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Publication numberUS20060095138 A1
Publication typeApplication
Application numberUS 11/148,973
Publication dateMay 4, 2006
Filing dateJun 9, 2005
Priority dateJun 9, 2004
Also published asUS8163031, US20110054482
Publication number11148973, 148973, US 2006/0095138 A1, US 2006/095138 A1, US 20060095138 A1, US 20060095138A1, US 2006095138 A1, US 2006095138A1, US-A1-20060095138, US-A1-2006095138, US2006/0095138A1, US2006/095138A1, US20060095138 A1, US20060095138A1, US2006095138 A1, US2006095138A1
InventorsCsaba Truckai, John Shadduck
Original AssigneeCsaba Truckai, Shadduck John H
Export CitationBiBTeX, EndNote, RefMan
External Links: USPTO, USPTO Assignment, Espacenet
Composites and methods for treating bone
US 20060095138 A1
Abstract
A system and method for treating bone abnormalities including vertebral compression fractures and the like. In one vertebroplasty method, a fill material is injected under high pressures into cancellous bone wherein the fill material includes a flowable bone cement component and an elastomeric polymer component that is carried therein. The elastomer component can further carry microscale or mesoscale reticulated elements. Under suitable injection pressures, the elastomeric component ultimately migrates within the flowable material to alter the apparent viscosity across the plume of fill material to accomplish multiple functions. For example, the differential in apparent viscosity across the fill material creates a broad load-distributing layer within cancellous bone for applying retraction forces to cortical bone endplates. The differential in apparent viscosity also transitions into a flow impermeable layer at the interface of cancellous bone and the flowable material to prevent extravasion of the flowable bone cement component.
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Claims(20)
1-31. (canceled)
32. A method of treating mammalian bone, comprising introducing a flowable media under pressure into cancellous bone, the media including a volume of elastomeric elements wherein the elastomeric elements cause differential apparent viscosity within regions of the flowable media.
33. The method of claim 32 wherein the elastomeric elements cause surface regions of the flowable media to have substantially higher apparent viscosity than interior regions thereof.
34. The method of claim 32 wherein the elastomeric elements cause surface regions of the flowable media to be substantially less permeable to flows therethrough.
35. The method of claim 32 wherein introducing the flowable media applies expansion forces to the bone substantially without extravasation.
36. The method of claim 32 wherein introducing the flowable media expands the cancellous bone.
37. The method of claim 32 wherein introducing the flowable media includes introducing a hardenable cement.
38. The method of claim 37 including permitting the cement to harden thereby providing support to the cortical bone about the cancellous bone.
39. The method of claim 32 wherein introducing the flowable media reduces a fracture.
40. The method of claim 32 wherein introducing the flowable media moves cortical bone.
41. The method of claim 32 wherein introducing the flowable media increases height of a fractured vertebra.
42. The method of claim 32 further including the step of applying energy to the elastomeric elements to heat the flowable media.
43. The method of claim 42 wherein applying energy is carried out by at least one of a radiofrequency energy source and a light energy source.
44. A method of treating mammalian bone, comprising flowing a volume of flowable composite media into cancellous bone and transforming the surface regions of the flowable composite media to a substantially flow impermeable form while introducing additional flowable media into the interior of volume.
45. The method of claim 44 wherein transforming the surface regions to a substantially flow impermeable form includes causing the aggregation of elastomeric elements in said surface regions.
46. The method of claim 44 wherein transforming the surface regions to a substantially flow impermeable form includes causing the expansion of shape memory polymer elements.
47. The method of claim 44 wherein transforming the surface regions to a substantially flow impermeable form includes delivering energy to said surface regions from a remote energy source.
48. The method of claim 44 wherein flowing the volume of composite media expands cancellous bone.
49. The method of claim 44 wherein flowing the volume of composite media moves cortical bone.
50. A method of treating mammalian bone, comprising:
introducing a volume of elastomeric elements into the interior of a bone; and
introducing a flowable media within the volume of elastomeric elements, wherein the elastomeric elements aggregate in outward regions of a plume of the flowable media to cause said outward regions to be substantially flow-impermeable.
Description
    CROSS-REFERENCE TO RELATED APPLICATIONS
  • [0001]
    This application claims benefit of Provisional U.S. Patent Application Ser. No. 60/578,182 filed Jun. 9, 2004 (Docket No. S-7700-030) titled Scaffold Composites and Methods for Treating Abnormalities in Bone, the entire contents of which are hereby incorporated by reference in their entirety and should be considered a part of this specification.
  • BACKGROUND OF THE INVENTION
  • [0002]
    1. Field of the Invention
  • [0003]
    This invention relates to bone implant materials and methods and more particularly to composite materials including an elastomer component for treating abnormalities in bones such as compression fractures of vertebra, necrosis of femurs, joint implants and the like. An exemplary method includes introducing a flowable composite material into the interior of a bone wherein increasing pressures result in the elastomer component causing a differential apparent viscosity within selected regions across the flowable material to thereby allow controlled application of forces to the bone for reducing a fracture.
  • [0004]
    2. Description of the Related Art
  • [0005]
    Osteoporotic fractures are prevalent in the elderly, with an annual estimate of 1.5 million fractures in the United States alone. These include 750,000 vertebral compression fractures (VCFs) and 250,000 hip fractures. The annual cost of osteoporotic fractures in the United States has been estimated at $13.8 billion. The prevalence of VCFs in women age 50 and older has been estimated at 26%. The prevalence increases with age, reaching 40% among 80-year-old women. Medical advances aimed at slowing or arresting bone loss from aging have not provided solutions to this problem. Further, the affected population will grow steadily as life expectancy increases. Osteoporosis affects the entire skeleton but most commonly causes fractures in the spine and hip. Spinal or vertebral fractures also have serious consequences, with patients suffering from loss of height, deformity and persistent pain which can significantly impair mobility and quality of life. Fracture pain usually lasts 4 to 6 weeks, with intense pain at the fracture site. Chronic pain often occurs when one level is greatly collapsed or multiple levels are collapsed.
  • [0006]
    Postmenopausal women are predisposed to fractures, such as in the vertebrae, due to a decrease in bone mineral density that accompanies postmenopausal osteoporosis. Osteoporosis is a pathologic state that literally means “porous bones”. Skeletal bones are made up of a thick cortical shell and a strong inner meshwork, or cancellous bone, of collagen, calcium salts and other minerals. Cancellous bone is similar to a honeycomb, with blood vessels and bone marrow in the spaces. Osteoporosis describes a condition of decreased bone mass that leads to fragile bones which are at an increased risk for fractures. In an osteoporotic bone, the sponge-like cancellous bone has pores or voids that increase in dimension, making the bone very fragile. In young, healthy bone tissue, bone breakdown occurs continually as the result of osteoclast activity, but the breakdown is balanced by new bone formation by osteoblasts. In an elderly patient, bone resorption can surpass bone formation thus resulting in deterioration of bone density. Osteoporosis occurs largely without symptoms until a fracture occurs.
  • [0007]
    Vertebroplasty and kyphoplasty are recently developed techniques for treating vertebral compression fractures. Percutaneous vertebroplasty was first reported by a French group in 1987 for the treatment of painful hemangiomas. In the 1990's, percutaneous vertebroplasty was extended to indications including osteoporotic vertebral compression fractures, traumatic compression fractures, and painful vertebral metastasis. In one percutaneous vertebroplasty technique, bone cement such as PMMA (polymethylmethacrylate) is percutaneously injected into a fractured vertebral body via a trocar and cannula system. The targeted vertebrae are identified under fluoroscopy. A needle is introduced into the vertebral body under fluoroscopic control to allow direct visualization. A transpedicular (through the pedicle of the vertebrae) approach is typically bilateral but can be done unilaterally. The bilateral transpedicular approach is typically used because inadequate PMMA infill is achieved with a unilateral approach.
  • [0008]
    In a bilateral approach, approximately 1 to 4 ml of PMMA are injected on each side of the vertebra. Since the PMMA needs to be forced into cancellous bone, the technique requires high pressures and fairly low viscosity cement. Since the cortical bone of the targeted vertebra may have a recent fracture, there is the potential of PMMA leakage. The PMMA cement contains radiopaque materials so that when injected under live fluoroscopy, cement localization and leakage can be observed. The visualization of PMMA injection and extravasion are critical to the technique and the physician terminates PMMA injection when leakage is evident. The cement is injected using small syringe-like injectors to allow the physician to manually control the injection pressures.
  • [0009]
    Kyphoplasty is a modification of percutaneous vertebroplasty. Kyphoplasty involves a preliminary step that comprises the percutaneous placement of an inflatable balloon tamp in the vertebral body. Inflation of the balloon creates a cavity in the bone prior to cement injection. Further, the proponents of percutaneous kyphoplasty have suggested that high pressure balloon-tamp inflation can at least partially restore vertebral body height. In kyphoplasty, it has been proposed that PMMA can be injected at lower pressures into the collapsed vertebra since a cavity exists to receive the cement—which is not the case in conventional vertebroplasty.
  • [0010]
    The principal indications for any form of vertebroplasty are osteoporotic vertebral collapse with debilitating pain. Radiography and computed tomography must be performed in the days preceding treatment to determine the extent of vertebral collapse, the presence of epidural or foraminal stenosis caused by bone fragment retropulsion, the presence of cortical destruction or fracture and the visibility and degree of involvement of the pedicles. Leakage of PMMA during vertebroplasty can result in very serious complications including compression of adjacent structures that necessitate emergency decompressive surgery.
  • [0011]
    Leakage or extravasion of PMMA is a critical issue and can be divided into paravertebral leakage, venous infiltration, epidural leakage and intradiscal leakage. The exothermic reaction of PMMA carries potential catastrophic consequences if thermal damage were to extend to the dural sac, cord, and nerve roots. Surgical evacuation of leaked cement in the spinal canal has been reported. It has been found that leakage of PMMA is related to various clinical factors such as the vertebral compression pattern, and the extent of the cortical fracture, bone mineral density, the interval from injury to operation, the amount of PMMA injected and the location of the injector tip. In one recent study, close to 50% of vertebroplasty cases resulted in leakage of PMMA from the vertebral bodies. See Hyun-Woo Do et al, “The Analysis of Polymethylmethacrylate Leakage after Vertebroplasty for Vertebral Body Compression Fractures”, Jour. of Korean Neurosurg. Soc. Vol. 35, No. 5 (May 2004) pp. 478-82, (http://www.jkns.or.kr/htm/abstract.asp?no=0042004086).
  • [0012]
    Another recent study was directed to the incidence of new VCFs adjacent to the vertebral bodies that were initially treated. Vertebroplasty patients often return with new pain caused by a new vertebral body fracture. Leakage of cement into an adjacent disc space during vertebroplasty increases the risk of a new fracture of adjacent vertebral bodies. See Am. J. Neuroradiol. 2004 February; 25(2):175-80. The study found that 58% of vertebral bodies adjacent to a disc with cement leakage fractured during the follow-up period compared with 12% of vertebral bodies adjacent to a disc without cement leakage.
  • [0013]
    Another life-threatening complication of vertebroplasty is pulmonary embolism. See Bernhard, J. et al., “Asymptomatic diffuse pulmonary embolism caused by acrylic cement: an unusual complication of percutaneous vertebroplasty”, Ann. Rheum. Dis. 2003; 62:85-86. The vapors from PMMA preparation and injection are also cause for concern. See Kirby, B., et al., “Acute bronchospasm due to exposure to polymethylmethacrylate vapors during percutaneous vertebroplasty”, Am. J. Roentgenol. 2003; 180:543-544.
  • [0014]
    Another disadvantage of PMMA is its inability to undergo remodeling—and the inability to use the PMMA to deliver osteoinductive agents, growth factors, chemotherapeutic agents and the like. Yet another disadvantage of PMMA is the need to add radiopaque agents which lower its viscosity with unclear consequences on its long-term endurance.
  • [0015]
    In both higher pressure cement injection (vertebroplasty) and balloon-tamped cementing procedures (kyphoplasty), the methods do not provide for well controlled augmentation of vertebral body height. The direct injection of bone cement simply follows the path of least resistance within the fractured bone. The expansion of a balloon also applies compacting forces along lines of least resistance in the collapsed cancellous bone. Thus, the reduction of a vertebral compression fracture is not optimized or controlled in high pressure balloons as forces of balloon expansion occur in multiple directions.
  • [0016]
    In a kyphoplasty procedure, the physician often uses very high pressures (e.g., up to 200 or 300 psi) to inflate the balloon which first crushes and compacts cancellous bone. Expansion of the balloon under high pressures close to cortical bone can fracture the cortical bone, or cause regional damage to the cortical bone that can result in cortical bone necrosis. Such cortical bone damage is highly undesirable and results in weakened cortical endplates.
  • [0017]
    Kyphoplasty also does not provide a distraction mechanism capable of 100% vertebral height restoration. Further, the kyphoplasty balloons under very high pressure typically apply forces to vertebral endplates within a central region of the cortical bone that may be weak, rather than distributing forces over the endplate.
  • [0018]
    There is a general need to provide systems and methods for use in treatment of vertebral compression fractures that provide a greater degree of control over introduction of bone support material, and that provide better outcomes. Embodiments of the present invention meet one or more of the above needs, or other needs, and provide several other advantages in a novel and non-obvious manner.
  • SUMMARY OF THE INVENTION
  • [0019]
    The invention provides systems and method of treating bone abnormalities including vertebral compression fractures, bone tumors and cysts, avascular necrosis of the femoral head and the like. In one embodiment, the invention comprises a bone infill system or implant system with a fill material that includes a flowable component and an elastomeric polymer component that is deformable in-situ (FIG. 1A). In one embodiment, the elastomer component comprises a matrix of base elastomer and a filler of microscale or mesoscale reticulated elements (FIG. 1B). The elastomeric component corresponding to the invention performs multiple functions, for example, (i) forming a load-distributing structure between a bone fill material or structure and the elastomer component; (ii) mechanically creating a seal at the interface of cancellous bone and bone fill material or structure to prevent extravasion of a flowable material, (iii) creating a substantially porous layer around the surface of non-porous bone fill material or structures and/or (vi) creating an insulative layer around the surface of an exothermic bone fill material. The elastomer component can be used in bone support treatments or in treatments to move apart cortical bone surfaces as in treating vertebral compression fractures.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • [0020]
    In the following detailed description, similar reference numerals are used to depict like elements in the various figures.
  • [0021]
    FIG. 1A is a greatly enlarged sectional view of a flowable composite bone infill material such as PMMA with a volume of elastomeric elements or particles carried therein.
  • [0022]
    FIG. 1B is a greatly enlarged sectional view of an elastomeric element of FIG. 1A with reticulated elements dispersed within the elastomer.
  • [0023]
    FIG. 2A is a schematic view of a spine segment with a vertebra having a compression fracture showing a method of the invention wherein a volume of the flowable media of FIG. 1A is injected under pressure into cancellous bone in a targeted treatment site.
  • [0024]
    FIG. 2B is a schematic view of the spine segment of FIG. 2A showing the pressurized injection of additional flowable wherein the apparent viscosity of the media is altered at surface regions of the plume by outward migration of the elastomeric element to thereby create flow-impermeable surface regions.
  • [0025]
    FIGS. 3A-3B are schematic sectional views of a monolith implant structure fabricated of the composite elastomeric material of FIG. 1B; with FIG. 3A illustrating the implant structure introduced into a bore in a bone.
  • [0026]
    FIG. 3B illustrate the elastomeric material of FIG. 3A being inserted in the bore in the bone.
  • [0027]
    FIG. 3C illustrates an interference fit bone screw driven into the elastomeric material of FIGS. 3A-3B which distributes loads about the bore in cancellous bone.
  • [0028]
    FIG. 4 is a sectional cut-away view of one an implant segment with multiple layers having different moduli.
  • DETAILED DESCRIPTION OF THE INVENTION
  • [0029]
    FIG. 1A illustrates a cross-sectional view of fill material 4 that comprises flowable component 5 with elastomeric polymer component 6 dispersed therein. The flowable component or material 5 is an in-situ hardenable bone cement (e.g., PMMA) that is intermixed with elastomeric component 6 that comprises a plurality of small elastomeric elements, such as silicone particles or elements of another biocompatible polymer. The flowable material 5 and elastomeric elements 6 can be intermixed prior to introduction into bone or contemporaneous with introduction into bone from separate channels in an introducer. The elastomeric elements 6 are typically dimensioned to be small enough to allow their passage within the openings of cancellous bone in a targeted treatment site. In one embodiment as depicted in FIG. 1B, the elastomeric elements 6 themselves comprise a composite of base elastomer 10A and reticulated, open-cell scaffold structures indicated at 10B. Such reticulated open-cell structures can allow for later bone ingrowth into the surface of the volume of fill material. The term “reticulated” as used herein describes open-cell structures 10B and means having the appearance of, or functioning as, a wire-like network or a substantially rigid net-like structure. The terms reticulated and trabecular are used interchangeably herein to describe structures having ligaments that bound open cells or closed cells in the interior of the structure.
  • [0030]
    FIG. 2A-2B illustrate a method corresponding to the invention for use in the treatment of a vertebral compression fracture indicated at 13. In FIG. 2A, an initial volume of fill material 4 comprising a flowable bone cement component 5 and intermixed elastomeric elements 6 is injected under substantial pressure into cancellous bone 14 of the vertebra 15 resulting in plume 18. The fill material 4 is introduced in a unilateral or bilateral transpedicular approach through cannula 19 as is well known in the art of vertebroplasty. The fill material 4 propagates within the openings in cancellous bone and may also follow pre-existing fracture lines in cancellous bone, for example as may exist following a compression fracture. FIG. 2B illustrates the same step of injecting fill material 4 but after a greater volume of material has been introduced resulting in plume 18 of fill material being larger and engaging the cortical bone endplates. In the high pressure injection of a such a composite fill material, the elastomeric elements 6 migrate toward surface region 20 of plume 18 and create a differential in the apparent viscosity of the flowable material across the volume or plume. The term “apparent viscosity” is used herein to describe the flow characteristics of the combination of flowable component 5 and intermixed elastomeric elements 6. As the injection pressures and the resistance to inflows of fill material increase, the accumulation of elastomeric elements 6 about surface region 20 also increases. The elastomeric elements 6 can additionally deform and ultimately the pressures cause elastomeric elements 6 to form in-situ a substantially flow-impermeable surface region 20. As the surface region becomes substantially impermeable to flows or extravasion therethrough of flowable component 5, continued injection of fill material will elastically expand the surface regions and apply expansion forces to the bone. In a vertebral body as in FIG. 2B, the expansion pressures can expand cancellous bone 14 in which the flowable material 4 has flowed and apply retraction forces to the cortical bone endplates to at least partly reduce a vertebral fracture.
  • [0031]
    In general, an exemplary method corresponding to the invention for treating mammalian bone comprises the following: (a) flowing an initial volume of flowable media into the interior of a bone wherein the media includes a volume of elastomeric elements, and (b) flowing under pressure increasing volumes of the flowable media wherein injection pressures causes a differential apparent viscosity within selected regions across the flowable media. The method further includes causing surface regions 20 of the plume 18 of flowable media to be substantially impermeable to flows therethrough (FIG. 2B). The method includes allowing an in-situ polymerizable component of the flowable media to harden to thereby support expanded cancellous bone and to maintain retracted cortical bone in an altered position.
  • [0032]
    In another embodiment, the fill material 4 described above includes an elastomer filler composite 6 that carries microscale or mesoscale reticulated elements 10B (FIG. 1B). As the elastomer elements 6 aggregate about surface region 20 of the plume 18, the reticulated material is proximate to bone and can thus allow for subsequent bone ingrowth. In addition, elastomer elements 6 and surface region 20 create an insulative layer that prevents or moderates heating of the bone external to surface region 20 from an exothermic reaction of a typical bone cement used as flowable component 5 that is interior of surface region 20.
  • [0033]
    In any embodiment, elastomer composite elements 6 can carry radiosensitive and magnetic-sensitive fillers for cooperating with an RF source or an inductive heating source for elevating the polymer to a targeted temperature. Alternatively, the polymeric composition can be substantially transparent or substantially translucent and carry chromophores for cooperating with a light source introduced with the material for heating to material to a selected temperature for increasing the modulus of the material. Thus, such methods of heating surface regions 20 (FIG. 2B) in which the elastomer composite elements 6 have aggregated will cause accelerated heating of adjacent interior regions of flowable component 5. This system can be used to selectively polymerize regions of flowable media 5 adjacent the surface region 20. By this means, the peripheral portions of plume 18 interior of, and within, the aggregated elastomeric elements, can be formed into a flow-impermeable layer.
  • [0034]
    The reticulated structures 10B as in FIG. 1B define a mean cross section which can be expressed in microns. In preferred embodiments, the cells are bounded by polyhedral faces, typically pentagonal or hexagonal, that are formed with five or six ligaments 15. The cell dimension is selected for enhancing tissue ingrowth, and mean cell cross-sections can range between 10 microns and 200 microns; and more preferably ranges between 20 microns and 100 microns. Such reticulated materials and structures are available from ERG Materials and Aerospace Corp., 900 Stanford Avenue, Oakland Calif. 94608 and Porvair Advanced Materials, Inc., 700 Shepherd Street, Hendersonville N.C. 28792, and are more fully described in co-pending U.S. patent application Ser. No. 11/______, filed Jun. 7, 2005 (Docket No. S-7700-020A) titled Implants and Methods for Treating Bone, the contents of which are incorporated herein by this reference in their entirety and should be considered a part of this specification.
  • [0035]
    Referring back to FIGS. 1A and 1B, the elastomeric composition comprises any biocompatible polymer having an elastic modulus ranging between about 10 MPa and 1 KPa. The polymer can be a foam, or a shape memory polymer (SMP) that releases stored energy after heating and moving from a compacted temporary shape to an expanded memory shape. A description of suitable shape memory polymers is described in U.S. patent application Ser. No. 10/837, 858 titled Orthopedic Implants, Methods of Use and Methods of Fabrication filed May 3, 2004, the contents of which are incorporated herein by this reference in their entirety and should be considered a part of this specification. In a preferred embodiment, the elastomer elements 5 are at least one of bioerodible, bioabsorbable or bioexcretable.
  • [0036]
    FIGS. 3A-3C illustrate an alternative embodiment of the invention wherein the composite of an elastomer 10A and reticulated elements 10B (FIG. 1B) is formed into exemplary implant body 40A. In FIGS. 3A and 3B, implant 40A is fabricated by molding in a suitable dimension for introduction into bore 25 in a bone, indicated as cancellous bone 26 and a cortical bone surface 28. FIG. 3C illustrates that implant 40A can have an optional channel or opening 44 for receiving or guiding the positioning of fill material 48 comprising a threaded implant. In FIG. 3C, it can be seen that a threaded implant 48 can be screwed into the implant wherein the elastomeric implant 40A and reticulated elements 10B dispersed therein are compressed to form an interference fit between the bone and implant member 40A. Of particular interest, the insertion of the threaded implant 48 causes self-adjustment of the distribution, location and orientation of the reticulated elements 10B within the elastomer matrix, thus optimally self-distributing loads between the implant 48 and the bone. In the prior art, a threaded implant would engage the bone highest engagement pressures generally about the apex of the threads. In the system as in FIG. 3C, the engagement forces would be distributed about all surfaces of threaded implant 48—which also preferably has a surface region that is reticulated, roughened or porous.
  • [0037]
    FIG. 4 illustrates another exemplary implant 40B that is fabricated of an elastomer composite. In this embodiment, the composite body has at least two layers 50 a and 50 b that are polymer matrices that carry reticulated elements having different parameters (density, cell dimensions etc.) to provide different elastic moduli. The scope of the invention thus encompasses an implant structure 40B that has a gradient modulus for transitioning from an interface with cortical bone 55 to the interface with a rigid member 48 which is needed in various implants and reconstructions, such as in hip implants.
  • [0038]
    In another embodiment depicted in FIGS. 5A and 5B, the elastomeric composite implant 60 can be configured with a plurality of composite regions 62 a and 62 b that provide variations or gradients in material properties for enhancing implant fixation in bone 64. In FIG. 5B, it can be seen that regions 62 a of the composite are deformable but more rigid than the adjacent regions 62 b. Thus, the higher modulus regions will be forced outward more into the bone that other regions 62 b upon insertion of bone screw 68. The scope of the invention encompasses varying all the obvious properties of different regions of the composite to achieve the desired regional variations or gradients, and include adjusting the: (i) density of ligaments of the reticulated elements dispersed in the matrix; (ii) the overall shape, dimensions and orientations of the reticulated elements; (iii) the pore size of the reticulated elements; (iv) the modulus, deformability and material of the reticulated elements; (v) the percentage volume of reticulated elements in the matrix, (vi) the properties media carried in the pores of the reticulated elements, and (vii) the modulus and other properties of the polymer base material 10A (FIG. 1B).
  • [0039]
    The above-described embodiments describe elastomer composites that cooperate with fill materials to control properties of the interface between fill material and bone. The scope of the invention extends to elastomer composites as in FIGS. 2A-2B, 3A-3C and 4 that are introduced into bone wherein a base polymer can be elevated to a transition temperature so that the composite then adjusts its orientation. Upon cooling, the elastomer composite can then freeze in a particular form. In such embodiments, it is preferred that reticulated elements in the composite have varied shapes for non-slip engagement between such elements to thereby increase the modulus of the material. In an exemplary embodiment, the polymeric composition has a transition temperature in the range of 40° C. to 120° C.; and preferably in the range of 40° C. to 80° C. The transition temperature is a glass transition temperature or a melt temperature. Again, the polymeric matrix can carry radiosensitive or magnetic-sensitive fillers for cooperating with an RF source or an inductive heating source for elevating the polymer to a targeted temperature. Alternatively, the polymeric composition can be substantially transparent or substantially translucent and carry chromophores for cooperating with a light source for heating to material to a selected temperature for elevating the composition to a transition temperature.
  • [0040]
    In any embodiment, the fill materials or implants can further carry a radiopaque or radiovisible composition if the material of the reticulated elements is not radiovisible.
  • [0041]
    In any embodiment, the fill materials or implants can carry any pharmacological agent or any of the following: antibiotics, cortical bone material, synthetic cortical replacement material, demineralized bone material, autograft and allograft materials. The implant body also can include drugs and agents for inducing bone growth, such as bone morphogenic protein (BMP). The implants can carry the pharmacological agents for immediate or timed release.
  • [0042]
    The above description of the invention intended to be illustrative and not exhaustive. A number of variations and alternatives will be apparent to one having ordinary skills in the art. Such alternatives and variations are intended to be included within the scope of the claims. Particular features that are presented in dependent claims can be combined and fall within the scope of the invention. The invention also encompasses embodiments as if dependent claims were alternatively written in a multiple dependent claim format with reference to other independent claims.
Patent Citations
Cited PatentFiling datePublication dateApplicantTitle
US4250887 *Apr 18, 1979Feb 17, 1981Dardik Surgical Associates, P.A.Remote manual injecting apparatus
US4265618 *Sep 9, 1977May 5, 1981Solar Energy Technology, Inc.Electrically heated endodontic syringe for injecting thermoplastic material into a root canal cavity
US4280233 *Aug 3, 1979Jul 28, 1981Raab SBone connective prosthesis comprising a reinforcement element carrying a polymer layer having a varying modulus of elasticity
US4338925 *Dec 20, 1979Jul 13, 1982Jo MillerPressure injection of bone cement apparatus and method
US4377168 *Feb 27, 1981Mar 22, 1983Wallach Surgical Instruments, Inc.Cryosurgical instrument
US4735625 *Sep 11, 1985Apr 5, 1988Richards Medical CompanyBone cement reinforcement and method
US4849223 *Dec 30, 1985Jul 18, 1989Johnson Matthey Public Limited CompanyAntimicrobial compositions consisting of metallic silver combined with titanium oxide or tantalum oxide
US5037437 *Jan 18, 1990Aug 6, 1991University Of WashingtonMethod of bone preparation for prosthetic fixation
US5108404 *Aug 15, 1990Apr 28, 1992Arie ScholtenSurgical protocol for fixation of bone using inflatable device
US5130950 *May 16, 1990Jul 14, 1992Schlumberger Technology CorporationUltrasonic measurement apparatus
US5431654 *Sep 30, 1991Jul 11, 1995Stryker CorporationBone cement injector
US5514135 *Jun 7, 1995May 7, 1996Earle; Michael L.Bone cement delivery gun
US5542928 *Jun 27, 1994Aug 6, 1996Innerdyne, Inc.Method and device for thermal ablation having improved heat transfer
US5788711 *Oct 7, 1996Aug 4, 1998Implex Gmgh SpezialhorgerateImplantable positioning and fixing system for actuator and sensor implants
US6048346 *Aug 13, 1997Apr 11, 2000Kyphon Inc.Systems and methods for injecting flowable materials into bones
US6075067 *Sep 3, 1997Jun 13, 2000Corpipharm Gmbh & CoCement for medical use, method for producing the cement, and use of the cement
US6171312 *Jan 15, 1999Jan 9, 2001Implant Innovations, Inc.Power-driven osteotome tools for compaction of bone tissue
US6231615 *Oct 18, 1999May 15, 2001Parallax Medical, Inc.Enhanced visibility materials for implantation in hard tissue
US6235043 *Jan 23, 1997May 22, 2001Kyphon, Inc.Inflatable device for use in surgical protocol relating to fixation of bone
US6236020 *Dec 1, 1999May 22, 2001Joshua FriedmanHeating assembly for preheating dental materials
US6241734 *Aug 14, 1998Jun 5, 2001Kyphon, Inc.Systems and methods for placing materials into bone
US6248110 *Jun 9, 1997Jun 19, 2001Kyphon, Inc.Systems and methods for treating fractured or diseased bone using expandable bodies
US6261289 *Oct 22, 1999Jul 17, 2001Mark LevyExpandable orthopedic device
US6264659 *Dec 8, 1999Jul 24, 2001Anthony C. RossMethod of treating an intervertebral disk
US6280456 *Sep 23, 1999Aug 28, 2001Kyphon IncMethods for treating bone
US6358254 *Sep 11, 2000Mar 19, 2002D. Greg AndersonMethod and implant for expanding a spinal canal
US6395007 *Mar 14, 2000May 28, 2002American Osteomedix, Inc.Apparatus and method for fixation of osteoporotic bone
US6425923 *Mar 7, 2000Jul 30, 2002Zimmer, Inc.Contourable polymer filled implant
US6524102 *Dec 8, 2000Feb 25, 2003Kerry N DavisMethod and apparatus for applying thermoplastic border molding to denture impression trays
US6558428 *Jan 30, 2001May 6, 2003Joon B. ParkPrecoated polymeric prosthesis and process for making same
US6676664 *Jul 24, 2000Jan 13, 2004Grupo Grifols, S.A.Device for metering hardenable mass for vertebroplastia and other similar bone treatments
US6706069 *Sep 13, 2001Mar 16, 2004J. Lee BergerSpinal grooved director with built in balloon
US6709149 *Dec 14, 1998Mar 23, 2004Ao Research Institute DavosMethod of bone cement preparation
US6712852 *Sep 30, 2002Mar 30, 2004Depuy Spine, Inc.Laminoplasty cage
US6719773 *Jun 19, 2000Apr 13, 2004Kyphon Inc.Expandable structures for deployment in interior body regions
US6723095 *Dec 28, 2001Apr 20, 2004Hemodynamics, Inc.Method of spinal fixation using adhesive media
US6726691 *Apr 5, 2001Apr 27, 2004Kyphon Inc.Methods for treating fractured and/or diseased bone
US6726991 *Sep 9, 2002Apr 27, 2004Eastman Kodak CompanyPorous polymer particles and method for preparation thereof
US6736537 *Aug 27, 2002May 18, 2004Stryker InstrumentsBone cement mixing and delivery device for injection and method thereof
US6740093 *Feb 27, 2001May 25, 2004Stephen HochschulerMethod and apparatus for treating a vertebral body
US6753358 *Jun 28, 2002Jun 22, 2004William Marsh Rice UniversityPhotocrosslinking of diethyl fumarate/poly(propylene fumarate) biomaterials
US6767936 *Dec 3, 2002Jul 27, 2004Dentsply Detrey GmbhDental compositions comprising bisacrylamides and use thereof
US6872403 *Jan 31, 2001Mar 29, 2005University Of Kentucky Research FoundationPolymethylmethacrylate augmented with carbon nanotubes
US6899713 *Aug 29, 2001May 31, 2005Vertelink CorporationFormable orthopedic fixation system
US6985061 *Jul 2, 2001Jan 10, 2006Vetco Aibel AsArrangement and method for installing a subsea transformer
US7008433 *Feb 15, 2001Mar 7, 2006Depuy Acromed, Inc.Vertebroplasty injection device
US7044954 *Jun 19, 2001May 16, 2006Kyphon Inc.Method for treating a vertebral body
US7081125 *Mar 8, 2004Jul 25, 2006Neomend, Inc.Universal introducer
US7160020 *Apr 24, 2006Jan 9, 2007Kyphon Inc.Methods for mixing and transferring flowable materials
US7241303 *Jun 8, 2004Jul 10, 2007Kyphon Inc.Devices and methods using an expandable body with internal restraint for compressing cancellous bone
US7510579 *Apr 4, 2001Mar 31, 2009Arthrocare CorporationEnhanced visibility materials for implantation in hard tissue
US7559932 *Jun 24, 2005Jul 14, 2009Dfine, Inc.Bone treatment systems and methods
US7662133 *Feb 23, 2004Feb 16, 2010Smith & Nephew, Inc.Spinal fluid introduction
US7678116 *Jun 24, 2005Mar 16, 2010Dfine, Inc.Bone treatment systems and methods
US7708733 *Oct 20, 2004May 4, 2010Arthrocare CorporationElectrosurgical method and apparatus for removing tissue within a bone body
US7717918 *Aug 20, 2005May 18, 2010Dfine, Inc.Bone treatment systems and methods
US7722624 *Feb 23, 2004May 25, 2010Kyphon SĀRLExpandable structures for deployment in interior body regions
US20010011190 *Jan 30, 2001Aug 2, 2001Park Joon B.Precoated polymeric prosthesis and process for making same
US20010012968 *Apr 4, 2001Aug 9, 2001Howard PreissmanEnhanced visibility materials for implantation in hard tissue
US20020026195 *Apr 6, 2001Feb 28, 2002Kyphon Inc.Insertion devices and method of use
US20020058947 *Feb 27, 2001May 16, 2002Stephen HochschulerMethod and apparatus for treating a vertebral body
US20020068974 *Jul 20, 2001Jun 6, 2002Kuslich Stephen D.Expandable porous mesh bag device and methods of use for reduction, filling, fixation and supporting of bone
US20020082608 *Nov 13, 2001Jun 27, 2002Kyphon Inc.Systems and methods using expandable bodies to push apart cortical bone surfaces
US20020099385 *Oct 25, 2001Jul 25, 2002Kyphon Inc.Systems and methods for reducing fractured bone using a fracture reduction cannula
US20030032733 *Jun 28, 2002Feb 13, 2003Wm. Marsh Rice UniversityPhotocrosslinking of diethyl fumarate/poly (propylene fumarate) biomaterials
US20030032929 *Jul 22, 2002Feb 13, 2003Mcguckin James F.Hollow curved superelastic medical needle and method
US20030130373 *Dec 3, 2002Jul 10, 2003Dentsply Detrey GmbhDental compositions comprising bisacrylamides and use thereof
US20030130738 *Nov 8, 2002Jul 10, 2003Arthrocare CorporationSystem and method for repairing a damaged intervertebral disc
US20040006347 *Jan 30, 2003Jan 8, 2004Sproul Michael E.Ultrasonic cannula system
US20040024410 *Aug 2, 2002Feb 5, 2004Scimed Life Systems, Inc.Media delivery device for bone structures
US20040073308 *May 16, 2003Apr 15, 2004Spineology, Inc.Expandable porous mesh bag device and methods of use for reduction, filling, fixation, and supporting of bone
US20040083002 *Oct 22, 2003Apr 29, 2004Belef William MartinMethods for treating spinal discs
US20040092948 *Oct 7, 2002May 13, 2004Kyphon Inc.Inflatable device for use in surgical protocol relating to fixation of bone
US20040102845 *Nov 21, 2002May 27, 2004Reynolds Martin A.Methods of performing embolism-free vertebroplasty and devices therefor
US20040110285 *May 31, 2001Jun 10, 2004Andreas LendleinShape memory thermoplastics and polymer networks for tissue engineering
US20040138748 *Dec 29, 2003Jul 15, 2004Synthes (Usa)Plugs for filling bony defects
US20050010231 *Jun 21, 2004Jan 13, 2005Myers Thomas H.Method and apparatus for strengthening the biomechanical properties of implants
US20050015148 *Jul 18, 2003Jan 20, 2005Jansen Lex P.Biocompatible wires and methods of using same to fill bone void
US20050059979 *Mar 9, 2004Mar 17, 2005Duran YetkinlerUse of vibration with orthopedic cements
US20050113843 *Nov 25, 2003May 26, 2005Arramon Yves P.Remotely actuated system for bone cement delivery
US20060052743 *Aug 18, 2005Mar 9, 2006Reynolds Martin AMethods of performing embolism-free vertebroplasty and devices therefor
US20060052794 *Aug 17, 2004Mar 9, 2006Scimed Life Systems, Inc.Apparatus and methods for delivering compounds into vertebrae for vertebroplasty
US20060074433 *Sep 30, 2004Apr 6, 2006Scimed Life Systems, Inc.Apparatus and methods for delivering compounds into vertebrae for vertebroplasty
US20060079905 *Aug 1, 2005Apr 13, 2006Disc-O-Tech Medical Technologies Ltd.Methods, materials and apparatus for treating bone and other tissue
US20060100635 *Aug 9, 2005May 11, 2006Kyphon, Inc.Inflatable device for use in surgical protocol relating to fixation of bone
US20060122614 *Aug 2, 2005Jun 8, 2006Csaba TruckaiBone treatment systems and methods
US20060122621 *Aug 20, 2005Jun 8, 2006Csaba TruckaiBone treatment systems and methods
US20060122622 *Jun 24, 2005Jun 8, 2006Csaba TruckaiBone treatment systems and methods
US20060122623 *Jun 24, 2005Jun 8, 2006Csaba TruckaiBone treatment systems and methods
US20060122624 *Aug 2, 2005Jun 8, 2006Csaba TruckaiBone treatment systems and methods
US20060122625 *Aug 22, 2005Jun 8, 2006Csaba TruckaiBone treatment systems and methods
US20060150862 *Jul 10, 2003Jul 13, 2006Qi ZhaoCoatings
US20070022912 *Sep 11, 2006Feb 1, 2007Kyphon Inc.Magnesium Ammonium Phosphate Cement Composition
US20070027230 *Feb 22, 2006Feb 1, 2007Disc-O-Tech Medical Technologies Ltd.Methods, materials, and apparatus for treating bone and other tissue
US20070112299 *May 26, 2006May 17, 2007Stryker CorporationHand-held fluid delivery device with sensors to determine fluid pressure and volume of fluid delivered to intervertebral discs during discography
US20070118144 *Sep 1, 2006May 24, 2007Csaba TruckaiSystems for sensing retrograde flows of bone fill material
US20070162043 *Sep 1, 2006Jul 12, 2007Csaba TruckaiMethods for sensing retrograde flows of bone fill material
US20080103506 *Sep 27, 2007May 1, 2008Depuy Mitek, Inc.Methods and devices for ligament repair
US20090024161 *Aug 29, 2008Jan 22, 2009Bonutti Peter MMethods and devices for utilizing thermal energy to bond, stake and/or remove implants
Referenced by
Citing PatentFiling datePublication dateApplicantTitle
US7569626Mar 2, 2004Aug 4, 2009Dfine, Inc.Polymer composites for biomedical applications and methods of making
US7666226Aug 15, 2006Feb 23, 2010Benvenue Medical, Inc.Spinal tissue distraction devices
US7666227Aug 15, 2006Feb 23, 2010Benvenue Medical, Inc.Devices for limiting the movement of material introduced between layers of spinal tissue
US7670374Aug 15, 2006Mar 2, 2010Benvenue Medical, Inc.Methods of distracting tissue layers of the human spine
US7670375Aug 15, 2006Mar 2, 2010Benvenue Medical, Inc.Methods for limiting the movement of material introduced between layers of spinal tissue
US7678116Jun 24, 2005Mar 16, 2010Dfine, Inc.Bone treatment systems and methods
US7717918Aug 20, 2005May 18, 2010Dfine, Inc.Bone treatment systems and methods
US7722620Aug 22, 2005May 25, 2010Dfine, Inc.Bone treatment systems and methods
US7785368Aug 15, 2006Aug 31, 2010Benvenue Medical, Inc.Spinal tissue distraction devices
US7909873Dec 14, 2007Mar 22, 2011Soteira, Inc.Delivery apparatus and methods for vertebrostenting
US7955391Feb 15, 2010Jun 7, 2011Benvenue Medical, Inc.Methods for limiting the movement of material introduced between layers of spinal tissue
US7963993Feb 15, 2010Jun 21, 2011Benvenue Medical, Inc.Methods of distracting tissue layers of the human spine
US7967864Feb 15, 2010Jun 28, 2011Benvenue Medical, Inc.Spinal tissue distraction devices
US7967865Feb 15, 2010Jun 28, 2011Benvenue Medical, Inc.Devices for limiting the movement of material introduced between layers of spinal tissue
US8057544Aug 15, 2006Nov 15, 2011Benvenue Medical, Inc.Methods of distracting tissue layers of the human spine
US8070753Aug 2, 2005Dec 6, 2011Dfine, Inc.Bone treatment systems and methods
US8080061Jun 19, 2006Dec 20, 2011Synthes Usa, LlcApparatus and methods for treating bone
US8157806Oct 10, 2006Apr 17, 2012Synthes Usa, LlcApparatus and methods for vertebral augmentation
US8192442Jul 13, 2009Jun 5, 2012Dfine, Inc.Bone treatment systems and methods
US8267971Feb 11, 2010Sep 18, 2012Synthes Usa, LlcApparatus and methods for vertebral augmentation using linked expandable bodies
US8268010 *Jan 12, 2007Sep 18, 2012Warsaw Orthopedic, Inc.System and method for forming bone filling materials with microparticles
US8348955May 24, 2010Jan 8, 2013Dfine, Inc.Bone treatment systems and methods
US8366773Jan 25, 2008Feb 5, 2013Benvenue Medical, Inc.Apparatus and method for treating bone
US8430887Apr 30, 2008Apr 30, 2013Dfine, Inc.Bone treatment systems and methods
US8454617Feb 21, 2008Jun 4, 2013Benvenue Medical, Inc.Devices for treating the spine
US8487021Feb 27, 2009Jul 16, 2013Dfine, Inc.Bone treatment systems and methods
US8535327Mar 16, 2010Sep 17, 2013Benvenue Medical, Inc.Delivery apparatus for use with implantable medical devices
US8556978Nov 15, 2011Oct 15, 2013Benvenue Medical, Inc.Devices and methods for treating the vertebral body
US8591583Feb 21, 2008Nov 26, 2013Benvenue Medical, Inc.Devices for treating the spine
US8623025Jan 15, 2010Jan 7, 2014Gmedelaware 2 LlcDelivery apparatus and methods for vertebrostenting
US8663294Aug 13, 2012Mar 4, 2014DePuy Synthes Products, LLCApparatus and methods for vertebral augmentation using linked expandable bodies
US8696679Dec 10, 2007Apr 15, 2014Dfine, Inc.Bone treatment systems and methods
US8764761Apr 8, 2013Jul 1, 2014Dfine, Inc.Bone treatment systems and methods
US8777618 *Sep 17, 2007Jul 15, 2014Synergy Biosurgical AgMedical implant II
US8795369Jul 18, 2011Aug 5, 2014Nuvasive, Inc.Fracture reduction device and methods
US8801787Jun 16, 2011Aug 12, 2014Benvenue Medical, Inc.Methods of distracting tissue layers of the human spine
US8808376Mar 25, 2009Aug 19, 2014Benvenue Medical, Inc.Intravertebral implants
US8814873Jun 22, 2012Aug 26, 2014Benvenue Medical, Inc.Devices and methods for treating bone tissue
US8828080Feb 21, 2006Sep 9, 2014Barry M. FellMethod and system for knee joint repair
US8840618Jan 12, 2007Sep 23, 2014Warsaw Orthopedic, Inc.System and method for pressure mixing bone filling material
US8882836Dec 18, 2012Nov 11, 2014Benvenue Medical, Inc.Apparatus and method for treating bone
US8926623Jan 12, 2007Jan 6, 2015Warsaw Orthopedic, Inc.System and method for forming porous bone filling material
US8961609Sep 26, 2013Feb 24, 2015Benvenue Medical, Inc.Devices for distracting tissue layers of the human spine
US8968408Apr 24, 2013Mar 3, 2015Benvenue Medical, Inc.Devices for treating the spine
US8979929Jun 16, 2011Mar 17, 2015Benvenue Medical, Inc.Spinal tissue distraction devices
US9000066 *Apr 18, 2008Apr 7, 2015Smith & Nephew, Inc.Multi-modal shape memory polymers
US9005210Jan 4, 2013Apr 14, 2015Dfine, Inc.Bone treatment systems and methods
US9044338Mar 12, 2013Jun 2, 2015Benvenue Medical, Inc.Spinal tissue distraction devices
US9066808Feb 20, 2009Jun 30, 2015Benvenue Medical, Inc.Method of interdigitating flowable material with bone tissue
US9144501Jul 18, 2011Sep 29, 2015Nuvasive, Inc.Fracture reduction device and methods
US9161797Jun 13, 2014Oct 20, 2015Dfine, Inc.Bone treatment systems and methods
US9192397Jun 17, 2009Nov 24, 2015Gmedelaware 2 LlcDevices and methods for fracture reduction
US9216195Jun 19, 2013Dec 22, 2015Dfine, Inc.Bone treatment systems and methods
US9220553Sep 2, 2014Dec 29, 2015Warsaw Orthopedic, Inc.System and method for pressure mixing bone filling material
US9237916Dec 14, 2007Jan 19, 2016Gmedeleware 2 LlcDevices and methods for vertebrostenting
US9259216Dec 28, 2011Feb 16, 2016DePuy Synthes Products, Inc.Elongated fixation element
US9259326Nov 21, 2014Feb 16, 2016Benvenue Medical, Inc.Spinal tissue distraction devices
US9283016Dec 23, 2014Mar 15, 2016Warsaw Orthopedic, Inc.System and method for forming porous bone filling material
US9289240Jul 26, 2012Mar 22, 2016DePuy Synthes Products, Inc.Flexible elongated chain implant and method of supporting body tissue with same
US9301792Jan 26, 2007Apr 5, 2016Stryker CorporationLow pressure delivery system and method for delivering a solid and liquid mixture into a target site for medical treatment
US9308293 *Feb 5, 2015Apr 12, 2016Smith & Nephew, Inc.Multi-modal shape memory polymers
US9314252Aug 15, 2014Apr 19, 2016Benvenue Medical, Inc.Devices and methods for treating bone tissue
US9326866Nov 8, 2013May 3, 2016Benvenue Medical, Inc.Devices for treating the spine
US9398927Jul 3, 2007Jul 26, 2016Synergy Biosurgical AgMedical implant
US9402725Nov 14, 2013Aug 2, 2016DePuy Synthes Products, Inc.Expandable implant
US9445854Feb 27, 2009Sep 20, 2016Dfine, Inc.Bone treatment systems and methods
US9457125 *Jun 2, 2014Oct 4, 2016Synergy Biosurgical AgMedical implant with electromagnetic radiation responsive polymer and related methods
US9480485Mar 23, 2010Nov 1, 2016Globus Medical, Inc.Devices and methods for vertebrostenting
US9498205Jan 7, 2016Nov 22, 2016DePuy Synthes Products, Inc.Methods for employing elongated fixation elements
US9572613Oct 19, 2015Feb 21, 2017Dfine, Inc.Bone treatment systems and methods
US9592317Jul 31, 2013Mar 14, 2017Dfine, Inc.Medical system and method of use
US9597118Jan 6, 2010Mar 21, 2017Dfine, Inc.Bone anchor apparatus and method
US9610110Apr 10, 2015Apr 4, 2017Dfine, Inc.Bone treatment systems and methods
US9642712Feb 4, 2015May 9, 2017Benvenue Medical, Inc.Methods for treating the spine
US20040247849 *Mar 2, 2004Dec 9, 2004Csaba TruckaiPolymer composites for biomedical applications and methods of making
US20060122622 *Jun 24, 2005Jun 8, 2006Csaba TruckaiBone treatment systems and methods
US20060122623 *Jun 24, 2005Jun 8, 2006Csaba TruckaiBone treatment systems and methods
US20060122624 *Aug 2, 2005Jun 8, 2006Csaba TruckaiBone treatment systems and methods
US20060122625 *Aug 22, 2005Jun 8, 2006Csaba TruckaiBone treatment systems and methods
US20060190078 *Feb 21, 2006Aug 24, 2006Fell Barry MMethod and system for joint repair
US20070055274 *Jun 19, 2006Mar 8, 2007Andreas AppenzellerApparatus and methods for treating bone
US20070093822 *Sep 18, 2006Apr 26, 2007Christof DutoitApparatus and methods for vertebral augmentation using linked expandable bodies
US20070093846 *Oct 10, 2006Apr 26, 2007Robert FriggApparatus and methods for vertebral augmentation
US20070093899 *Sep 25, 2006Apr 26, 2007Christof DutoitApparatus and methods for treating bone
US20070233146 *Jan 26, 2007Oct 4, 2007Stryker CorporationLow pressure delivery system and method for delivering a solid and liquid mixture into a target site for medical treatment
US20080027456 *Jul 19, 2007Jan 31, 2008Csaba TruckaiBone treatment systems and methods
US20080154273 *Dec 10, 2007Jun 26, 2008Shadduck John HBone treatment systems and methods
US20080172058 *Jan 12, 2007Jul 17, 2008Warsaw Orthopedic, Inc.System and Method for Pressure Mixing Bone Filling Material
US20080172059 *Jan 12, 2007Jul 17, 2008Warsaw Orthopedic, Inc.System and Method for Forming Porous Bone Filling Material
US20080172131 *Jan 12, 2007Jul 17, 2008Warsaw Orthopedic, Inc.System and Method for Forming Bone Filling Materials With Microparticles
US20080188858 *Feb 1, 2008Aug 7, 2008Robert LuzziBone treatment systems and methods
US20080269761 *Apr 30, 2008Oct 30, 2008Dfine. Inc.Bone treatment systems and methods
US20090247664 *Feb 27, 2009Oct 1, 2009Dfine, Inc.Bone treatment systems and methods
US20090275995 *Jul 13, 2009Nov 5, 2009Dfine, Inc.Bone treatment systems and methods
US20100016467 *Feb 27, 2009Jan 21, 2010Dfine, Inc.Bone treatment systems and methods
US20100030220 *Jul 30, 2009Feb 4, 2010Dfine, Inc.Bone treatment systems and methods
US20100069547 *Apr 15, 2008Mar 18, 2010Smith & Nephew, Inc.Shape Memory Polymers Containing Degradation Accelerant
US20100070049 *May 6, 2009Mar 18, 2010O'donnell PatrickMethod and apparatus for treating compression fractures in vertebral bodies
US20100136648 *Apr 16, 2008Jun 3, 2010Smith & Nephew, PlcExpansion Moulding of Shape Memory Polymers
US20100145392 *Feb 11, 2010Jun 10, 2010Christof DutoitApparatus and methods for vertebral augmentation using linked expandable bodies
US20100145448 *Apr 16, 2008Jun 10, 2010Smith & Nephew, Inc.Graft Fixation
US20100198225 *Apr 15, 2008Aug 5, 2010Thompson Andrew NmiShape memory spine jack
US20100241229 *Jul 3, 2007Sep 23, 2010Synergy Biosurgical AgMedical implant
US20100280520 *May 24, 2010Nov 4, 2010Dfine, Inc.Bone treatment systems and methods
US20110144751 *Apr 18, 2008Jun 16, 2011Smith & Nephew, IncMulti-Modal Shape Memory Polymers
US20120129131 *Sep 17, 2007May 24, 2012Synergy Biosurgical AgMedical implant ii
US20130079878 *Apr 18, 2012Mar 28, 2013Patrick O'DonnellMethod and apparatus for treating compression fractures in vertebral bodies
US20140277568 *Jun 2, 2014Sep 18, 2014Synergy Biosurgical AgMedical Implant II
US20150151023 *Feb 5, 2015Jun 4, 2015Smith & Nephew, Inc.Multi-modal shape memory polymers
CN103327909A *Dec 28, 2011Sep 25, 2013新特斯有限责任公司Elongated fixation element
EP2306913A2 *Mar 27, 2009Apr 13, 2011Osteotech, Inc.,Bone anchors for orthopedic applications
EP2306913A4 *Mar 27, 2009Jun 4, 2014Warsaw Orthopedic IncBone anchors for orthopedic applications
EP2712634A1 *Sep 17, 2007Apr 2, 2014Synergy Biosurgical AGMedical Implant
EP2712634B1Sep 17, 2007Jun 8, 2016Synergy Biosurgical AGMedical Implant
WO2008057860A2 *Oct 31, 2007May 15, 2008Warsaw Orthopedic, IncMethods of employing calcium phosphate cement compositions and osteoinductive proteins to effect vertebrae interbody fusion absent an interbody device
WO2008057860A3 *Oct 31, 2007Aug 7, 2008Steven M PeckhamMethods of employing calcium phosphate cement compositions and osteoinductive proteins to effect vertebrae interbody fusion absent an interbody device
WO2008129241A1Apr 15, 2008Oct 30, 2008Smith & Nephew PlcFixation device
WO2008130989A2 *Apr 16, 2008Oct 30, 2008Smith & Nephew, Inc.Prosthetic implants
WO2008130989A3 *Apr 16, 2008Feb 4, 2010Smith & Nephew, Inc.Prosthetic implants
WO2009036576A1 *Sep 17, 2007Mar 26, 2009Synergy Biosurgical AgMedical implant
WO2012096786A1 *Dec 28, 2011Jul 19, 2012Synthes Usa, LlcElongated fixation element
Legal Events
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Jul 20, 2006ASAssignment
Owner name: DFINE, INC., CALIFORNIA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:TRUCKAI, CSABA;SHADDUCK, JOHN;REEL/FRAME:017969/0063
Effective date: 20060713