synthes Products, Inc. | Bone graft cage |
US10918426B2 (en) | 2017-07-04 | 2021-02-16 | Conventus Orthopaedics, Inc. | Apparatus and methods for treatment of a bone |
US11219520B2 (en) | 2017-03-14 | 2022-01-11 | Shape Memory Medical, Inc. | Shape memory polymer foams to seal space around valves |
US11419645B2 (en) | 2016-10-05 | 2022-08-23 | University Of British Columbia | Intramedullary fixation device with shape locking interface |
US11504240B2 (en) | 2020-06-04 | 2022-11-22 | DePuy Synthes Products, Inc. | Modular bone graft cage |
US11832856B2 (en) | 2018-10-17 | 2023-12-05 | The University Of British Columbia | Bone-fixation device and system |
Families Citing this family (102)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9060809B2 (en) * | 2001-10-18 | 2015-06-23 | Orthoip, Llc | Lagwire system and method for the fixation of bone fractures |
US8828067B2 (en) | 2001-10-18 | 2014-09-09 | Orthoip, Llc | Bone screw system and method |
WO2006034436A2 (en) | 2004-09-21 | 2006-03-30 | Stout Medical Group, L.P. | Expandable support device and method of use |
US7771411B2 (en) | 2004-09-24 | 2010-08-10 | Syntheon, Llc | Methods for operating a selective stiffening catheter |
US9452001B2 (en) * | 2005-02-22 | 2016-09-27 | Tecres S.P.A. | Disposable device for treatment of infections of human limbs |
WO2007058943A2 (en) * | 2005-11-10 | 2007-05-24 | Zimmer, Inc. | Minamally invasive orthopaedic delivery devices and tools |
US9814372B2 (en) | 2007-06-27 | 2017-11-14 | Syntheon, Llc | Torque-transmitting, variably-flexible, locking insertion device and method for operating the insertion device |
US10123683B2 (en) | 2006-03-02 | 2018-11-13 | Syntheon, Llc | Variably flexible insertion device and method for variably flexing an insertion device |
WO2007127255A2 (en) | 2006-04-26 | 2007-11-08 | Illuminoss Medical, Inc. | Apparatus and methods for reinforcing bone |
US7806900B2 (en) | 2006-04-26 | 2010-10-05 | Illuminoss Medical, Inc. | Apparatus and methods for delivery of reinforcing materials to bone |
JP5542273B2 (en) * | 2006-05-01 | 2014-07-09 | スタウト メディカル グループ,エル.ピー. | Expandable support device and method of use |
EP2091445B1 (en) | 2006-11-10 | 2015-03-11 | Illuminoss Medical, Inc. | Systems for internal bone fixation |
US7879041B2 (en) | 2006-11-10 | 2011-02-01 | Illuminoss Medical, Inc. | Systems and methods for internal bone fixation |
EP3300676A1 (en) * | 2007-03-12 | 2018-04-04 | Stout Medical Group, L.P. | Expandable attachment device |
EP3111869B1 (en) | 2007-03-15 | 2017-09-20 | Ortho-Space Ltd. | System of sealing an inflatable prosthesis |
WO2009018248A1 (en) * | 2007-07-30 | 2009-02-05 | Audubon Technologies, Llc | Device for maintaining patent paranasal sinus ostia |
WO2009059090A1 (en) | 2007-10-31 | 2009-05-07 | Illuminoss Medical, Inc. | Light source |
US8403968B2 (en) | 2007-12-26 | 2013-03-26 | Illuminoss Medical, Inc. | Apparatus and methods for repairing craniomaxillofacial bones using customized bone plates |
US20090265016A1 (en) * | 2008-04-21 | 2009-10-22 | Lasse Daniel Efskind | Material for surgical use in traumatology |
US20090263458A1 (en) * | 2008-04-21 | 2009-10-22 | Lasse Daniel Efskind | Material for surgical use in traumatology |
US20090292172A1 (en) * | 2008-05-21 | 2009-11-26 | Boston Scientific Scimed, Inc. | Expandable Delivery Devices and Methods of Use |
US20100094292A1 (en) * | 2008-10-14 | 2010-04-15 | Zimmer, Inc. | Modular intramedullary nail |
US20100211176A1 (en) | 2008-11-12 | 2010-08-19 | Stout Medical Group, L.P. | Fixation device and method |
US20100204795A1 (en) | 2008-11-12 | 2010-08-12 | Stout Medical Group, L.P. | Fixation device and method |
US10610364B2 (en) | 2008-12-04 | 2020-04-07 | Subchondral Solutions, Inc. | Method for ameliorating joint conditions and diseases and preventing bone hypertrophy |
US20100217391A1 (en) * | 2009-02-21 | 2010-08-26 | Ladd Amy L | Tensioning bone implant device |
US8012155B2 (en) * | 2009-04-02 | 2011-09-06 | Zimmer, Inc. | Apparatus and method for prophylactic hip fixation |
US8210729B2 (en) | 2009-04-06 | 2012-07-03 | Illuminoss Medical, Inc. | Attachment system for light-conducting fibers |
US8512338B2 (en) | 2009-04-07 | 2013-08-20 | Illuminoss Medical, Inc. | Photodynamic bone stabilization systems and methods for reinforcing bone |
US8870965B2 (en) | 2009-08-19 | 2014-10-28 | Illuminoss Medical, Inc. | Devices and methods for bone alignment, stabilization and distraction |
US9232954B2 (en) | 2009-08-20 | 2016-01-12 | Howmedica Osteonics Corp. | Flexible ACL instrumentation, kit and method |
US8545499B2 (en) * | 2009-09-28 | 2013-10-01 | Zimmer, Inc. | Expandable intramedullary rod |
US20110118740A1 (en) * | 2009-11-10 | 2011-05-19 | Illuminoss Medical, Inc. | Intramedullary Implants Having Variable Fastener Placement |
WO2011075745A2 (en) * | 2009-12-18 | 2011-06-23 | Palmaz Scientific, Inc. | Interosteal and intramedullary implants and method of implanting same |
US20110288652A1 (en) * | 2010-05-20 | 2011-11-24 | Indiana University Research & Technology Corporation | Materials and methods for treating critically sized defects in mouse bone |
WO2011153454A2 (en) * | 2010-06-03 | 2011-12-08 | The University Of North Carolina At Chapel Hill | Threaded elastic intramedullary nails devices and methods |
US8684965B2 (en) | 2010-06-21 | 2014-04-01 | Illuminoss Medical, Inc. | Photodynamic bone stabilization and drug delivery systems |
WO2012024332A2 (en) * | 2010-08-20 | 2012-02-23 | Osteospring Medical, Inc. | Reduced bone fracture fixation device |
EP2608747A4 (en) | 2010-08-24 | 2015-02-11 | Flexmedex Llc | Support device and method for use |
WO2012033983A2 (en) * | 2010-09-09 | 2012-03-15 | Dr. Reddy's Laboratories Ltd. | Candesartan pharmaceutical compositions |
EP2613720B1 (en) | 2010-09-09 | 2017-03-01 | Synthes GmbH | Surgical nail |
US10525169B2 (en) | 2010-10-20 | 2020-01-07 | 206 Ortho, Inc. | Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants, and novel composite structures which may be used for medical and non-medical applications |
WO2015095745A1 (en) | 2010-10-20 | 2015-06-25 | 206 Ortho, Inc. | Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants, and novel composite structures which may be used for medical and non-medical applications |
EP2629780A4 (en) | 2010-10-20 | 2014-10-01 | 206 Ortho Inc | Implantable polymer for bone and vascular lesions |
US9320601B2 (en) | 2011-10-20 | 2016-04-26 | 206 Ortho, Inc. | Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants |
US11207109B2 (en) | 2010-10-20 | 2021-12-28 | 206 Ortho, Inc. | Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants, and novel composite structures which may be used for medical and non-medical applications |
US11484627B2 (en) | 2010-10-20 | 2022-11-01 | 206 Ortho, Inc. | Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants, and novel composite structures which may be used for medical and non-medical applications |
US11291483B2 (en) | 2010-10-20 | 2022-04-05 | 206 Ortho, Inc. | Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants |
US11058796B2 (en) | 2010-10-20 | 2021-07-13 | 206 Ortho, Inc. | Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants, and novel composite structures which may be used for medical and non-medical applications |
CN101991460A (en) * | 2010-11-16 | 2011-03-30 | 张英泽 | Gas-liquid two-phase intramedullary nail |
EP2654584A1 (en) | 2010-12-22 | 2013-10-30 | Illuminoss Medical, Inc. | Systems and methods for treating conditions and diseases of the spine |
TWI434668B (en) | 2011-02-10 | 2014-04-21 | Metal Ind Res & Dev Ct | Medical instrument with modular intramedullary nail |
US20120283811A1 (en) * | 2011-05-02 | 2012-11-08 | Cook Medical Technologies Llc | Biodegradable, bioabsorbable stent anchors |
JP2014529445A (en) | 2011-08-23 | 2014-11-13 | フレックスメデックス,エルエルシー | Tissue removal apparatus and method |
US9974640B2 (en) | 2011-09-22 | 2018-05-22 | Boston Scientific Scimed, Inc. | Pelvic implant and treatment method |
WO2013057566A2 (en) | 2011-10-18 | 2013-04-25 | Ortho-Space Ltd. | Prosthetic devices and methods for using same |
WO2013059609A1 (en) | 2011-10-19 | 2013-04-25 | Illuminoss Medical, Inc. | Systems and methods for joint stabilization |
EP2617370B1 (en) | 2012-01-19 | 2017-12-20 | Stryker European Holdings I, LLC | Sleeve in particular for suprapatellar surgery |
US9554836B2 (en) | 2012-06-29 | 2017-01-31 | The Cleveland Clinic Foundation | Intramedullary bone stent |
US8939977B2 (en) | 2012-07-10 | 2015-01-27 | Illuminoss Medical, Inc. | Systems and methods for separating bone fixation devices from introducer |
US11051864B2 (en) * | 2012-08-30 | 2021-07-06 | DePuy Synthes Products, Inc. | Intramedullary fixation assembly |
TW201422268A (en) | 2012-12-07 | 2014-06-16 | Ind Tech Res Inst | Injection device and heting device thereof |
US9687281B2 (en) | 2012-12-20 | 2017-06-27 | Illuminoss Medical, Inc. | Distal tip for bone fixation devices |
US9585695B2 (en) | 2013-03-15 | 2017-03-07 | Woven Orthopedic Technologies, Llc | Surgical screw hole liner devices and related methods |
US10010609B2 (en) | 2013-05-23 | 2018-07-03 | 206 Ortho, Inc. | Method and apparatus for treating bone fractures, and/or for fortifying and/or augmenting bone, including the provision and use of composite implants |
RU2526242C1 (en) * | 2013-10-03 | 2014-08-20 | Анатолий Петрович Барабаш | Intramedullary blocking device for osteosynthesis |
US9770278B2 (en) | 2014-01-17 | 2017-09-26 | Arthrex, Inc. | Dual tip guide wire |
KR101624614B1 (en) | 2014-07-18 | 2016-05-27 | 주식회사 케이씨스 | Shrinkage or expansion possible functional intramedullary fixation apparatus |
US8956394B1 (en) | 2014-08-05 | 2015-02-17 | Woven Orthopedic Technologies, Llc | Woven retention devices, systems and methods |
US9907593B2 (en) | 2014-08-05 | 2018-03-06 | Woven Orthopedic Technologies, Llc | Woven retention devices, systems and methods |
US9943351B2 (en) | 2014-09-16 | 2018-04-17 | Woven Orthopedic Technologies, Llc | Woven retention devices, systems, packaging, and related methods |
US9814499B2 (en) | 2014-09-30 | 2017-11-14 | Arthrex, Inc. | Intramedullary fracture fixation devices and methods |
CN104323875B (en) * | 2014-10-14 | 2017-01-18 | 刘振东 | Bone grafting device for repairing large segmental bone defects |
USD740427S1 (en) | 2014-10-17 | 2015-10-06 | Woven Orthopedic Technologies, Llc | Orthopedic woven retention device |
US9770279B2 (en) * | 2015-05-18 | 2017-09-26 | Little Engine, LLC | Method and apparatus for extraction of medical implants |
US10154863B2 (en) | 2015-07-13 | 2018-12-18 | IntraFuse, LLC | Flexible bone screw |
US10485595B2 (en) | 2015-07-13 | 2019-11-26 | IntraFuse, LLC | Flexible bone screw |
US10136929B2 (en) | 2015-07-13 | 2018-11-27 | IntraFuse, LLC | Flexible bone implant |
US10499960B2 (en) | 2015-07-13 | 2019-12-10 | IntraFuse, LLC | Method of bone fixation |
WO2017024277A1 (en) | 2015-08-05 | 2017-02-09 | Woven Orthopedic Technologies, Llc | Tapping devices, systems and methods for use in bone tissue |
US11331191B2 (en) | 2015-08-12 | 2022-05-17 | Howmedica Osteonics Corp. | Bioactive soft tissue implant and methods of manufacture and use thereof |
CA2938576A1 (en) | 2015-08-12 | 2017-02-12 | Howmedica Osteonics Corp. | Methods for forming scaffolds |
US10729548B2 (en) | 2016-05-02 | 2020-08-04 | Howmedica Osteonics Corp. | Bioactive soft tissue implant and methods of manufacture and use thereof |
WO2017046647A1 (en) | 2015-09-18 | 2017-03-23 | Ortho-Space Ltd. | Intramedullary fixated subacromial spacers |
US9974581B2 (en) | 2015-11-20 | 2018-05-22 | Globus Medical, Inc. | Expandable intramedullary systems and methods of using the same |
US10092333B2 (en) | 2015-11-20 | 2018-10-09 | Globus Medical, Inc. | Expandable intramedullary systems and methods of using the same |
US9827025B2 (en) | 2015-11-20 | 2017-11-28 | Globus Medical, Inc. | Expandable intramedullary systems and methods of using the same |
US11039927B2 (en) | 2015-11-25 | 2021-06-22 | Subchondral Solutions, Inc. | Methods, systems and devices for repairing anatomical joint conditions |
CN105943146B (en) * | 2016-05-14 | 2020-04-17 | 苏州苏南捷迈得医疗器械有限公司 | Shape memory alloy bone plate cooler |
CN105919663A (en) * | 2016-06-08 | 2016-09-07 | 河北医科大学第三医院 | Elastic intramedullary nail with bionic internal fixation action |
CN106108998A (en) * | 2016-07-25 | 2016-11-16 | 南京医科大学第附属医院 | A kind of braided steel wire inner core antibiotic-loaded bone cement intramedullary pin and preparation method thereof and making mould |
FR3054430B1 (en) * | 2016-07-27 | 2018-07-27 | Centre Hospitalier Universitaire De Bordeaux | INTRA-BONE STENT |
WO2018107114A1 (en) | 2016-12-09 | 2018-06-14 | Woven Orthopedic Technologies, LLC. | Retention devices, lattices and related systems and methods |
US11045981B2 (en) | 2017-01-30 | 2021-06-29 | Ortho-Space Ltd. | Processing machine and methods for processing dip-molded articles |
US10751507B2 (en) | 2017-04-10 | 2020-08-25 | Syn Variflex, Llc | Thermally controlled variable-flexibility catheters and methods of manufacturing same |
CN109464220A (en) * | 2017-09-08 | 2019-03-15 | 重庆润泽医药有限公司 | A kind of tantalum stick for medical surgery |
CN107981926B (en) * | 2017-09-20 | 2021-03-12 | 北京航空航天大学 | Pedicle screw with anti-pulling-out performance |
US10888363B2 (en) | 2017-12-06 | 2021-01-12 | Stout Medical Group, L.P. | Attachment device and method for use |
US20190215627A1 (en) * | 2018-01-11 | 2019-07-11 | Orello Hearing Technologies Inc. | Hearing assistance device |
WO2020006239A1 (en) | 2018-06-27 | 2020-01-02 | Illuminoss Medical, Inc. | Systems and methods for bone stabilization and fixation |
FR3096883B1 (en) * | 2019-06-05 | 2023-11-24 | One Ortho | Fixation system between a medical device and at least part of a bone |
WO2021157145A1 (en) * | 2020-02-05 | 2021-08-12 | 富士フィルター工業株式会社 | Implant for bone fracture treatment and method for manufacturing implant for bone fracture treatment |
Citations (65)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US426665A (en) * | 1890-04-29 | Clamp | ||
US4177524A (en) * | 1976-05-14 | 1979-12-11 | Pfaudler-Werke A.G. | Medical securement element with abrasive grains on thread surface |
US4204531A (en) * | 1977-12-28 | 1980-05-27 | Yacov Aginsky | Intramedullary nail with expanding mechanism |
US4222128A (en) * | 1977-05-20 | 1980-09-16 | Kureha Kagaku Kogyo Kabushiki Kaisha | Composite implant materials and process for preparing same |
US4453539A (en) * | 1982-03-01 | 1984-06-12 | The University Of Toledo | Expandable intramedullary nail for the fixation of bone fractures |
US4522200A (en) * | 1983-06-10 | 1985-06-11 | Ace Orthopedic Company | Adjustable intramedullar rod |
US4854312A (en) * | 1988-04-13 | 1989-08-08 | The University Of Toledo | Expanding intramedullary nail |
US4932969A (en) * | 1987-01-08 | 1990-06-12 | Sulzer Brothers Limited | Joint endoprosthesis |
US5108404A (en) * | 1989-02-09 | 1992-04-28 | Arie Scholten | Surgical protocol for fixation of bone using inflatable device |
US5108398A (en) * | 1990-10-16 | 1992-04-28 | Orthopaedic Research Institute | Orthopaedic knee fusion apparatus |
US5620445A (en) * | 1994-07-15 | 1997-04-15 | Brosnahan; Robert | Modular intramedullary nail |
US5653709A (en) * | 1992-12-04 | 1997-08-05 | Synthes (U.S.A.) | Modular marrow nail |
US5855579A (en) * | 1994-07-15 | 1999-01-05 | Smith & Nephew, Inc. | Cannulated modular intramedullary nail |
US6206880B1 (en) * | 2000-02-21 | 2001-03-27 | Abbas Karladani | Method for percutaneous intramedullary nailing of tibial shaft fractures |
US6245102B1 (en) * | 1997-05-07 | 2001-06-12 | Iowa-India Investments Company Ltd. | Stent, stent graft and stent valve |
US6261289B1 (en) * | 1998-10-26 | 2001-07-17 | Mark Levy | Expandable orthopedic device |
US6299635B1 (en) * | 1997-09-29 | 2001-10-09 | Cook Incorporated | Radially expandable non-axially contracting surgical stent |
US6312455B2 (en) * | 1997-04-25 | 2001-11-06 | Nitinol Devices & Components | Stent |
US20020032444A1 (en) * | 1999-12-09 | 2002-03-14 | Mische Hans A. | Methods and devices for treatment of bone fractures |
US6475237B2 (en) * | 1999-05-03 | 2002-11-05 | William J. Drasler | Intravascular hinge stent |
US20020165544A1 (en) * | 1999-11-11 | 2002-11-07 | Stephan Perren | Radially expandable intramedullary nail |
US6491718B1 (en) * | 1999-10-05 | 2002-12-10 | Amjad Ahmad | Intra vascular stent |
US6506211B1 (en) * | 2000-11-13 | 2003-01-14 | Scimed Life Systems, Inc. | Stent designs |
US6551321B1 (en) * | 2000-06-23 | 2003-04-22 | Centerpulse Orthopedics Inc. | Flexible intramedullary nail |
US6554833B2 (en) * | 1998-10-26 | 2003-04-29 | Expanding Orthopedics, Inc. | Expandable orthopedic device |
US20030109932A1 (en) * | 2000-01-03 | 2003-06-12 | Ory Keynan | Intramedullary support strut |
US6613081B2 (en) * | 1997-11-14 | 2003-09-02 | Transvascular, Inc. | Deformable scaffolding multicellular stent |
US6626937B1 (en) * | 2000-11-14 | 2003-09-30 | Advanced Cardiovascular Systems, Inc. | Austenitic nitinol medical devices |
US6682554B2 (en) * | 1998-09-05 | 2004-01-27 | Jomed Gmbh | Methods and apparatus for a stent having an expandable web structure |
US6709454B1 (en) * | 1999-05-17 | 2004-03-23 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent with enhanced delivery precision and stent delivery system |
US6746477B2 (en) * | 2000-03-09 | 2004-06-08 | Lpl Systems, Inc. | Expandable stent |
US6746479B2 (en) * | 1997-04-25 | 2004-06-08 | Scimed Life Systems, Inc. | Stent cell configurations including spirals |
US6761731B2 (en) * | 2002-06-28 | 2004-07-13 | Cordis Corporation | Balloon-stent interaction to help reduce foreshortening |
US6764506B2 (en) * | 1997-02-07 | 2004-07-20 | Endosystems Llc | Non-foreshortening intraluminal prosthesis |
US6764507B2 (en) * | 2000-10-16 | 2004-07-20 | Conor Medsystems, Inc. | Expandable medical device with improved spatial distribution |
US6770088B1 (en) * | 1996-04-26 | 2004-08-03 | Scimed Life Systems, Inc. | Intravascular stent |
US6770089B1 (en) * | 2000-12-28 | 2004-08-03 | Advanced Cardiovascular Systems, Inc. | Hybrid stent fabrication using metal rings and polymeric links |
US6776793B2 (en) * | 1995-03-01 | 2004-08-17 | Scimed Life Systems, Inc. | Longitudinally flexible expandable stent |
US6790227B2 (en) * | 2001-03-01 | 2004-09-14 | Cordis Corporation | Flexible stent |
US20040199246A1 (en) * | 2003-04-02 | 2004-10-07 | Scimed Life Systems, Inc. | Expandable stent |
US6805706B2 (en) * | 2002-08-15 | 2004-10-19 | Gmp Cardiac Care, Inc. | Stent-graft with rails |
US6808561B2 (en) * | 2000-10-16 | 2004-10-26 | University Of South Carolina | Biocompatible cement containing reactive calcium phosphate nanoparticles and methods for making and using such cement |
US6866805B2 (en) * | 2001-12-27 | 2005-03-15 | Advanced Cardiovascular Systems, Inc. | Hybrid intravascular stent |
US6896696B2 (en) * | 1998-11-20 | 2005-05-24 | Scimed Life Systems, Inc. | Flexible and expandable stent |
US6911048B2 (en) * | 2000-03-13 | 2005-06-28 | Exactech, Inc. | Modular hip prosthesis |
US6939373B2 (en) * | 2003-08-20 | 2005-09-06 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US6955686B2 (en) * | 2001-03-01 | 2005-10-18 | Cordis Corporation | Flexible stent |
US6962603B1 (en) * | 1995-03-01 | 2005-11-08 | Boston Scientific Scimed, Inc. | Longitudinally flexible expandable stent |
US6979349B1 (en) * | 2001-06-29 | 2005-12-27 | Advanced Cardiovascular Systems, Inc. | Universal stent link design |
US6998060B2 (en) * | 2001-03-01 | 2006-02-14 | Cordis Corporation | Flexible stent and method of manufacture |
US6997946B2 (en) * | 2002-11-27 | 2006-02-14 | Boston Scientific Scimed, Inc. | Expandable stents |
US7005136B2 (en) * | 2002-03-29 | 2006-02-28 | Ethicon, Inc. | Bone replacement materials utilizing bioabsorbable liquid polymers |
US7025777B2 (en) * | 2002-07-31 | 2006-04-11 | Unison Therapeutics, Inc. | Flexible and conformable stent and method of forming same |
US7029493B2 (en) * | 2002-01-25 | 2006-04-18 | Cordis Corporation | Stent with enhanced crossability |
US7044963B1 (en) * | 1996-09-19 | 2006-05-16 | Medinol, Ltd. | Stent with variable features to optimize support and method of making such stent |
US7060088B1 (en) * | 1998-11-13 | 2006-06-13 | Cordis Corporation | Stent with improved flexible connecting links |
US7081130B2 (en) * | 1996-04-26 | 2006-07-25 | Boston Scientific Scimed, Inc. | Intravascular Stent |
US7094255B2 (en) * | 1996-03-05 | 2006-08-22 | Evysio Medical Devices Ulc | Expandable stent and method for delivery of same |
US7101391B2 (en) * | 2000-09-18 | 2006-09-05 | Inflow Dynamics Inc. | Primarily niobium stent |
US7108714B1 (en) * | 1997-06-13 | 2006-09-19 | Orbus Medical Technologies, Inc. | Expandable intraluminal endoprosthesis |
US7112216B2 (en) * | 2003-05-28 | 2006-09-26 | Boston Scientific Scimed, Inc. | Stent with tapered flexibility |
US20060264952A1 (en) * | 2005-05-18 | 2006-11-23 | Nelson Charles L | Methods of Using Minimally Invasive Actuable Bone Fixation Devices |
US20060264945A1 (en) * | 2005-05-18 | 2006-11-23 | Edidin Avram A | Selectively-expandable bone scaffold |
US20080033522A1 (en) * | 2006-08-03 | 2008-02-07 | Med Institute, Inc. | Implantable Medical Device with Particulate Coating |
US20080255560A1 (en) * | 2004-05-21 | 2008-10-16 | Myers Surgical Solutions, Llc | Fracture Fixation and Site Stabilization System |
Family Cites Families (58)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE2603456C2 (en) * | 1976-01-30 | 1984-04-05 | Robert Bosch Gmbh, 7000 Stuttgart | Process for the production of a bone implant |
SU848004A1 (en) * | 1979-01-04 | 1981-07-23 | Всесоюзный Научно-Исследовательскийи Испытательный Институт Медицинскойтехники | Joining element for fixation of bone tissue |
US4262665A (en) | 1979-06-27 | 1981-04-21 | Roalstad W L | Intramedullary compression device |
US4409974A (en) * | 1981-06-29 | 1983-10-18 | Freedland Jeffrey A | Bone-fixating surgical implant device |
US4457301A (en) * | 1982-06-18 | 1984-07-03 | Howmedica Inc. | Intramedullary fixation device |
US5190546A (en) * | 1983-10-14 | 1993-03-02 | Raychem Corporation | Medical devices incorporating SIM alloy elements |
US4721103A (en) * | 1985-01-31 | 1988-01-26 | Yosef Freedland | Orthopedic device |
US4776330A (en) | 1986-06-23 | 1988-10-11 | Pfizer Hospital Products Group, Inc. | Modular femoral fixation system |
FR2626276B1 (en) * | 1988-01-22 | 1990-05-11 | Hoechst France | IMPROVEMENT IN THE PROCESS FOR THE MANUFACTURE OF ALKYL PYRUVATES |
CH676196A5 (en) * | 1988-08-30 | 1990-12-28 | Sulzer Ag | |
US5281225A (en) * | 1989-06-07 | 1994-01-25 | Guglielmo Vicenzi | Intramedullary pin with self-locking end for metadiaphyseal fractures of long bones |
AT393617B (en) | 1989-10-25 | 1991-11-25 | Ender Hans Georg | INSTRUMENTARIUM FOR REPOSITION AND FIXATION OF PER- AND SUBTROCHANTER FRACTURES |
US5053035A (en) | 1990-05-24 | 1991-10-01 | Mclaren Alexander C | Flexible intramedullary fixation rod |
US5324307A (en) * | 1990-07-06 | 1994-06-28 | American Cyanamid Company | Polymeric surgical staple |
US5720753A (en) * | 1991-03-22 | 1998-02-24 | United States Surgical Corporation | Orthopedic fastener |
US5501695A (en) * | 1992-05-27 | 1996-03-26 | The Anspach Effort, Inc. | Fastener for attaching objects to bones |
US5263991A (en) * | 1992-10-21 | 1993-11-23 | Biomet, Inc. | Method for heating biocompatible implants in a thermal packaging line |
US5423850A (en) | 1993-10-01 | 1995-06-13 | Berger; J. Lee | Balloon compressor for internal fixation of bone fractures |
US5480400A (en) * | 1993-10-01 | 1996-01-02 | Berger; J. Lee | Method and device for internal fixation of bone fractures |
US6248110B1 (en) * | 1994-01-26 | 2001-06-19 | Kyphon, Inc. | Systems and methods for treating fractured or diseased bone using expandable bodies |
US6413539B1 (en) * | 1996-10-31 | 2002-07-02 | Poly-Med, Inc. | Hydrogel-forming, self-solvating absorbable polyester copolymers, and methods for use thereof |
WO1997007743A1 (en) * | 1995-08-25 | 1997-03-06 | Grotz R Thomas | Stabilizer for human joints |
US5725541A (en) * | 1996-01-22 | 1998-03-10 | The Anspach Effort, Inc. | Soft tissue fastener device |
US5976139A (en) | 1996-07-17 | 1999-11-02 | Bramlet; Dale G. | Surgical fastener assembly |
US5849004A (en) | 1996-07-17 | 1998-12-15 | Bramlet; Dale G. | Surgical anchor |
US6083244A (en) * | 1996-09-13 | 2000-07-04 | Tendon Technology, Ltd. | Apparatus and method for tendon or ligament repair |
FR2753368B1 (en) * | 1996-09-13 | 1999-01-08 | Chauvin Jean Luc | EXPANSIONAL OSTEOSYNTHESIS CAGE |
DE69839051T2 (en) | 1997-03-07 | 2009-01-15 | Disc-O-Tech Medical Technologies, Ltd. | PERCUT BONE SYSTEMS AND SPINAL STABILIZATION, MOUNTING AND REPAIR |
AU734539B2 (en) * | 1998-01-06 | 2001-06-14 | Aderans Research Institute, Inc. | Bioabsorbable fibers and reinforced composites produced therefrom |
WO2000012832A2 (en) | 1998-08-26 | 2000-03-09 | Molecular Geodesics, Inc. | Radially expandable device |
DE60206274T2 (en) | 1998-10-26 | 2006-06-08 | Expanding Orthopedics Inc., Boston | SPREADABLE DEVICE FOR ORTHOPEDICS |
US6558414B2 (en) | 1999-02-02 | 2003-05-06 | Impra, Inc. | Partial encapsulation of stents using strips and bands |
US6342065B1 (en) * | 1999-03-17 | 2002-01-29 | Poly-Med, Inc. | High strength fibers of L-lactide copolymers ε-caprolactone and trimethylene carbonate and absorbable medical constructs thereof |
US7048753B2 (en) * | 1999-03-17 | 2006-05-23 | Poly-Med, Inc. | Coated, slow-absorbing textile constructs for sutures and tissue engineering |
US6423067B1 (en) | 1999-04-29 | 2002-07-23 | Theken Surgical Llc | Nonlinear lag screw with captive driving device |
FR2801189B1 (en) | 1999-11-24 | 2002-10-25 | Newdeal | IMPLANT FOR BONE SHORTENING, AND PARTICULARLY, METATARSIAN |
US7258692B2 (en) * | 2000-03-07 | 2007-08-21 | Zimmer, Inc. | Method and apparatus for reducing femoral fractures |
US6582453B1 (en) * | 2000-07-14 | 2003-06-24 | Opus Medical, Inc. | Method and apparatus for attaching connective tissues to bone using a suture anchoring device |
DE10204904A1 (en) | 2002-02-06 | 2003-08-14 | Wittenstein Ag | Device, in particular intramedullary nail and / or sleeve for insertion into long bones |
US7695471B2 (en) | 2003-04-18 | 2010-04-13 | The University Of Hong Kong | Fixation device |
EP1652384A1 (en) | 2003-07-24 | 2006-05-03 | Koninklijke Philips Electronics N.V. | Handling feature availability in a broadcast |
CN1909848B (en) * | 2004-01-16 | 2012-05-23 | 扩展整形外科公司 | Bone fracture treatment devices |
US7632277B2 (en) | 2004-03-29 | 2009-12-15 | Woll Bioorthopedics Llc | Orthopedic intramedullary fixation system |
US7091130B1 (en) * | 2004-06-25 | 2006-08-15 | Freescale Semiconductor, Inc. | Method of forming a nanocluster charge storage device |
WO2006108114A2 (en) | 2005-04-01 | 2006-10-12 | The Regents Of The University Of Colorado | A graft fixation device and method |
US7967820B2 (en) * | 2006-02-07 | 2011-06-28 | P Tech, Llc. | Methods and devices for trauma welding |
US7942876B2 (en) | 2006-03-10 | 2011-05-17 | Accelerated Orthopedic Repair, Llc | Intra-medullary implant with active compression |
US7806900B2 (en) | 2006-04-26 | 2010-10-05 | Illuminoss Medical, Inc. | Apparatus and methods for delivery of reinforcing materials to bone |
WO2007127255A2 (en) | 2006-04-26 | 2007-11-08 | Illuminoss Medical, Inc. | Apparatus and methods for reinforcing bone |
US20090005782A1 (en) | 2007-03-02 | 2009-01-01 | Chirico Paul E | Fracture Fixation System and Method |
US20080169582A1 (en) | 2006-10-23 | 2008-07-17 | Vipul Bhupendra Dave | Method and apparatus for making polymeric drug delivery devices having differing morphological structures |
US7879041B2 (en) | 2006-11-10 | 2011-02-01 | Illuminoss Medical, Inc. | Systems and methods for internal bone fixation |
EP2091445B1 (en) * | 2006-11-10 | 2015-03-11 | Illuminoss Medical, Inc. | Systems for internal bone fixation |
US8128626B2 (en) | 2007-04-24 | 2012-03-06 | Flexfix, Llc | System and method for delivery conformation and removal of intramedullary bone fixation devices |
US8512338B2 (en) | 2009-04-07 | 2013-08-20 | Illuminoss Medical, Inc. | Photodynamic bone stabilization systems and methods for reinforcing bone |
US8870965B2 (en) | 2009-08-19 | 2014-10-28 | Illuminoss Medical, Inc. | Devices and methods for bone alignment, stabilization and distraction |
US20110118740A1 (en) | 2009-11-10 | 2011-05-19 | Illuminoss Medical, Inc. | Intramedullary Implants Having Variable Fastener Placement |
US8684965B2 (en) | 2010-06-21 | 2014-04-01 | Illuminoss Medical, Inc. | Photodynamic bone stabilization and drug delivery systems |
-
2007
- 2007-07-13 US US11/777,892 patent/US8128626B2/en not_active Expired - Fee Related
- 2007-07-13 US US11/777,846 patent/US20080269745A1/en not_active Abandoned
- 2007-07-13 US US11/777,872 patent/US20080269746A1/en not_active Abandoned
-
2008
- 2008-02-07 US US12/027,629 patent/US20080269749A1/en not_active Abandoned
- 2008-02-07 US US12/027,521 patent/US8167881B2/en not_active Expired - Fee Related
- 2008-02-07 US US12/027,600 patent/US8162943B2/en not_active Expired - Fee Related
- 2008-02-07 US US12/027,555 patent/US8147492B2/en not_active Expired - Fee Related
- 2008-04-21 JP JP2010506420A patent/JP2010524642A/en active Pending
- 2008-04-21 CA CA002685046A patent/CA2685046A1/en not_active Abandoned
- 2008-04-21 EP EP08746463.2A patent/EP2139432A4/en not_active Withdrawn
- 2008-04-21 WO PCT/US2008/061047 patent/WO2008134287A2/en active Application Filing
-
2012
- 2012-03-19 US US13/423,914 patent/US8834468B2/en not_active Expired - Fee Related
-
2014
- 2014-03-20 US US14/220,132 patent/US9421045B2/en not_active Expired - Fee Related
-
2016
- 2016-07-13 US US15/208,861 patent/US20160317201A1/en not_active Abandoned
Patent Citations (70)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US426665A (en) * | 1890-04-29 | Clamp | ||
US4177524A (en) * | 1976-05-14 | 1979-12-11 | Pfaudler-Werke A.G. | Medical securement element with abrasive grains on thread surface |
US4222128A (en) * | 1977-05-20 | 1980-09-16 | Kureha Kagaku Kogyo Kabushiki Kaisha | Composite implant materials and process for preparing same |
US4204531A (en) * | 1977-12-28 | 1980-05-27 | Yacov Aginsky | Intramedullary nail with expanding mechanism |
US4453539A (en) * | 1982-03-01 | 1984-06-12 | The University Of Toledo | Expandable intramedullary nail for the fixation of bone fractures |
US4522200A (en) * | 1983-06-10 | 1985-06-11 | Ace Orthopedic Company | Adjustable intramedullar rod |
US4932969A (en) * | 1987-01-08 | 1990-06-12 | Sulzer Brothers Limited | Joint endoprosthesis |
US4854312A (en) * | 1988-04-13 | 1989-08-08 | The University Of Toledo | Expanding intramedullary nail |
US5108404A (en) * | 1989-02-09 | 1992-04-28 | Arie Scholten | Surgical protocol for fixation of bone using inflatable device |
US5108398A (en) * | 1990-10-16 | 1992-04-28 | Orthopaedic Research Institute | Orthopaedic knee fusion apparatus |
US5653709A (en) * | 1992-12-04 | 1997-08-05 | Synthes (U.S.A.) | Modular marrow nail |
US5620445A (en) * | 1994-07-15 | 1997-04-15 | Brosnahan; Robert | Modular intramedullary nail |
US5855579A (en) * | 1994-07-15 | 1999-01-05 | Smith & Nephew, Inc. | Cannulated modular intramedullary nail |
US6962603B1 (en) * | 1995-03-01 | 2005-11-08 | Boston Scientific Scimed, Inc. | Longitudinally flexible expandable stent |
US6776793B2 (en) * | 1995-03-01 | 2004-08-17 | Scimed Life Systems, Inc. | Longitudinally flexible expandable stent |
US7094255B2 (en) * | 1996-03-05 | 2006-08-22 | Evysio Medical Devices Ulc | Expandable stent and method for delivery of same |
US6770088B1 (en) * | 1996-04-26 | 2004-08-03 | Scimed Life Systems, Inc. | Intravascular stent |
US7081130B2 (en) * | 1996-04-26 | 2006-07-25 | Boston Scientific Scimed, Inc. | Intravascular Stent |
US7044963B1 (en) * | 1996-09-19 | 2006-05-16 | Medinol, Ltd. | Stent with variable features to optimize support and method of making such stent |
US6764506B2 (en) * | 1997-02-07 | 2004-07-20 | Endosystems Llc | Non-foreshortening intraluminal prosthesis |
US6746479B2 (en) * | 1997-04-25 | 2004-06-08 | Scimed Life Systems, Inc. | Stent cell configurations including spirals |
US6312455B2 (en) * | 1997-04-25 | 2001-11-06 | Nitinol Devices & Components | Stent |
US6245102B1 (en) * | 1997-05-07 | 2001-06-12 | Iowa-India Investments Company Ltd. | Stent, stent graft and stent valve |
US7108714B1 (en) * | 1997-06-13 | 2006-09-19 | Orbus Medical Technologies, Inc. | Expandable intraluminal endoprosthesis |
US6299635B1 (en) * | 1997-09-29 | 2001-10-09 | Cook Incorporated | Radially expandable non-axially contracting surgical stent |
US6613081B2 (en) * | 1997-11-14 | 2003-09-02 | Transvascular, Inc. | Deformable scaffolding multicellular stent |
US6682554B2 (en) * | 1998-09-05 | 2004-01-27 | Jomed Gmbh | Methods and apparatus for a stent having an expandable web structure |
US6261289B1 (en) * | 1998-10-26 | 2001-07-17 | Mark Levy | Expandable orthopedic device |
US6554833B2 (en) * | 1998-10-26 | 2003-04-29 | Expanding Orthopedics, Inc. | Expandable orthopedic device |
US7060088B1 (en) * | 1998-11-13 | 2006-06-13 | Cordis Corporation | Stent with improved flexible connecting links |
US6896696B2 (en) * | 1998-11-20 | 2005-05-24 | Scimed Life Systems, Inc. | Flexible and expandable stent |
US6475237B2 (en) * | 1999-05-03 | 2002-11-05 | William J. Drasler | Intravascular hinge stent |
US6709454B1 (en) * | 1999-05-17 | 2004-03-23 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent with enhanced delivery precision and stent delivery system |
US6491718B1 (en) * | 1999-10-05 | 2002-12-10 | Amjad Ahmad | Intra vascular stent |
US6783530B1 (en) * | 1999-10-22 | 2004-08-31 | Expanding Orthopedics Inc. | Expandable orthopedic device |
US6736818B2 (en) * | 1999-11-11 | 2004-05-18 | Synthes (U.S.A.) | Radially expandable intramedullary nail |
US20020165544A1 (en) * | 1999-11-11 | 2002-11-07 | Stephan Perren | Radially expandable intramedullary nail |
US20020032444A1 (en) * | 1999-12-09 | 2002-03-14 | Mische Hans A. | Methods and devices for treatment of bone fractures |
US6755862B2 (en) * | 2000-01-03 | 2004-06-29 | Orthoscope Ltd. | Intramedullary support strut |
US20030109932A1 (en) * | 2000-01-03 | 2003-06-12 | Ory Keynan | Intramedullary support strut |
US6206880B1 (en) * | 2000-02-21 | 2001-03-27 | Abbas Karladani | Method for percutaneous intramedullary nailing of tibial shaft fractures |
US6746477B2 (en) * | 2000-03-09 | 2004-06-08 | Lpl Systems, Inc. | Expandable stent |
US6911048B2 (en) * | 2000-03-13 | 2005-06-28 | Exactech, Inc. | Modular hip prosthesis |
US6551321B1 (en) * | 2000-06-23 | 2003-04-22 | Centerpulse Orthopedics Inc. | Flexible intramedullary nail |
US7101391B2 (en) * | 2000-09-18 | 2006-09-05 | Inflow Dynamics Inc. | Primarily niobium stent |
US6808561B2 (en) * | 2000-10-16 | 2004-10-26 | University Of South Carolina | Biocompatible cement containing reactive calcium phosphate nanoparticles and methods for making and using such cement |
US6764507B2 (en) * | 2000-10-16 | 2004-07-20 | Conor Medsystems, Inc. | Expandable medical device with improved spatial distribution |
US6506211B1 (en) * | 2000-11-13 | 2003-01-14 | Scimed Life Systems, Inc. | Stent designs |
US6626937B1 (en) * | 2000-11-14 | 2003-09-30 | Advanced Cardiovascular Systems, Inc. | Austenitic nitinol medical devices |
US6770089B1 (en) * | 2000-12-28 | 2004-08-03 | Advanced Cardiovascular Systems, Inc. | Hybrid stent fabrication using metal rings and polymeric links |
US6955686B2 (en) * | 2001-03-01 | 2005-10-18 | Cordis Corporation | Flexible stent |
US6998060B2 (en) * | 2001-03-01 | 2006-02-14 | Cordis Corporation | Flexible stent and method of manufacture |
US6790227B2 (en) * | 2001-03-01 | 2004-09-14 | Cordis Corporation | Flexible stent |
US6979349B1 (en) * | 2001-06-29 | 2005-12-27 | Advanced Cardiovascular Systems, Inc. | Universal stent link design |
US6866805B2 (en) * | 2001-12-27 | 2005-03-15 | Advanced Cardiovascular Systems, Inc. | Hybrid intravascular stent |
US7029493B2 (en) * | 2002-01-25 | 2006-04-18 | Cordis Corporation | Stent with enhanced crossability |
US7005136B2 (en) * | 2002-03-29 | 2006-02-28 | Ethicon, Inc. | Bone replacement materials utilizing bioabsorbable liquid polymers |
US6761731B2 (en) * | 2002-06-28 | 2004-07-13 | Cordis Corporation | Balloon-stent interaction to help reduce foreshortening |
US7025777B2 (en) * | 2002-07-31 | 2006-04-11 | Unison Therapeutics, Inc. | Flexible and conformable stent and method of forming same |
US6805706B2 (en) * | 2002-08-15 | 2004-10-19 | Gmp Cardiac Care, Inc. | Stent-graft with rails |
US6997946B2 (en) * | 2002-11-27 | 2006-02-14 | Boston Scientific Scimed, Inc. | Expandable stents |
US20040199246A1 (en) * | 2003-04-02 | 2004-10-07 | Scimed Life Systems, Inc. | Expandable stent |
US7112216B2 (en) * | 2003-05-28 | 2006-09-26 | Boston Scientific Scimed, Inc. | Stent with tapered flexibility |
US6939373B2 (en) * | 2003-08-20 | 2005-09-06 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US20080255560A1 (en) * | 2004-05-21 | 2008-10-16 | Myers Surgical Solutions, Llc | Fracture Fixation and Site Stabilization System |
US20060264952A1 (en) * | 2005-05-18 | 2006-11-23 | Nelson Charles L | Methods of Using Minimally Invasive Actuable Bone Fixation Devices |
US20060264951A1 (en) * | 2005-05-18 | 2006-11-23 | Nelson Charles L | Minimally Invasive Actuable Bone Fixation Devices Having a Retractable Interdigitation Process |
US20060264950A1 (en) * | 2005-05-18 | 2006-11-23 | Nelson Charles L | Minimally Invasive Actuable Bone Fixation Devices |
US20060264945A1 (en) * | 2005-05-18 | 2006-11-23 | Edidin Avram A | Selectively-expandable bone scaffold |
US20080033522A1 (en) * | 2006-08-03 | 2008-02-07 | Med Institute, Inc. | Implantable Medical Device with Particulate Coating |
Cited By (105)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8961516B2 (en) | 2005-05-18 | 2015-02-24 | Sonoma Orthopedic Products, Inc. | Straight intramedullary fracture fixation devices and methods |
US9060820B2 (en) * | 2005-05-18 | 2015-06-23 | Sonoma Orthopedic Products, Inc. | Segmented intramedullary fracture fixation devices and methods |
US20130012942A1 (en) * | 2005-05-18 | 2013-01-10 | Sonoma Orthopedic Products, Inc. | Segmented intramedullary fracture fixation devices and methods |
US9259250B2 (en) | 2006-11-22 | 2016-02-16 | Sonoma Orthopedic Products, Inc. | Fracture fixation device, tools and methods |
US20100179549A1 (en) * | 2007-02-23 | 2010-07-15 | Zimmer, Gmbh | Implant for fracture treatment |
US9023046B2 (en) * | 2007-02-23 | 2015-05-05 | Zimmer Gmbh | Implant for fracture treatment |
US8128626B2 (en) | 2007-04-24 | 2012-03-06 | Flexfix, Llc | System and method for delivery conformation and removal of intramedullary bone fixation devices |
US8147492B2 (en) | 2007-04-24 | 2012-04-03 | Flexfix, Llc | System and method for guidance and implantation of implantable devices |
US8162943B2 (en) | 2007-04-24 | 2012-04-24 | Flexfix, Llc | Deformable implant systems and methods |
US8167881B2 (en) | 2007-04-24 | 2012-05-01 | Flexfix, Llc | Implantable composite apparatus and method |
US9421045B2 (en) | 2007-04-24 | 2016-08-23 | Flexfix, Llc | Bone stabilization device and method |
US20080269776A1 (en) * | 2007-04-24 | 2008-10-30 | Osteolign | System and Method for Guidance and Implantation of Implantable Devices |
US8834468B2 (en) | 2007-04-24 | 2014-09-16 | Flexfix, Llc | Bone stabilization device and method |
US10278747B2 (en) | 2007-07-03 | 2019-05-07 | Medacta International S.A. | Medical implant |
US9398927B2 (en) | 2007-07-03 | 2016-07-26 | Synergy Biosurgical Ag | Medical implant |
US20100241229A1 (en) * | 2007-07-03 | 2010-09-23 | Synergy Biosurgical Ag | Medical implant |
US9457125B2 (en) | 2007-09-17 | 2016-10-04 | Synergy Biosurgical Ag | Medical implant with electromagnetic radiation responsive polymer and related methods |
US8777618B2 (en) | 2007-09-17 | 2014-07-15 | Synergy Biosurgical Ag | Medical implant II |
US20100286775A1 (en) * | 2007-10-11 | 2010-11-11 | Tavor [I.T.N] Ltd., | Ligament and Tendon Prosthesis |
US8287538B2 (en) | 2008-01-14 | 2012-10-16 | Conventus Orthopaedics, Inc. | Apparatus and methods for fracture repair |
US9517093B2 (en) * | 2008-01-14 | 2016-12-13 | Conventus Orthopaedics, Inc. | Apparatus and methods for fracture repair |
US10603087B2 (en) | 2008-01-14 | 2020-03-31 | Conventus Orthopaedics, Inc. | Apparatus and methods for fracture repair |
US11399878B2 (en) | 2008-01-14 | 2022-08-02 | Conventus Orthopaedics, Inc. | Apparatus and methods for fracture repair |
US20150320459A1 (en) * | 2008-01-14 | 2015-11-12 | Conventus Orthopaedics, Inc. | Apparatus and methods for fracture repair |
US9788870B2 (en) | 2008-01-14 | 2017-10-17 | Conventus Orthopaedics, Inc. | Apparatus and methods for fracture repair |
US9730740B2 (en) | 2008-07-25 | 2017-08-15 | Smith & Nephew, Inc. | Fracture fixation systems |
US8546456B2 (en) | 2008-07-25 | 2013-10-01 | Smith & Nephew, Inc. | Fracture fixation systems |
WO2010094032A3 (en) * | 2009-02-16 | 2010-11-11 | Aoi Medical Inc. | Trauma nail accumulator |
US20140074252A1 (en) * | 2009-11-30 | 2014-03-13 | Adrian Baumgartner | Expandable implant |
US20160302926A1 (en) * | 2009-11-30 | 2016-10-20 | DePuy Synthes Products, Inc. | Expandable Implant |
KR101737335B1 (en) * | 2009-11-30 | 2017-05-18 | 신세스 게엠바하 | Expandable implant |
US9402725B2 (en) * | 2009-11-30 | 2016-08-02 | DePuy Synthes Products, Inc. | Expandable implant |
US8608743B2 (en) * | 2009-11-30 | 2013-12-17 | DePuy Synthes Products, LLC | Expandable implant |
US10022228B2 (en) * | 2009-11-30 | 2018-07-17 | DePuy Synthes Products, Inc. | Expandable implant |
CN102639073A (en) * | 2009-11-30 | 2012-08-15 | 斯恩蒂斯有限公司 | Expandable implant |
WO2011066522A3 (en) * | 2009-11-30 | 2011-07-21 | Synthes Usa, Llc | Expandable implant |
US20110160870A1 (en) * | 2009-11-30 | 2011-06-30 | Adrian Baumgartner | Expandable implant |
US9730739B2 (en) | 2010-01-15 | 2017-08-15 | Conventus Orthopaedics, Inc. | Rotary-rigid orthopaedic rod |
EP2523614A4 (en) * | 2010-01-15 | 2017-02-15 | Conventus Orthopaedics, Inc. | Rotary-rigid orthopaedic rod |
US8961518B2 (en) | 2010-01-20 | 2015-02-24 | Conventus Orthopaedics, Inc. | Apparatus and methods for bone access and cavity preparation |
US9848889B2 (en) | 2010-01-20 | 2017-12-26 | Conventus Orthopaedics, Inc. | Apparatus and methods for bone access and cavity preparation |
US8906022B2 (en) | 2010-03-08 | 2014-12-09 | Conventus Orthopaedics, Inc. | Apparatus and methods for securing a bone implant |
US9993277B2 (en) | 2010-03-08 | 2018-06-12 | Conventus Orthopaedics, Inc. | Apparatus and methods for securing a bone implant |
US9265616B2 (en) | 2010-08-10 | 2016-02-23 | DePuy Synthes Products, Inc. | Expandable implant |
US10010327B2 (en) | 2010-12-16 | 2018-07-03 | Lawrence Livermore National Security, Llc | Expandable implant and implant system |
US10898199B2 (en) | 2010-12-16 | 2021-01-26 | Lawrence Livermore National Security, Llc | Expandable implant and implant system |
US11771435B2 (en) | 2010-12-16 | 2023-10-03 | Lawrence Livermore National Security, Llc | Expandable implant and implant system |
WO2012083051A3 (en) * | 2010-12-16 | 2013-03-07 | Lawrence Livermore National Security, Llc | Expandable implant and implant system |
EP2734133A4 (en) * | 2011-07-19 | 2015-04-01 | Illuminoss Medical Inc | Combination photodynamic devices |
EP2734133A1 (en) * | 2011-07-19 | 2014-05-28 | Illuminoss Medical, Inc. | Combination photodynamic devices |
US9283006B2 (en) | 2011-09-22 | 2016-03-15 | Mx Orthopedics, Corp. | Osteosynthetic shape memory material intramedullary bone stent and method for treating a bone fracture using the same |
US10603088B2 (en) | 2011-09-22 | 2020-03-31 | Arthrex, Inc. | Intermedullary devices for generating and applying compression within a body |
US9724138B2 (en) | 2011-09-22 | 2017-08-08 | Arthrex, Inc. | Intermedullary devices for generating and applying compression within a body |
CN104203132A (en) * | 2011-11-14 | 2014-12-10 | 不列颠哥伦比亚大学 | Intramedullary fixation system for management of pelvic and acetabular fractures |
US9839435B2 (en) | 2011-11-14 | 2017-12-12 | The University Of British Columbia | Intramedullary fixation system for management of pelvic and acetabular fractures |
WO2013071432A1 (en) | 2011-11-14 | 2013-05-23 | The University Of British Columbia | Intramedullary fixation system for management of pelvic and acetabular fractures |
US11529148B2 (en) | 2011-11-14 | 2022-12-20 | The University Of British Columbia | Intramedullary fixation system for management of pelvic and acetabular fractures |
EP2779928A4 (en) * | 2011-11-14 | 2015-07-15 | Univ British Columbia | Intramedullary fixation system for management of pelvic and acetabular fractures |
US11337835B2 (en) | 2012-07-23 | 2022-05-24 | Abbott Cardiovascular Systems Inc. | Shape memory bioresorbable polymer peripheral scaffolds |
US10500076B2 (en) * | 2012-07-23 | 2019-12-10 | Abbott Cardiovascular Systems Inc. | Shape memory bioresorbable polymer peripheral scaffolds |
US9532881B2 (en) * | 2012-08-12 | 2017-01-03 | Brian Albert Hauck | Memory material implant system and methods of use |
US20140067073A1 (en) * | 2012-08-12 | 2014-03-06 | Brian Albert Hauck | Memory material implant system and methods of use |
US10772729B2 (en) | 2012-08-23 | 2020-09-15 | DePuy Synthes Products, Inc. | Bone implant |
US10716606B2 (en) | 2012-08-23 | 2020-07-21 | DePuy Synthes Products, Inc. | Bone fixation system |
US9861406B2 (en) | 2012-08-23 | 2018-01-09 | DePuy Synthes Products, Inc. | Bone fixation system |
US20140058391A1 (en) * | 2012-08-23 | 2014-02-27 | Andreas Appenzeller | Intramedullary Fixation System |
US9452005B2 (en) | 2012-08-23 | 2016-09-27 | DePuy Synthes Products, Inc. | Bone fixation system |
US10004603B2 (en) | 2012-08-23 | 2018-06-26 | DePuy Synthes Products, Inc. | Bone implant |
US9510876B2 (en) * | 2012-08-23 | 2016-12-06 | DePuy Synthes Products, Inc. | Intramedullary fixation system |
US20150157370A1 (en) * | 2012-09-23 | 2015-06-11 | Impetus Innovations, Inc. | Segmental reconstructive intramedullary nail and delivery system |
WO2014043794A1 (en) * | 2012-09-23 | 2014-03-27 | Impetus Innovations, Inc. | A segmental reconstructive intramedullary nail and delivery system |
US20160166291A1 (en) * | 2013-06-24 | 2016-06-16 | The University Of Toledo | Bioactive Fusion Device |
US9743961B2 (en) * | 2013-06-24 | 2017-08-29 | The University Of Toledo | Bioactive fusion device |
US10076342B2 (en) | 2013-12-12 | 2018-09-18 | Conventus Orthopaedics, Inc. | Tissue displacement tools and methods |
US10022132B2 (en) | 2013-12-12 | 2018-07-17 | Conventus Orthopaedics, Inc. | Tissue displacement tools and methods |
US10307188B2 (en) | 2014-03-06 | 2019-06-04 | The University Of British Columbia | Shape adaptable intramedullary fixation device |
US11369421B2 (en) | 2014-03-06 | 2022-06-28 | The University of British Columbia and British Columbia Cancer Agency Branch | Shape adaptable intramedullary fixation device |
US20170027624A1 (en) * | 2014-04-11 | 2017-02-02 | Smith & Nephew, Inc. | Dmls orthopedic intramedullary device and method of manufacture |
CN104207867A (en) * | 2014-08-13 | 2014-12-17 | 中国科学院福建物质结构研究所 | Low-modulus medical implant porous scaffold structure |
US20190231401A1 (en) * | 2014-10-14 | 2019-08-01 | University Of British Columbia | Systems and methods for intermedullary bone fixation |
US10973559B2 (en) * | 2014-10-14 | 2021-04-13 | University Of British Columbia | Systems and methods for intermedullary bone fixation |
US20170238977A1 (en) * | 2014-10-14 | 2017-08-24 | Empire Technology Development Llc | Systems and methods for intermedullary bone fixation |
US10258394B2 (en) * | 2014-10-14 | 2019-04-16 | The University Of British Columbia | Systems and methods for intermedullary bone fixation |
US9925046B2 (en) | 2015-03-31 | 2018-03-27 | DePuy Synthes Products, Inc. | Bone graft cage |
US10292822B2 (en) | 2015-03-31 | 2019-05-21 | DePuy Synthes Products, Inc. | Bone graft cage |
WO2016160180A1 (en) * | 2015-03-31 | 2016-10-06 | DePuy Synthes Products, Inc. | Bone graft cage |
US10258472B2 (en) | 2015-03-31 | 2019-04-16 | DePuy Synthes Products, Inc. | Bone graft cage |
US20160346018A1 (en) * | 2015-06-01 | 2016-12-01 | The Texas A &M University System | Defect fixation device |
US10561765B2 (en) | 2015-07-27 | 2020-02-18 | The Texas A&M University System | Medical devices coated with shape memory polymer foams |
US11369720B2 (en) | 2015-07-27 | 2022-06-28 | The Texas A&M University System | Medical devices coated with shape memory polymer foams |
US20170156766A1 (en) * | 2015-12-03 | 2017-06-08 | David M. Anderson | Hammertoe implant promoting bony in-growth |
US10321940B2 (en) * | 2015-12-03 | 2019-06-18 | Biomet Manufacturing, Llc | Hammertoe implant promoting bony in-growth |
US11419646B2 (en) | 2015-12-03 | 2022-08-23 | Biomet Manufacturing, Llc | Hammertoe implant promoting bony in-growth |
US10695181B2 (en) | 2016-02-16 | 2020-06-30 | DePuy Synthes Products, Inc. | Bone graft cage |
US10568671B2 (en) | 2016-03-29 | 2020-02-25 | Merete Holding Gmbh | Implantable compensating sleeve for an endoprosthesis |
US10743997B2 (en) * | 2016-03-29 | 2020-08-18 | Merete Holding Gmbh | Implantable compensating sleeve for an endoprosthesis |
DE102016003838A1 (en) * | 2016-03-29 | 2017-10-05 | Merete Holding Gmbh | Implantable compensating cuff for an endoprosthesis |
US11051944B2 (en) | 2016-06-13 | 2021-07-06 | DePuy Synthes Products, Inc. | Bone graft cage |
US10507110B2 (en) | 2016-06-13 | 2019-12-17 | DePuy Synthes Products, Inc. | Bone graft cage |
US11419645B2 (en) | 2016-10-05 | 2022-08-23 | University Of British Columbia | Intramedullary fixation device with shape locking interface |
US11219520B2 (en) | 2017-03-14 | 2022-01-11 | Shape Memory Medical, Inc. | Shape memory polymer foams to seal space around valves |
CN106943210A (en) * | 2017-04-21 | 2017-07-14 | 无锡市第九人民医院 | A kind of titanium cage for being used to wrap up long bone cortex bone ectonexine bone grafting |
US10918426B2 (en) | 2017-07-04 | 2021-02-16 | Conventus Orthopaedics, Inc. | Apparatus and methods for treatment of a bone |
US11832856B2 (en) | 2018-10-17 | 2023-12-05 | The University Of British Columbia | Bone-fixation device and system |
US11504240B2 (en) | 2020-06-04 | 2022-11-22 | DePuy Synthes Products, Inc. | Modular bone graft cage |
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US20080269750A1 (en) | 2008-10-30 |
US20140207138A1 (en) | 2014-07-24 |
EP2139432A2 (en) | 2010-01-06 |
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US20160317201A1 (en) | 2016-11-03 |
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US9421045B2 (en) | 2016-08-23 |
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US20120239037A1 (en) | 2012-09-20 |
US8147492B2 (en) | 2012-04-03 |
EP2139432A4 (en) | 2013-05-22 |
WO2008134287A2 (en) | 2008-11-06 |
CA2685046A1 (en) | 2008-11-06 |
JP2010524642A (en) | 2010-07-22 |
US20080269746A1 (en) | 2008-10-30 |
WO2008134287A3 (en) | 2009-01-22 |
US8128626B2 (en) | 2012-03-06 |
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