WO2004089240A2 - Artificial disc prosthesis - Google Patents
Artificial disc prosthesis Download PDFInfo
- Publication number
- WO2004089240A2 WO2004089240A2 PCT/US2004/010000 US2004010000W WO2004089240A2 WO 2004089240 A2 WO2004089240 A2 WO 2004089240A2 US 2004010000 W US2004010000 W US 2004010000W WO 2004089240 A2 WO2004089240 A2 WO 2004089240A2
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- WO
- WIPO (PCT)
- Prior art keywords
- endplate
- intervertebral disc
- artificial intervertebral
- disc prosthesis
- motion
- Prior art date
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/44—Joints for the spine, e.g. vertebrae, spinal discs
- A61F2/442—Intervertebral or spinal discs, e.g. resilient
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
- A61F2002/30316—The prosthesis having different structural features at different locations within the same prosthesis; Connections between prosthetic parts; Special structural features of bone or joint prostheses not otherwise provided for
- A61F2002/30329—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
- A61F2002/30331—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements made by longitudinally pushing a protrusion into a complementarily-shaped recess, e.g. held by friction fit
- A61F2002/30362—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements made by longitudinally pushing a protrusion into a complementarily-shaped recess, e.g. held by friction fit with possibility of relative movement between the protrusion and the recess
- A61F2002/3037—Translation along the common longitudinal axis, e.g. piston
- A61F2002/30372—Translation along the common longitudinal axis, e.g. piston with additional means for limiting said translation
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- A—HUMAN NECESSITIES
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
- A61F2002/30316—The prosthesis having different structural features at different locations within the same prosthesis; Connections between prosthetic parts; Special structural features of bone or joint prostheses not otherwise provided for
- A61F2002/30329—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
- A61F2002/30383—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements made by laterally inserting a protrusion, e.g. a rib into a complementarily-shaped groove
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
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- A61F2002/30329—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
- A61F2002/30462—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements retained or tied with a rope, string, thread, wire or cable
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
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- A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
- A61F2002/30316—The prosthesis having different structural features at different locations within the same prosthesis; Connections between prosthetic parts; Special structural features of bone or joint prostheses not otherwise provided for
- A61F2002/30535—Special structural features of bone or joint prostheses not otherwise provided for
- A61F2002/30563—Special structural features of bone or joint prostheses not otherwise provided for having elastic means or damping means, different from springs, e.g. including an elastomeric core or shock absorbers
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
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- A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
- A61F2002/30316—The prosthesis having different structural features at different locations within the same prosthesis; Connections between prosthetic parts; Special structural features of bone or joint prostheses not otherwise provided for
- A61F2002/30535—Special structural features of bone or joint prostheses not otherwise provided for
- A61F2002/30604—Special structural features of bone or joint prostheses not otherwise provided for modular
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
- A61F2/30771—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth applied in original prostheses, e.g. holes or grooves
- A61F2002/30878—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth applied in original prostheses, e.g. holes or grooves with non-sharp protrusions, for instance contacting the bone for anchoring, e.g. keels, pegs, pins, posts, shanks, stems, struts
- A61F2002/30884—Fins or wings, e.g. longitudinal wings for preventing rotation within the bone cavity
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
- A61F2/30771—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth applied in original prostheses, e.g. holes or grooves
- A61F2002/30878—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth applied in original prostheses, e.g. holes or grooves with non-sharp protrusions, for instance contacting the bone for anchoring, e.g. keels, pegs, pins, posts, shanks, stems, struts
- A61F2002/30891—Plurality of protrusions
- A61F2002/30892—Plurality of protrusions parallel
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
- A61F2/30771—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth applied in original prostheses, e.g. holes or grooves
- A61F2002/30904—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth applied in original prostheses, e.g. holes or grooves serrated profile, i.e. saw-toothed
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
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- A61F2002/3097—Designing or manufacturing processes using laser
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/46—Special tools or methods for implanting or extracting artificial joints, accessories, bone grafts or substitutes, or particular adaptations therefor
- A61F2/4657—Measuring instruments used for implanting artificial joints
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- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
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- A61F2220/0025—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
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- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0025—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
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- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
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- A61F2310/00029—Cobalt-based alloys, e.g. Co-Cr alloys or Vitallium
Definitions
- This invention relates to an artificial visco-elastic, constrained motion disc for replacing mtervertebral discs in the lower back, particularly in the lumbar and lumbar-sacral regions.
- the human spine is composed of many vertebral bones stacked one upon the other, with an mtervertebral disc between each pair of adjacent vertebral bones.
- the discs act as cartilaginous cushions and shock absorbers.
- the spinal cord runs in a bony canal formed by successive openings in these bones.
- the spinal nerves exit the spinal cord between pairs of vertebrae and supply nerves and nerve signals to and from other body structures.
- the mtervertebral disc is a complex joint both anatomically and functionally. It is composed of three component structures: the nucleus pulposus; the annulus fibrosus, and the vertebral endplates. The biomedical composition and anatomical anangements within these component structures are related to the biomechanical function of the disc. [0004]
- the nucleus pulposus occupying about 25% to 40% of the total disc cross- sectional area, usually contains approximately 70% to 90% water by weight. Because of this high water content, the nucleus may be mechanically described as an incompressible hydrostatic material.
- the annulus fibrosus is a concentrically laminated structure which contains highly aligned collagen fibers and fibrocartilage embedded in an amorphous ground substance.
- the annular layers are oriented at approximately +/- 60° to the longitudinal axis of the spine.
- the annulus fibrosus usually contains approximately 8 to 12 layers, and is mechanically the main stabilizing structure which resists torsional and bending forces applied to the disc.
- the two vertebral endplates separate the disc from the adjacent vertebral bodies, and are composed of hyaline cartilage.
- Spinal discs may be damaged or displaced due to trauma or disease. In either case, the nucleus pulposus may herniate and protrude into the vertebral canal or mtervertebral foramen. This condition is known as a herniated or "slipped" disc. The disc may in turn press upon the spinal nerve that exits the vertebral canal through the partially obstructed foramen, causing pain or paralysis in the area of its distribution. The most frequent site of occunence of a herniated disc is in the lower lumbar region. To alleviate this condition, two procedures are common.
- a second method for alleviating disc problems is insertion of an mtervertebral disc replacement.
- the object of an mtervertebral disc replacement is to provide a prosthetic disc that combines both stability to support the high loads of the patient's vertebrae and flexibility to provide the patient with sufficient mobility and proper spinal column load distribution.
- basically four types of artificial mtervertebral discs have been developed: elastomer discs, ball and socket discs, mechanical spring discs, and hybrid discs.
- Elastomer discs typically include an elastomer cushion which is sandwiched between upper and lower rigid endplates. Elastomer discs can provide cushion or damping functions similar in mechanical behavior to the removed mtervertebral disc tissue.
- known elastomer discs experience long-term in-vivo problems stemming from micro-cracking, fixation problems with respect to the endplates, insufficient compression and torsional resistance, and excessive motion which can lead to bulging of the replacement disc and resultant pain for the patient.
- One hypothesis for the failures of previous elastomer based disc designs is the unlimited potential for strain. High load in vivo events cause subsequent changes in structural characteristics of the elastomer, a characteristic called the Mullins effect.
- Ball and socket discs typically incorporate two plate members having cooperating inner ball and socket portions allowing an articulating motion of the members during movement of the spine. These types of discs generally restore spinal motion, but inadequately replicate the natural stiffness of the mtervertebral disc. Furthermore, dislocation and wear problems exist with these devices as well as unsatisfactory motion limiting components. Some types also comprise polymers in conjunction with metallic components.
- a Link Charite disc includes polyethylene/cobalt chrome molybdenum (CCM) construction.
- CCM polyethylene/cobalt chrome molybdenum
- This design restores motion, but in a very unphysiologic manner.
- the design is essentially a ball and socket joint which does not provide the nonlinear elastic response of the normal disc including hysteresis and therefore shock absorption. As in hip replacements this design is subject to wear and polyethylene debris complications.
- This disc which has been extensively implanted in Europe and the United States, relies on a relatively incompressible ultra high molecular weight polyethylene center mating with concave surfaces in cobalt chrome upper and lower endplates.
- the mating surfaces provide a low friction pseudo ball-socket joint with motion constraints in compression and anterior-posterior as well as lateral translation.
- the device is totally unconstrained in rotation about its axis, and in tension. Though this device has a semi successful in vivo history, it lacks fundamental stress strain characteristics of the normal disc. Instead, it provides low friction, high movement, non-energy absorbing kinematic function restoration to the spine motion segment.
- the disc is designed to move freely until limits of travel are reached. The stopping action provided is very abrupt and thus loads the vertebral endplate in a shock-like manner at end-of-travel. This disc imitates a free moving ball and socket joint, not a natural disc that behaves very elastically until amiulus fibers play the role of a "limiter".
- a natural disc is load sharing between the elastic elements and fibrous tissue limiters.
- Mechanical spring discs which generally have only two or three degrees of freedom, typically incorporate one or more coiled springs disposed between metal endplates. These discs generally allow movement of the vertebrae during flexion and extension. However, these types have significant wear problems, as well as problems dealing with in- vivo torsional loads, and overall these discs cannot replicate the six-degree of freedom movement of a natural mtervertebral disc.
- Hybrid types of discs generally incorporate two or more principals of any of the aforementioned disc types.
- one common hybrid disc anangement includes a ball and socket set sunounded by a non-adhered elastomer ring.
- This hybrid disc is more complex than would be prefened for common usage, and more importantly, the intermittent contact between the ball socket and the elastomer ring that occasionally occurs in- vivo causes critical wear problems.
- an artificial disc constructed with a polymer between two metal endplates undergoes compression as a result of both gravity and patient activities requiring exertion of energy. Therefore, ideally a disc would include a means of protecting the polymer and the possible bond joint between polymer and metal. Mechanical stops and motion-limiters can be added to maintain the integrity of the prosthesis. Such structures can take the form of rods, tension cables, or other connectors, as well as metal-to-metal contact in compression, to name but a few examples. Moreover, it would be beneficial for a disc also to include a means to convey to surgeons and to patients the actual state of the loads experienced by the device.
- the artificial disc should maintain the vertebrae spaced from each other and prevent pinching of nerves or spinal cord.
- the artificial disc should provide good load distribution.
- the artificial disc should be sufficiently resilient to accommodate other motions of the spine, including flexion, extension, lateral bending, and rotation, as well as combinations of these motions. In humans, the bony facet joints actually limit the rotational movement.
- a disc typically need only rotate approximately three degrees.
- the disc should provide restorative force to bias toward the resting position.
- the artificial disc should be both biocompatible and biostable such that the disc itself or any of its degradation byproducts, if any, do not cause adverse tissue reactions.
- the disc can also provide stored or real-time data to the surgeon and the patient regarding the state of the loads and displacements experienced by the disc.
- the present invention is directed to a prosthetic mtervertebral disc replacement that restores and preserves the physiologic function of a normal spinal motion segment.
- the mtervertebral disc replacement addresses the detrimental phenomenon of cascading spine syndrome observed in long-term patients with fused-spinal segments.
- the present mtervertebral disc replacement is designed to avoid the need for spinal fusion or at least prolong the need for it.
- the invention incorporates elements to bear high load in the design, while preserving the ability of the elastomer to provide substantial motion at low to moderate loads.
- the invention demonstrates the potential to survive high cycle fatigue in bending, compression, and shear along all three mutually orthogonal axes. The motion- limiting features survive high load, low cycle fatigue and preserve the integrity of the elastic range performance of the device.
- the present invention is a visco-elastic constrained-motion disc prosthesis generally comprising specially designed rigid upper and lower endplates having therewithin channels or openings for receiving one or more motion-limiting members fitted on each end with an enlarged portion.
- the lower surface of the upper endplate contains a first projection therefrom that extends toward the lower endplate.
- the upper surface of the lower endplate can contain a second projection extending toward said upper endplate and substantially aligned with said first projection.
- the first and second projections terminate to create a gap therebetween, forming a compression stop.
- Interposed between the upper and lower endplates is an elastomer cushion.
- the elastomer cushion is not in direct contact with either the motion-limiting members or the first or second projections to avoid wear and debris problems.
- the gap allows a predetermined amount of axial movement, but no more, between the upper endplate and the lower endplate.
- the gap prevents excess compression from occuning, and is usually designed to allow approximately 1 to 2 millimeters of relative movement between the upper and lower endplates. This limits the compressive stresses seen by the elastomer. During most activities of the patient, the elastomer will exclusively cany the load. The compression stop will be engaged typically only during activities of high exertion.
- the motion-limiting members with enlarged portions are inserted into internal cavities in the elastomer and link the upper endplate to the lower endplate.
- the motion- limiting members are dimensioned so as to have a length that is slightly greater than the distance between the lower surface of the upper endplate and the upper surface of the lower endplate (and also preferably slightly less than the overall length of the internal cavities in which they reside). This allows space for the motion-limiting members to move during compression.
- the motion-limiting members are strategically oriented to resist the tension in the posterior region of the disc. If motion-limiting members are present at the anterior portion of the disc, they float freely in the internal cavities during bending.
- the external surfaces of the upper and lower endplates can also be fitted with wedges, spikes, keels, or other appurtenances to aid in attachment to a vertebral body. These appurtenances can also serve as covers to enclose the enlarged portions of the motion-limiting members.
- some embodiments of the invention utilize strain gauges, pressure transducers, piezoelectric force transducers, or other means of force transduction to provide stored or real-time data to the surgeon or patient of the load state of the disc.
- Several commercially available low durometer (i.e., approximately 70-85A) polyurethanes with a history of animal and human implantation are candidates to be used in a titanium or CoCrMo/elastomer construction.
- Hybrid discs according to the invention can overcome one of the failure modes of previous artificial disc designs, namely that of delamination and fatigue failure of the bonded interface between the elastomer and metal.
- a particularly useful embodiment comprises an artificial intervertebral disc prosthesis having an anterior portion and a posterior portion, further comprising: a first endplate having an upper surface and a lower surface, wherein the first endplate further comprises at least one opening for receiving at least one motion-limiting member; a first projection extending from the lower surface of the first endplate terminating in a first distal end; a second endplate having an upper surface and a lower surface, wherein the second endplate further comprises at least one opening for receiving at least one motion-limiting member; a second projection extending from the upper surface of the second endplate and substantially aligned with the first projection, wherein the second projection terminates at a second distal end to form a gap having a predetermined distance between the first and second distal ends; at least one motion-limiting member received respectively in the at least one opening of the first and second endplates, linking the two endplates and allowing only a predetermined amount of movement thereof; and a visco-
- Figure 1 is a graph showing the typical nonlinear response to load of human spine motion segments
- Figure 2 is a diagram showing a reference coordinate system for a functional spinal unit to be used herein;
- Figure 3 is a posterior perspective view of a first embodiment of an artificial disc of the present invention.
- Figure 3(a) is the artificial disc of Figure 3 showing a second type of appurtenance fitted to the upper and lower endplates;
- Figure 3(b) is the artificial disc of Figure 3 showing a third type of appurtenance fitted to the upper and lower endplates;
- Figure 3(c) is the artificial disc of Figure 3 showing a fourth type of appurtenance fitted to the upper and lower endplates;
- Figure 4 is a top plan view of the artificial disc of Figure 3;
- Figure 5 is a bottom plan view of the artificial disc of Figure 3;
- Figure 6 is a posterior elevation view of the artificial disc of Figure 3;
- Figure 7 is a lateral elevation view of the artificial disc of Figure 3;
- Figure 8 is an exploded perspective view of the artificial disc shown in Figure 3;
- Figure 9 is a section view taken along plane A-A in Figure 3;
- Figure 10 is a section view taken along plane B-B in Figure 3;
- Figure 11 is a section view taken along plane C-C in Figure 3;
- Figure 12 is a section view taken along plane D-D in Figure 3;
- Figure 13 is an exploded perspective view of an exemplary motion-limiting member of a first embodiment of the invention.
- Figure 14 is a perspective view of a second embodiment of an artificial disc of the present invention having four motion-limiting members therein;
- Figure 15 is an exploded perspective view of the embodiment of the artificial disc of the present invention shown in Figure 14;
- Figure 16 is a section view taken along plane E-E in Figure 14;
- Figure 17 is a section view taken along plane F-F in Figure 14;
- Figure 18 is a section view taken along plane G-G in Figure 14;
- Figure 19 is a section view taken along plane H-H in Figure 14;
- Figure 20 is a section view taken along plane I-I in Figure 14;
- Figure 21 is a side elevation view of a disc according to a first embodiment of the invention showing the disc in normal bending mode;
- Figure 22 is a top view of an embodiment of a lower endplate flex circuit for an artificial disc using strain gauges to provide force transduction for providing data external to the disc;
- Figure 23 is a side section view of the disc shown in Figure 21 in normal bending mode
- Figure 24 is a perspective view of a motion-limiting member according to an embodiment of the invention incorporating a split ring in place around the enlarged portion of the motion-limiting member;
- Figure 25 is a side elevation schematic of an embodiment of an artificial disc using strain gauges to provide force transduction for providing data to locations external to the disc;
- Figure 26 is a perspective view of the posterior side of an alternative embodiment of the disc showing removable appurtenances;
- Figure 27 is a perspective view of the anterior side of the disc shown in Figure 26;
- Figure 28 is a perspective view of the posterior side of an appurtenance and an upper endplate according to an embodiment of the invention.
- Figure 29 is a perspective view of the anterior side of the endplate shown in
- FIG. 1 is a graph of the response of the nonnal human disc to load.
- the nonlinear response of the motion segment is a function not only of the disc, but of the facet joints and ligaments. Facet joint function and ligamentous structures may be compromised and unable to provide load sharing as in a normal motion segment.
- the nonlinear response of spine motion segment to load shown in Figure 1 is a typical curve shape in compression, shear, torsion, and bending.
- Figure 2 is a perspective view of a reference intervertebral disc coordinate system that will be used throughout this discussion for ease of reference.
- the figure shows typical loads (forces and moments) and typical displacements (translation and rotation) that can occur in each of the three mutually orthogonal directions.
- the load-deflection curve shape of Figure 1 is similar in all three directions for a nonnal disc.
- a disc 10 of the present invention provides a nonlinear response to torsion, shear, and compressive loads.
- the disc 10 comprises a first or upper endplate 20, a second or lower endplate 30, and a visco-elastic cushion 40 interposed between and adhered to the two endplates.
- the upper and lower plates 20, 30 are substantially symmetrical about an anterior-posterior horizontally extending plane (a transverse plane shown in Figure 2), as well as about a sagittal plane ( Figure 2).
- the terms "upper” and “lower” are used herein only for illustration purposes with reference to the orientation of the disc 10 when it is implanted in the human body between two adjacent vertebrae VI and V2 (defined as the cephalad-caudal direction in Figure 2).
- the upper endplate 20 is rigid and is preferably made from a biocompatible material such as stainless steel, titanium, titanium alloys (such as Ti6A14V), composite materials, and the like.
- the most prefened material is cobalt chrome molybdenum (CoCrMo or "CCM") comprising approximately 66% Co, 28% Cr, and 6% Mo by weight.
- the upper endplate 20 has an upper surface 21 and a lower surface 22 and an anterior portion 23 and a posterior portion 24. Upper surface 21 and lower surface 22 are generally parallel.
- the anterior portion 23 is the portion of the upper endplate 20 that is disposed anteriorly in the spine when the disc 10 is implanted.
- the posterior portion 24 is the portion of the upper endplate 20 that is disposed posteriorly in the spine when the disc 10 is implanted.
- the upper endplate 20 has an external surface 29 therearound that preferably defines a generally "D" shape.
- the posterior portion 24 of the external surface 29 has a concavity 28 therein that defines posterior lobes 25, 26 projecting from the posterior portion 24 (see Figures 3, 4, 5, 12, 14, and 15).
- One or more appurtenance 27 may be optionally affixed to the upper surface 21 to facilitate attachment.
- the upper endplate 20 likewise may comprise an upper subplate 200 (see Figure 15) that can be formed monolithic with the upper endplate 20 or as a separate component affixed thereto subsequent to manufacture.
- the structures that comprise the upper subplate 200 may simply be included in the upper endplate 20.
- the subplate 200 further comprises an upper surface 210 and a lower surface 220 and an anterior portion 230 and a posterior portion 240.
- a first projection 270 optionally may depend from the lower surface 220 of the subplate 200 to act as part of a compression stop, as will be described below.
- the upper subplate 200 also has a plurality of openings 271 therethrough for receiving one or more motion-limiting members 80 (described below).
- the upper subplate 200 includes two openings 271, one disposed posteriorly and slightly to the left (in the medial- lateral plane) of the first projection 270 and another disposed posteriorly and slightly to the right (in the medial-lateral plane) of the first projection 270 (assuming the center of rotation is at the geometric center of the disc).
- the openings 271 further comprise a bearing surface 272 for interacting with the motion-limiting members 80 or a split ring assembly 400 (described below).
- the bearing surface 272 is preferably a tapered opening having a larger diameter at the upper surface 210 than at the lower surface 220.
- the taper can be linear or nonlinear, including conic sections, parabolic sections, spherical sections, and so forth, to name only a few examples.
- the first projection 270 preferably extends from said lower surface 220 a height of approximately 1 mm to approximately 3 mm. Many shapes are possible for the first projection 270, and indeed multiple projections, or no projections, are contemplated as well.
- the first projection 270 takes the form of a substantially cylindrical section having a slight radius on its terminal end of approximately 2 mm to approximately 15 mm, preferably approximately 8 mm to approximately 12 mm.
- the disc 10 further comprises a lower endplate 30.
- the lower endplate 30 is rigid and is preferably made from a biocompatible material such as stainless steel, titanium, titanium alloys (such as Ti6A14V), composite materials, and the like.
- the prefened material is cobalt chrome molybdenum (CCM) comprising approximately 66% Co, 28%o Cr, and 6% Mo by weight, respectively.
- CCM cobalt chrome molybdenum
- the lower endplate 30 has an upper surface 31 and a lower surface 32 and an anterior portion 33 and a posterior portion 34. Upper surface 31 and lower surface 32 are generally parallel.
- the anterior portion 33 is the portion of the lower endplate 30 that is disposed anteriorly in the spine when the disc 10 is implanted.
- the posterior portion 34 is the portion of the lower endplate 30 that is disposed posteriorly in the spine when the disc 10 is implanted.
- the lower endplate 30 has an external surface 39 therearound that preferably defines a generally "D" shape.
- the posterior portion 34 of the external surface 39 has a concavity 38 therein that defines posterior lobes 35, 36 projecting from the posterior portion 34 (see Figures 3, 4, 5, 12, 14, and 15).
- One or more appurtenance 37 may be optionally affixed to the lower surface 32 to facilitate attachment.
- the lower endplate 30 may comprise a lower subplate 300 (see Figures 8 and 15) that can be formed monolithic with the lower endplate 30 or as a separate component affixed thereto subsequent to manufacture.
- the subplate 300 further comprises an upper surface 310 and a lower surface 320 and an anterior portion 330 and a posterior portion 340.
- a second projection 370 depends from the upper surface 310 of the subplate 300 to act as part of a compression stop, as will be described below.
- the lower subplate 300 also has a plurality of openings 371 therethrough, having bearing surfaces 372, for receiving one or more motion-limiting members 80 (described below).
- the lower subplate 300 includes two openings 371, one disposed posteriorly and slightly to the left of the first projection 370 and another disposed posteriorly and slightly to the right of the first projection 370.
- the second projection 370 preferably extends from said upper surface 310 a height of approximately 3 mm to approximately 6 mm.
- the second projection 370 is in substantial alignment with the first projection 270.
- the second projection 370 preferably will have its longitudinal axis aligned with or close to the longitudinal axis of the first projection 270.
- the two projections 270, 370 may be offset from one another, it being more important that at least a portion of the projections 270, 370 overlap during contact therebetween. And, depending on the respective shapes of the projections 270, 370, the amount of offset may vary. Many shapes are possible for the second projection 370, including, but not limited to, all regular polygonal shapes.
- the projections 270, 370 may take the form of partial polygons (for example, a half cylinder or a partial elliptical cylinder, to name but a few), hi the prefened embodiment, the second projection 370 takes the form of a cylindrical platform having a diameter of approximately 6 mm to 10 mm, and more particularly, approximately 7 mm to approximately 9 mm.
- a motion-limiting member 80 typically resides within each opening 271, 371.
- Each motion-limiting member 80 has a length 81 and a diameter 82, and a first end 83 and a second end 84. At each end 83, 84 is an enlarged portion 90.
- the motion-limiting members 80 link the upper endplate 20 to the lower endplate 30 and assist in handling the loads associated with flexion, as will be described below.
- the motion-limiting members 80 can be any of several longitudinal rod-like members, both rigid and semi-rigid, including solid metallic bars or rods of varying cross- sections, and wire. If wire is used as the motion-limiting member 80, the motion-limiting members 80 typically have diameters of approximately 0.038 inches to approximately 0.080 inches. However, the number of motion-limiting members 80 used plays a role in determining the diameter of each motion-limiting member 80. In the prefened embodiment, there are two motion-limiting members 80 that are braided metal wires, preferably a braided stainless steel wire having a diameter of approximately 0.062 inches and a rated tensile strength of approximately 320 pounds.
- the motion-limiting members 80 can be of any material described above, but are preferably cables of 316L stainless, MP35N, Haynes 25. In alternative, though less prefened, embodiments where substantially more numerous motion-limiting members 80 are used (for example ten to twenty), the diameters can be significantly smaller.
- the enlarged portion 90 at each end 83, 84 is typically a spherically-shaped structure, or ball 91, that is affixed to the motion-limiting member 80.
- Balls 91 are preferably of the same material as the motion-limiting members 80.
- the ball 91 has an upper surface 92 and a lower surface 93.
- ball 91 is preformed onto the motion- limiting member 80.
- methods of fixation are also varied and include welding, both during formation of the ball 91 at the first end 83 and during assembly of the ball 91 at the second end 84; as well as crimping on a ball 91.
- the balls 91 are preferably hemispheres wherein the lower surface 93 engages the bearing surface 272 of the plates 20, 30 and/or the subplate 200, 300.
- the upper surface 92 of the ball 91 provides little to no advantage and merely takes up space.
- the upper surface 92 is preferably flat or very low-profile so as to take up a minimal amount of space.
- the appurtenances 27, 37 on the upper and lower endplates 20, 30, respectively, may be used to cover a portion of the enlarged portions 91.
- the inside surface 400d of the split ring assembly (described below) can be used to effectively shorten the length of the motion- limiting member 80 such that no part of the enlarged portion 91 extends beyond the upper surface 21 of the upper endplate or the lower surface 32 of the lower endplate 30.
- a split ring assembly 400 as shown in Figures 8, 13, 15, and 24, fits into the openings 271 of the upper subplate 200 and into openings 371 of the lower subplate 300.
- the split ring assembly 400 comprises a first half 400a and a second half 400b.
- the split ring assembly 400 includes an inside surface 400d that serves as a bearing surface against which the balls 91 can articulate, resulting in a mini-ball and socket joint.
- the diameter of port 400c is smaller than that of the ball 91.
- the first half 400a of the split ring assembly 400 is then inserted into the opening 271 underneath the ball 91 at the first end 83 of the motion-limiting member 80. Then, the second half 400b of the split ring assembly 400 is inserted into the opening 271 of the upper subplate 200 underneath the ball 91 at the first end 83 of the motion-limiting member 80, completing the split ring assembly 400 in the upper subplate 200. Since the diameter of the port 400c in the split ring assembly is smaller than that of the ball 91 at the first end 83 of the motion-limiting member 80, the motion-limiting member 80 is prevented from slipping through the opening 271 of the upper subplate 270.
- a split ring assembly 400 is inserted into the opening 371 of the lower subplate 300 above the ball 91 at the second end 84 of the motion-limiting member 80 in order to prevent the motion-limiting member 80 from slipping through the opening 370 of the lower subplate 300.
- the split ring assemblies 400 may be welded or permanently affixed by some other means known in the art to the upper and lower subplate assemblies 200, 300.
- the split ring assembly 400 includes an inside surface 400d that serves as a bearing surface against which the balls 91 can articulate, resulting in a mini-ball and socket joint, thus minimizing the bending of the motion-limiting member 80 and extending fatigue life.
- the split ring assembly 400 is not present, and the balls 91 are not preformed onto the motion-limiting members 80. Instead the balls 91 are fixed onto the motion-limiting members 80 through some other means such as welding or crimping, as discussed above. However, welding the ends of the motion-limiting members 80 into balls 91 can lower the strength of the motion-limiting members 80 by 10 to 15 percent.
- the diameter of ball 91 can be controlled during welding, ranging in size from approximately slightly larger than the diameter of the motion-limiting member 80 up to a maximum diameter of approximately two times the motion-limiting member diameter. In embodiments using other attachment methods, other diameters are possible.
- each union of ball 91 and bearing surface 272 results in a mini-ball and socket joint that allows articulation of the ball 91 and motion-limiting member 80 within the opening 271, thus limiting bending of the motion- limiting member 80, thereby extending fatigue life.
- the disc 10 of the prefened embodiment provides motion-limiting features in compression and bending, thereby behaving in vivo in a fashion more similar to a natural spinal disc.
- the first projection 270 and the second projection 370 by way of the predetermined gap 470 therebetween (see Figures 9, 10, 11, 16, 17, and 19), provide a compression stop preventing movement between the upper and lower plates 20, 30 in a magnitude greater than a predetermined amount. Varying limits of movement may be set, depending on the type and location of the disc 10 in the body, hi the prefened embodiment, the gap 470 between the first and second projections 270, 370 is approximately 1 to 2 millimeters.
- Elastomers that can handle excessive compressive loadings may be able to accommodate a gap greater than 2 millimeters.
- the visco-elastic cushion 40 absorbs the compression in a visco-elastic fashion according to design properties of the elastomer.
- the first and second projections 270, 370 then come into contact and prevent further compressive loads from being applied to the elastomer. It is expected that the stop mechanism will only be activated during the most strenuous of activities of the patient.
- the motion-limiting members 80 can perform the primary or secondary motion limiting functions.
- the most common bending scenario for the spine is bending in the sagittal plane (that is, bending about the x-axis). For example, this would be accomplished by bending over to tie one's shoes.
- the disc 10 can undergo both shear and lateral displacement.
- Figures 21 and 23 a disc 10 is depicted in such a scenario and is shown exaggerated for easier reference. It can be seen that the anterior side is slightly compressed, while the posterior side is slightly in tension and a slight translation of the upper endplate 20 with respect the lower endplate 30.
- the motion-limiting members 80 can become oriented diagonally, hi this event, the motion-limiting members 80 in tension provide a force preventing the upper endplate 20 and lower endplate 30 from separating because the lower surface 93 of the ball 91 begins to bear upon the split ring assembly 400 and/or bearing surfaces 272 of the openings 271.
- the mechanics of the disc 10 depicted in Figures 21 and 23, with reference to Figure 2 are basically identical whether the bending is in the sagittal plane (front to back, or tying ones shoes) or in the frontal plane (side to side bending).
- the motion-limiting members 80 are strategically oriented to resist the tension in the posterior region of the disc 10.
- compression of the cables can cause splaying, which shortens their fatigue life. Therefore, placing more motion-limiting members 80 posteriorly than anteriorly (for example, see Figure 12) accounts for the greater expected flexion moments of 20-30 N-m versus the lesser extension moments of about 10 N-m.
- a further factor in the allowed range of motion in flexion and extension is a consideration of the cable distance from an assumed center of rotation at the center of the disc 10. The farther from the center, the greater the resisting moment, but the more initial slack necessary to allow the required 8-12 degrees of flexion. The more initial slack allowed, the more bending movement is allowed. Combinations of cable placement and initial diagonal orientation may be necessary to solve these conflicting design goals.
- Preable ranges of stiffnesses and motion for the disc 10 are as follows: Nonlinear stiffness in compression (1,000 to 3,000 N/mm) and in flexion (1.0 to 5.0 N-m/deg) and maximum motion in compression (1.0 to 2.0 mm) and in flexion (8 to 12 deg).
- each motion-limiting member there are conesponding four openings 271, 371 in both the upper and lower subplates, 200, 300.
- One of the openings 271, 371 is located anteriorly and slightly to the left of the first and second projections 270, 370, while another opening 271, 371 is located anteriorly and slightly to the right of the first and second projections 270, 370.
- a third opening 271, 371 is located posteriorly and slightly to the left of the first and second projections 270, 370
- the fourth opening 271, 371 is located posteriorly and slightly to the right of the first and second projection 270, 370.
- the motion-limiting members 80 at the posterior portion of the disc 10 are strategically-oriented to resist the tension in the posterior region of the disc 10, while the motion-limiting members 80 at the anterior portion of the disc 10 float freely in the spike cavity in the anterior region of the disc 10.
- a disadvantage of this embodiment is the presence of motion-limiting members 80 at the anterior portion of the disc 10. As discussed above, when braided cables are used for the motion-limiting members 80, compression can cause splaying, leading to a shorter fatigue life.
- anteriorly-located motion-limiting members 80 are likely to have a shorter life than those located at the posterior of the disc 10.
- FIG. 1 Another embodiment of the artificial disc intervertebral prosthesis is envisioned in which no motion-limiting member 80 is present. Instead, the compression stop formed by the first and second projections 270, 370 also limits motion in flexion and lateral bending. This is accomplished by sizing the first and second projections 270, 370 such that when the prosthesis engages in flexion or bending and the first projection 270 tilts toward the second projection 370, the leading edge of the first projection 270 will come into contact with the second projection 370 after a predetermined amount of flexion or bending, preventing further motion. This has the advantage of eliminating the need for the motion-limiting members 80, thereby reducing the number of elements within the prosthesis that are susceptible to wear and fatigue.
- the prefened disc has certain load versus deflection characteristics that are similar to those found in the natural human disc. As was stated above, it is useful, once implanted, that the surgeon and patient can know the state of load experienced by the device.
- embodiments of the disc have, integral to its construction, strain gauges or other means of force or pressure transduction.
- strain gauges can be connected to signal conditioning and amplification circuitry on a micro scale in order to fit within the constraints of space available in the upper or lower endplate.
- the center stop is integral to the lower endplate and consists of a hollow raised cylindrical platform.
- the space inside this cylinder can house, for example, a 3 x 3 x 3 mm electronics package.
- the package can be wired to strain gauges on the inside of the raised cylinder and in peripheral locations around the bottom endplate.
- the transduction means can be connected to electronics such as piezoelectronics that eliminate the need for signal conditioning and amplification.
- the data can indicate changes in the device since its implantation. It can also store load history to indicate if the patient is following doctor's orders for allowed activities.
- the power source for memory-based data is optionally a micro battery or a capacitor charged from the external inductive couple. The use of piezos is also possible.
- a mylar flex circuit is pre-made and placed on the second endplate. Transducers are embedded on the mylar circuit and connected to the signal conditioning and amplifying electronics.
- Figures 26-29 show an alternative embodiment of the invention wherein the disc 10 comprises multiple components that may be implanted separately. Indeed, the disc 10 may comprise many forms and embodiments that are implantable in pieces. The desirability of multi-part prostheses is known by surgeons and simplifies the implantation procedures.
- Figures 26-29 simply depict one example.
- the appurtenances 27 are removably insertable into the upper and lower endplates 20, 30.
- the upper surface 92 of the balls 91 is not depicted but typically would be visible.
- the groove into which appurtenances 27 are slid form a taper lock fit to lock the appurtenance into place.
- One example of a surgical procedure using a multi-part disc 10 involves the surgeon first removing the diseased or damaged disc using the typical procedures in practice.
- An instrument (not shown) is used to prepare the site by cutting grooves into the adjacent vertebrae to receive the appurtenances 27 of the disc 10.
- the instrument cuts both the upper and lower grooves simultaneously so as to maintain the tolerances needed for the implantation of the disc 10.
- An instrument then inserts the appurtenances 27 into the prepared site.
- the disc 10 is then inserted between the appurtenances 27, which receive the grooves of the upper and lower endplates 20, 30.
- the taper lock secures the appurtenances 27 to the prosthesis.
- the endplates 20, 30 and/or endplate subplates 200, 300 may be of the materials described above. Further, they may have thicknesses in the range of approximately 1 mm to approximately 3 mm. Their surfaces may be surface-treated or machined for texture and bonding improvement. Examples of such treatments include but are not limited to ion etching, simple grit blasting, plasma spraying, or CNC machined geometry.
- the endplates 20, 30 (and/or 200, 300) are a CCM which is good in wear.
- the upper surfaces 21, 210 of the upper endplate 20 and upper subplate 200, and the lower surfaces 31, 310 of the lower endplate 30 and lower subplate 300, as well as the surfaces that interact with the visco-elastic cushion, may be coated with Titanium 6A14V to improve bone interface and bonding.
- the second projection 370 can, as stated above, take many forms, including by way of mere examples, a cylinder, a post, a platform, and so forth.
- the prefened cylindrical member is a solid projection from the lower endplate 20 or lower subplate 200. However, the cylindrical member could be hollow so as to accommodate integral microelectronics diagnostics, as was discussed above.
- the endplates 20, 30 are first machined of either titanium or cobalt chrome molybdenum (CCM), with openings 270 representing areas where there will be no elastomer cushion 40.
- CCM cobalt chrome molybdenum
- the endplates 20, 30 are inserted into a mold with cores to create voids that will later contain the center stop and the motion-limiting members 80. It is preferable to keep the elastomer free of the cables and center stop so as not to introduce elastomer abrasion leading to fatigue failures.
- the motion-limiting members 80 are then assembled to the molded subassembly with a welding process.
- the cable assemblies terminate in a ball end. hi the prefened embodiment the ball is preformed onto the cable, though this is not required.
- the enlarged portion 90 extends beyond the plane of the upper surface 21 of the upper endplate 20 or the lower surface 32 of the lower endplate 30
- these appurtenances serve as temporary anchors in the vertebra and covers that enclose the mini ball-socket joint created between the endplate and the ball.
- the ball-socket articulation prevents bending in the cables, thereby extending fatigue life.
- the motion-limiting members 80 it is possible for the motion-limiting members 80 to be laser welded into the endplates in the openings where cores created voids in the elastomer.
- the center stop is a designed gap preferably to prevent more than 1-2 mm of compression from occuning, thereby limiting the elastomer compressive stress. This mandates a good wear interface for the stop.
- a choice of CCM on CCM is prefened due to its recent introduction as the wear couple in some FDA-approved metal-on-metal hips.
- many structural configurations for the first and second protrusions 270, 370 are possible, including pin-on-pin, pin-on-plate (shown), plate-on-plate, ball-on-plate, and so forth.
- the elastomer will exclusively cany the load during most activities of daily living.
- the center stop will be engaged only during activities of high exertion, except in the embodiment in which no motion-limiting members 80 are present.
Abstract
Description
Claims
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US11/362,424 US7763076B2 (en) | 2003-04-04 | 2006-02-24 | Artificial disc prosthesis |
US11/361,895 US20060259145A1 (en) | 2003-04-04 | 2006-02-24 | Artificial disc prosthesis |
US11/361,733 US7806935B2 (en) | 2003-04-04 | 2006-02-24 | Artificial disc prosthesis |
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US11/361,621 US20060149384A1 (en) | 2003-04-04 | 2006-02-24 | Artificial disc prosthesis |
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US11/362,424 Continuation US7763076B2 (en) | 2003-04-04 | 2006-02-24 | Artificial disc prosthesis |
US11/361,895 Continuation US20060259145A1 (en) | 2003-04-04 | 2006-02-24 | Artificial disc prosthesis |
US11/361,880 Continuation US7771480B2 (en) | 2003-04-04 | 2006-02-24 | Artificial disc prosthesis |
US11/361,621 Continuation US20060149384A1 (en) | 2003-04-04 | 2006-02-24 | Artificial disc prosthesis |
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PCT/US2004/010000 WO2004089240A2 (en) | 2003-04-04 | 2004-04-02 | Artificial disc prosthesis |
Country Status (3)
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Cited By (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2007028098A2 (en) | 2005-09-01 | 2007-03-08 | Spinal Kinetics, Inc. | Prosthetic intervertebral discs |
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US8187333B2 (en) | 2008-09-18 | 2012-05-29 | Mayer Peter L | Intervertebral disc prosthesis and method for implanting and explanting |
US8814937B2 (en) | 2008-09-18 | 2014-08-26 | Peter L. Mayer | Intervertebral disc prosthesis, method for assembling, method for implanting prosthesis, and method for explanting |
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US10390955B2 (en) | 2016-09-22 | 2019-08-27 | Engage Medical Holdings, Llc | Bone implants |
US10456272B2 (en) | 2017-03-03 | 2019-10-29 | Engage Uni Llc | Unicompartmental knee arthroplasty |
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Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FR2824261B1 (en) | 2001-05-04 | 2004-05-28 | Ldr Medical | INTERVERTEBRAL DISC PROSTHESIS AND IMPLEMENTATION METHOD AND TOOLS |
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EP2329778A3 (en) | 2003-01-31 | 2012-06-20 | Spinalmotion, Inc. | Spinal midline indicator |
WO2004066884A1 (en) | 2003-01-31 | 2004-08-12 | Spinalmotion, Inc. | Intervertebral prosthesis placement instrument |
WO2004089240A2 (en) * | 2003-04-04 | 2004-10-21 | Theken Disc, Llc | Artificial disc prosthesis |
US7575599B2 (en) | 2004-07-30 | 2009-08-18 | Spinalmotion, Inc. | Intervertebral prosthetic disc with metallic core |
US10052211B2 (en) | 2003-05-27 | 2018-08-21 | Simplify Medical Pty Ltd. | Prosthetic disc for intervertebral insertion |
WO2004105638A2 (en) | 2003-05-27 | 2004-12-09 | Spinalmotion, Inc. | Prosthetic disc for intervertebral insertion |
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FR2865629B1 (en) | 2004-02-04 | 2007-01-26 | Ldr Medical | INTERVERTEBRAL DISC PROSTHESIS |
PT2113227E (en) | 2004-02-04 | 2015-10-16 | Ldr Medical | Intervertebral disc prosthesis |
US7393361B2 (en) * | 2004-02-20 | 2008-07-01 | Spinecore, Inc. | Artificial intervertebral disc having a bored semispherical bearing with a compression locking post and retaining caps |
FR2869528B1 (en) | 2004-04-28 | 2007-02-02 | Ldr Medical | INTERVERTEBRAL DISC PROSTHESIS |
EP1765204B1 (en) * | 2004-06-07 | 2018-12-26 | Synthes GmbH | Orthopaedic implant with sensors |
US9237958B2 (en) | 2004-06-30 | 2016-01-19 | Synergy Disc Replacement Inc. | Joint prostheses |
EP1773256B1 (en) * | 2004-06-30 | 2019-11-27 | Synergy Disc Replacement Inc. | Artificial spinal disc |
US8172904B2 (en) | 2004-06-30 | 2012-05-08 | Synergy Disc Replacement, Inc. | Artificial spinal disc |
US8114158B2 (en) * | 2004-08-03 | 2012-02-14 | Kspine, Inc. | Facet device and method |
US7585326B2 (en) | 2004-08-06 | 2009-09-08 | Spinalmotion, Inc. | Methods and apparatus for intervertebral disc prosthesis insertion |
US20060069436A1 (en) * | 2004-09-30 | 2006-03-30 | Depuy Spine, Inc. | Trial disk implant |
FR2879436B1 (en) | 2004-12-22 | 2007-03-09 | Ldr Medical | INTERVERTEBRAL DISC PROSTHESIS |
US8083797B2 (en) | 2005-02-04 | 2011-12-27 | Spinalmotion, Inc. | Intervertebral prosthetic disc with shock absorption |
US7799083B2 (en) * | 2005-05-02 | 2010-09-21 | Seaspine, Inc. | Prosthesis for restoring motion in an appendage or spinal joint and an intervertebral spacer |
EP1879531A4 (en) * | 2005-05-02 | 2011-08-03 | Seaspine Inc | Motion restoring intervertebral device |
FR2887762B1 (en) | 2005-06-29 | 2007-10-12 | Ldr Medical Soc Par Actions Si | INTERVERTEBRAL DISC PROSTHESIS INSERTION INSTRUMENTATION BETWEEN VERTEBRATES |
FR2891135B1 (en) | 2005-09-23 | 2008-09-12 | Ldr Medical Sarl | INTERVERTEBRAL DISC PROSTHESIS |
US8070813B2 (en) * | 2005-09-26 | 2011-12-06 | Coalign Innovations, Inc. | Selectively expanding spine cage, hydraulically controllable in three dimensions for vertebral body replacement |
US7985256B2 (en) * | 2005-09-26 | 2011-07-26 | Coalign Innovations, Inc. | Selectively expanding spine cage, hydraulically controllable in three dimensions for enhanced spinal fusion |
US9028550B2 (en) | 2005-09-26 | 2015-05-12 | Coalign Innovations, Inc. | Selectively expanding spine cage with enhanced bone graft infusion |
FR2893838B1 (en) | 2005-11-30 | 2008-08-08 | Ldr Medical Soc Par Actions Si | PROSTHESIS OF INTERVERTEBRAL DISC AND INSTRUMENTATION OF INSERTION OF THE PROSTHESIS BETWEEN VERTEBRATES |
US7691130B2 (en) * | 2006-01-27 | 2010-04-06 | Warsaw Orthopedic, Inc. | Spinal implants including a sensor and methods of use |
US8016859B2 (en) * | 2006-02-17 | 2011-09-13 | Medtronic, Inc. | Dynamic treatment system and method of use |
US10198733B2 (en) * | 2006-03-30 | 2019-02-05 | Alexander Blass | Systems and methods for management of fundraising campaigns |
US8734519B2 (en) | 2006-04-12 | 2014-05-27 | Spinalmotion, Inc. | Posterior spinal device and method |
WO2008033457A2 (en) * | 2006-09-14 | 2008-03-20 | The University Of Toledo | Variable height vertebral body replacement implant |
US8715352B2 (en) * | 2006-12-14 | 2014-05-06 | Depuy Spine, Inc. | Buckling disc replacement |
US20080161928A1 (en) * | 2006-12-27 | 2008-07-03 | Warsaw Orthopedic, Inc. | Compliant intervertebral prosthetic devices with motion constraining tethers |
US20080183292A1 (en) * | 2007-01-29 | 2008-07-31 | Warsaw Orthopedic, Inc. | Compliant intervertebral prosthetic devices employing composite elastic and textile structures |
US8465546B2 (en) | 2007-02-16 | 2013-06-18 | Ldr Medical | Intervertebral disc prosthesis insertion assemblies |
US8673005B1 (en) * | 2007-03-07 | 2014-03-18 | Nuvasive, Inc. | System and methods for spinal fusion |
FR2916956B1 (en) | 2007-06-08 | 2012-12-14 | Ldr Medical | INTERSOMATIC CAGE, INTERVERTEBRAL PROSTHESIS, ANCHORING DEVICE AND IMPLANTATION INSTRUMENTATION |
US10821003B2 (en) | 2007-06-20 | 2020-11-03 | 3Spline Sezc | Spinal osteotomy |
US20090043391A1 (en) | 2007-08-09 | 2009-02-12 | Spinalmotion, Inc. | Customized Intervertebral Prosthetic Disc with Shock Absorption |
US8758441B2 (en) | 2007-10-22 | 2014-06-24 | Spinalmotion, Inc. | Vertebral body replacement and method for spanning a space formed upon removal of a vertebral body |
AU2008316600B2 (en) | 2007-10-25 | 2014-09-18 | Jeffery D. Arnett | Systems and methods for vertebral disc replacement |
US8118873B2 (en) * | 2008-01-16 | 2012-02-21 | Warsaw Orthopedic, Inc. | Total joint replacement |
EP2244671A4 (en) * | 2008-01-25 | 2013-03-20 | Spinalmotion Inc | Intervertebral prosthetic disc with shock absorbing core formed with disc springs |
US20090204213A1 (en) * | 2008-02-13 | 2009-08-13 | Depuy Products, Inc. | Metallic implants |
US8992620B2 (en) | 2008-12-10 | 2015-03-31 | Coalign Innovations, Inc. | Adjustable distraction cage with linked locking mechanisms |
US8932355B2 (en) | 2008-02-22 | 2015-01-13 | Coalign Innovations, Inc. | Spinal implant with expandable fixation |
US20100145455A1 (en) * | 2008-12-10 | 2010-06-10 | Innvotec Surgical, Inc. | Lockable spinal implant |
US8696751B2 (en) * | 2008-12-10 | 2014-04-15 | Coalign Innovations, Inc. | Adjustable distraction cage with linked locking mechanisms |
US8764833B2 (en) | 2008-03-11 | 2014-07-01 | Spinalmotion, Inc. | Artificial intervertebral disc with lower height |
US20090234456A1 (en) * | 2008-03-14 | 2009-09-17 | Warsaw Orthopedic, Inc. | Intervertebral Implant and Methods of Implantation and Treatment |
US9034038B2 (en) | 2008-04-11 | 2015-05-19 | Spinalmotion, Inc. | Motion limiting insert for an artificial intervertebral disc |
KR20110009216A (en) | 2008-05-05 | 2011-01-27 | 스피날모우션, 인코포레이티드 | Polyaryletherketone artificial intervertebral disc |
US9220603B2 (en) | 2008-07-02 | 2015-12-29 | Simplify Medical, Inc. | Limited motion prosthetic intervertebral disc |
EP2299944A4 (en) | 2008-07-17 | 2013-07-31 | Spinalmotion Inc | Artificial intervertebral disc placement system |
US8172902B2 (en) * | 2008-07-17 | 2012-05-08 | Spinemedica, Llc | Spinal interbody spacers |
EP2299941A1 (en) | 2008-07-18 | 2011-03-30 | Spinalmotion Inc. | Posterior prosthetic intervertebral disc |
CA2731048C (en) * | 2008-07-23 | 2016-11-29 | Marc I. Malberg | Modular nucleus pulposus prosthesis |
US9364338B2 (en) | 2008-07-23 | 2016-06-14 | Resspond Spinal Systems | Modular nucleus pulposus prosthesis |
DE102008048739A1 (en) * | 2008-09-24 | 2010-04-01 | Franz Dr. Copf jun. | Disc prosthesis |
US20100100185A1 (en) * | 2008-10-22 | 2010-04-22 | Warsaw Orthopedic, Inc. | Intervertebral Disc Prosthesis Having Viscoelastic Properties |
US8287572B2 (en) * | 2009-02-11 | 2012-10-16 | Howmedica Osteonics Corp. | Intervertebral implant with integrated fixation |
RU2535775C2 (en) * | 2009-02-25 | 2014-12-20 | Спайнуэлдинг Аг | Device for spinal stabilisation, method and kit for implantation thereof |
US8128699B2 (en) * | 2009-03-13 | 2012-03-06 | Warsaw Orthopedic, Inc. | Spinal implant and methods of implantation and treatment |
US20100286777A1 (en) | 2009-05-08 | 2010-11-11 | Stryker Spine | Stand alone anterior cage |
US8421479B2 (en) * | 2009-06-30 | 2013-04-16 | Navisense | Pulsed echo propagation device and method for measuring a parameter |
US9462964B2 (en) * | 2011-09-23 | 2016-10-11 | Orthosensor Inc | Small form factor muscular-skeletal parameter measurement system |
US9700434B2 (en) | 2009-08-10 | 2017-07-11 | Howmedica Osteonics Corp. | Intervertebral implant with integrated fixation |
WO2011056845A1 (en) | 2009-11-03 | 2011-05-12 | Howmedica Osteonics Corp. | Intervertebral implant with integrated fixation |
RU2573945C2 (en) | 2009-12-31 | 2016-01-27 | Лдр Медикал | Fastening device, intervertebral implant and device for implantation |
US8206452B2 (en) * | 2010-02-18 | 2012-06-26 | Biomet Manufacturing Corp. | Prosthetic device with damper |
EP2377495A1 (en) * | 2010-04-19 | 2011-10-19 | Warsaw Orthopedic, Inc. | Spinal implant |
US8747479B2 (en) | 2011-04-26 | 2014-06-10 | Michael A. McShane | Tibial component |
US9615856B2 (en) | 2011-11-01 | 2017-04-11 | Imds Llc | Sacroiliac fusion cage |
US9844335B2 (en) * | 2012-02-27 | 2017-12-19 | Orthosensor Inc | Measurement device for the muscular-skeletal system having load distribution plates |
US9364339B2 (en) | 2012-04-30 | 2016-06-14 | Peter L. Mayer | Unilaterally placed expansile spinal prosthesis |
CN103006356B (en) * | 2013-01-07 | 2018-03-16 | 刘小勇 | A kind of bionic type hydraulic movable artificial vertebral body |
WO2015081240A1 (en) | 2013-11-27 | 2015-06-04 | Coalign Innovations, Inc. | Structurally supporting insert for spinal fusion cage |
JP6860290B2 (en) | 2015-01-14 | 2021-04-14 | ストライカー・ユーロピアン・ホールディングス・I,リミテッド・ライアビリティ・カンパニー | Spine implant with fluid delivery capability |
AU2016200179B2 (en) | 2015-01-14 | 2020-09-17 | Stryker European Operations Holdings Llc | Spinal implant with porous and solid surfaces |
CA2930123A1 (en) | 2015-05-18 | 2016-11-18 | Stryker European Holdings I, Llc | Partially resorbable implants and methods |
EP3103417B1 (en) * | 2015-06-10 | 2018-01-31 | Biedermann Technologies GmbH & Co. KG | Intervertebral implant and system of an intervertebral implant and an instrument for inserting the intervertebral implant |
JP6943598B2 (en) | 2016-04-07 | 2021-10-06 | ハウメディカ・オステオニクス・コーポレイション | Expandable interbody implant |
US10940018B2 (en) | 2016-05-20 | 2021-03-09 | Howmedica Osteonics Corp. | Expandable interbody implant with lordosis correction |
AU2017228529B2 (en) | 2016-09-12 | 2022-03-10 | Howmedica Osteonics Corp. | Interbody implant with independent control of expansion at multiple locations |
AU2017251734B2 (en) | 2016-10-26 | 2022-10-20 | Howmedica Osteonics Corp. | Expandable interbody implant with lateral articulation |
US11540928B2 (en) | 2017-03-03 | 2023-01-03 | Engage Uni Llc | Unicompartmental knee arthroplasty |
EP3456294A1 (en) | 2017-09-15 | 2019-03-20 | Stryker European Holdings I, LLC | Intervertebral body fusion device expanded with hardening material |
EP3459502A1 (en) | 2017-09-20 | 2019-03-27 | Stryker European Holdings I, LLC | Spinal implants |
US10765527B2 (en) | 2017-09-29 | 2020-09-08 | Axiomed, LLC | Artificial disk with sensors |
US10893951B2 (en) * | 2018-08-07 | 2021-01-19 | Minimally Invasive Spinal Technology, LLC | Device and method for correcting spinal deformities in patients |
WO2022182582A1 (en) | 2021-02-23 | 2022-09-01 | Nuvasive Specialized Orthopedics, Inc. | Adjustable implant, system and methods |
CN116763510B (en) * | 2023-08-24 | 2023-12-19 | 北京爱康宜诚医疗器材有限公司 | Intervertebral fusion prosthesis structure |
Family Cites Families (301)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US623525A (en) * | 1899-04-25 | Electric meter | ||
CA992255A (en) | 1971-01-25 | 1976-07-06 | Cutter Laboratories | Prosthesis for spinal repair |
US4057857A (en) * | 1975-09-08 | 1977-11-15 | Shiley Laboratories, Inc. | Heart valve with arcuate occluder |
US4241463A (en) * | 1978-10-16 | 1980-12-30 | Precision Cast Specialties, Inc. | Prosthetic implant device |
CA1146301A (en) | 1980-06-13 | 1983-05-17 | J. David Kuntz | Intervertebral disc prosthesis |
US4309777A (en) | 1980-11-13 | 1982-01-12 | Patil Arun A | Artificial intervertebral disc |
US4688000A (en) * | 1984-05-29 | 1987-08-18 | Donovan John S | Non biased push-pull amplifiers |
US4860751A (en) | 1985-02-04 | 1989-08-29 | Cordis Corporation | Activity sensor for pacemaker control |
US4714468A (en) * | 1985-08-13 | 1987-12-22 | Pfizer Hospital Products Group Inc. | Prosthesis formed from dispersion strengthened cobalt-chromium-molybdenum alloy produced by gas atomization |
CH671691A5 (en) | 1987-01-08 | 1989-09-29 | Sulzer Ag | |
CA1283501C (en) * | 1987-02-12 | 1991-04-30 | Thomas P. Hedman | Artificial spinal disc |
US4714469A (en) * | 1987-02-26 | 1987-12-22 | Pfizer Hospital Products Group, Inc. | Spinal implant |
US4863477A (en) | 1987-05-12 | 1989-09-05 | Monson Gary L | Synthetic intervertebral disc prosthesis |
US4772287A (en) | 1987-08-20 | 1988-09-20 | Cedar Surgical, Inc. | Prosthetic disc and method of implanting |
JPH01136655A (en) | 1987-11-24 | 1989-05-29 | Asahi Optical Co Ltd | Movable type pyramid spacer |
US4874389A (en) | 1987-12-07 | 1989-10-17 | Downey Ernest L | Replacement disc |
DE3809793A1 (en) | 1988-03-23 | 1989-10-05 | Link Waldemar Gmbh Co | SURGICAL INSTRUMENT SET |
DE8807485U1 (en) | 1988-06-06 | 1989-08-10 | Mecron Medizinische Produkte Gmbh, 1000 Berlin, De | |
US4911718A (en) | 1988-06-10 | 1990-03-27 | University Of Medicine & Dentistry Of N.J. | Functional and biocompatible intervertebral disc spacer |
CA1333209C (en) | 1988-06-28 | 1994-11-29 | Gary Karlin Michelson | Artificial spinal fusion implants |
US5609635A (en) | 1988-06-28 | 1997-03-11 | Michelson; Gary K. | Lordotic interbody spinal fusion implants |
US5545229A (en) | 1988-08-18 | 1996-08-13 | University Of Medicine And Dentistry Of Nj | Functional and biocompatible intervertebral disc spacer containing elastomeric material of varying hardness |
AU624627B2 (en) | 1988-08-18 | 1992-06-18 | Johnson & Johnson Orthopaedics, Inc. | Functional and biocompatible intervertebral disc spacer containing elastomeric material of varying hardness |
CA1318469C (en) * | 1989-02-15 | 1993-06-01 | Acromed Corporation | Artificial disc |
US5370694A (en) * | 1989-07-25 | 1994-12-06 | Smith & Nephew Richards, Inc. | Zirconium oxide and nitride coated endoprostheses for tissue protection |
US5062850A (en) | 1990-01-16 | 1991-11-05 | University Of Florida | Axially-fixed vertebral body prosthesis and method of fixation |
FR2659226B1 (en) | 1990-03-07 | 1992-05-29 | Jbs Sa | PROSTHESIS FOR INTERVERTEBRAL DISCS AND ITS IMPLEMENTATION INSTRUMENTS. |
US5123926A (en) | 1991-02-22 | 1992-06-23 | Madhavan Pisharodi | Artificial spinal prosthesis |
JP3007903B2 (en) | 1991-03-29 | 2000-02-14 | 京セラ株式会社 | Artificial disc |
US5197488A (en) * | 1991-04-05 | 1993-03-30 | N. K. Biotechnical Engineering Co. | Knee joint load measuring instrument and joint prosthesis |
US5306307A (en) | 1991-07-22 | 1994-04-26 | Calcitek, Inc. | Spinal disk implant |
US5320644A (en) | 1991-08-30 | 1994-06-14 | Sulzer Brothers Limited | Intervertebral disk prosthesis |
US5425773A (en) | 1992-01-06 | 1995-06-20 | Danek Medical, Inc. | Intervertebral disk arthroplasty device |
US5258031A (en) | 1992-01-06 | 1993-11-02 | Danek Medical | Intervertebral disk arthroplasty |
DE4208115A1 (en) | 1992-03-13 | 1993-09-16 | Link Waldemar Gmbh Co | DISC ENDOPROTHESIS |
DE4208116C2 (en) | 1992-03-13 | 1995-08-03 | Link Waldemar Gmbh Co | Intervertebral disc prosthesis |
ATE141149T1 (en) * | 1992-04-21 | 1996-08-15 | Sulzer Medizinaltechnik Ag | ARTIFICIAL DISC BODY |
DE4213771C1 (en) * | 1992-04-27 | 1993-09-30 | Eska Medical Gmbh & Co | Spinal disc endoprosthesis - has elastic core with rim beading between shaped cover plates with a screw bonding for implantation without adhesive |
US5306309A (en) | 1992-05-04 | 1994-04-26 | Calcitek, Inc. | Spinal disk implant and implantation kit |
US5431694A (en) | 1992-08-18 | 1995-07-11 | Snaper; Alvin A. | Bio-operable power source |
US5716407A (en) | 1992-08-24 | 1998-02-10 | Lipomatrix, Incorporated | Method of rendering identifiable a living tissue implant using an electrical transponder marker |
US5300120A (en) | 1992-08-24 | 1994-04-05 | Lipomatrix Incorporated | Implant with electrical transponder marker |
US5326363A (en) | 1992-09-14 | 1994-07-05 | Zimmer, Inc. | Provisional implant |
US5246458A (en) | 1992-10-07 | 1993-09-21 | Graham Donald V | Artificial disk |
US5511561A (en) * | 1992-11-16 | 1996-04-30 | Wanderman; Steven M. | Gait cycle force monitor |
US5676701A (en) | 1993-01-14 | 1997-10-14 | Smith & Nephew, Inc. | Low wear artificial spinal disc |
ATE205069T1 (en) | 1993-02-09 | 2001-09-15 | Acromed Corp | DISC |
US5476465A (en) * | 1993-04-21 | 1995-12-19 | Amei Technologies Inc. | Surgical cable crimp |
FR2707480B1 (en) | 1993-06-28 | 1995-10-20 | Bisserie Michel | Intervertebral disc prosthesis. |
FR2709949B1 (en) | 1993-09-14 | 1995-10-13 | Commissariat Energie Atomique | Intervertebral disc prosthesis. |
US5425772A (en) | 1993-09-20 | 1995-06-20 | Brantigan; John W. | Prosthetic implant for intervertebral spinal fusion |
US5456724A (en) * | 1993-12-15 | 1995-10-10 | Industrial Technology Research Institute | Load sensor for bone graft |
US5514180A (en) | 1994-01-14 | 1996-05-07 | Heggeness; Michael H. | Prosthetic intervertebral devices |
US5458642A (en) | 1994-01-18 | 1995-10-17 | Beer; John C. | Synthetic intervertebral disc |
US5536270A (en) * | 1994-02-24 | 1996-07-16 | Pioneer Laboratories, Inc. | Cable system for bone securance |
WO1998020939A2 (en) | 1996-11-15 | 1998-05-22 | Advanced Bio Surfaces, Inc. | Biomaterial system for in situ tissue repair |
WO1995031946A1 (en) | 1994-05-24 | 1995-11-30 | Smith & Nephew Plc | Intervertebral disc implant |
GB9415180D0 (en) | 1994-07-28 | 1994-09-21 | Walker Peter S | Stabilised mobile bearing knee |
US7494507B2 (en) | 2000-01-30 | 2009-02-24 | Diamicron, Inc. | Articulating diamond-surfaced spinal implants |
US5674296A (en) | 1994-11-14 | 1997-10-07 | Spinal Dynamics Corporation | Human spinal disc prosthesis |
FR2728159B1 (en) | 1994-12-16 | 1997-06-27 | Tornier Sa | ELASTIC DISC PROSTHESIS |
US6149688A (en) | 1995-06-07 | 2000-11-21 | Surgical Dynamics, Inc. | Artificial bone graft implant |
US6423095B1 (en) | 1995-10-16 | 2002-07-23 | Sdgi Holdings, Inc. | Intervertebral spacers |
ATE349190T1 (en) | 1995-11-08 | 2007-01-15 | Zimmer Gmbh | DEVICE FOR INSERTING AN IMPLANT, IN PARTICULAR AN INTERVERBAL PROSTHESIS |
US5683465A (en) | 1996-03-18 | 1997-11-04 | Shinn; Gary Lee | Artificial intervertebral disk prosthesis |
US5861018A (en) | 1996-05-28 | 1999-01-19 | Telecom Medical Inc. | Ultrasound transdermal communication system and method |
US7104986B2 (en) | 1996-07-16 | 2006-09-12 | Arthrocare Corporation | Intervertebral disc replacement method |
US5782832A (en) | 1996-10-01 | 1998-07-21 | Surgical Dynamics, Inc. | Spinal fusion implant and method of insertion thereof |
US5895428A (en) | 1996-11-01 | 1999-04-20 | Berry; Don | Load bearing spinal joint implant |
US5749909A (en) | 1996-11-07 | 1998-05-12 | Sulzer Intermedics Inc. | Transcutaneous energy coupling using piezoelectric device |
US5827328A (en) | 1996-11-22 | 1998-10-27 | Buttermann; Glenn R. | Intervertebral prosthetic device |
US7169123B2 (en) * | 1997-01-22 | 2007-01-30 | Advanced Medical Optics, Inc. | Control of pulse duty cycle based upon footswitch displacement |
US6034296A (en) | 1997-03-11 | 2000-03-07 | Elvin; Niell | Implantable bone strain telemetry sensing system and method |
US6033438A (en) | 1997-06-03 | 2000-03-07 | Sdgi Holdings, Inc. | Open intervertebral spacer |
US5893889A (en) * | 1997-06-20 | 1999-04-13 | Harrington; Michael | Artificial disc |
GB9713330D0 (en) | 1997-06-25 | 1997-08-27 | Bridport Gundry Plc | Surgical implant |
US6529127B2 (en) | 1997-07-11 | 2003-03-04 | Microstrain, Inc. | System for remote powering and communication with a network of addressable, multichannel sensing modules |
US6259937B1 (en) * | 1997-09-12 | 2001-07-10 | Alfred E. Mann Foundation | Implantable substrate sensor |
US5824094A (en) | 1997-10-17 | 1998-10-20 | Acromed Corporation | Spinal disc |
US20010016773A1 (en) | 1998-10-15 | 2001-08-23 | Hassan Serhan | Spinal disc |
US6139579A (en) | 1997-10-31 | 2000-10-31 | Depuy Motech Acromed, Inc. | Spinal disc |
US5888226A (en) | 1997-11-12 | 1999-03-30 | Rogozinski; Chaim | Intervertebral prosthetic disc |
US5935171A (en) | 1997-11-17 | 1999-08-10 | John E. Schneider | Apparatus for, and method of, detecting dislocations and material wear in hip replacements |
US5899941A (en) | 1997-12-09 | 1999-05-04 | Chubu Bearing Kabushiki Kaisha | Artificial intervertebral disk |
US6162252A (en) | 1997-12-12 | 2000-12-19 | Depuy Acromed, Inc. | Artificial spinal disc |
US6086613A (en) * | 1997-12-23 | 2000-07-11 | Depuy Acromed, Inc. | Spacer assembly for use in spinal surgeries |
US5989291A (en) | 1998-02-26 | 1999-11-23 | Third Millennium Engineering, Llc | Intervertebral spacer device |
US6679915B1 (en) | 1998-04-23 | 2004-01-20 | Sdgi Holdings, Inc. | Articulating spinal implant |
US6179874B1 (en) * | 1998-04-23 | 2001-01-30 | Cauthen Research Group, Inc. | Articulating spinal implant |
US6019792A (en) | 1998-04-23 | 2000-02-01 | Cauthen Research Group, Inc. | Articulating spinal implant |
US6800093B2 (en) | 1998-05-06 | 2004-10-05 | Cortek, Inc. | Device for spinal fusion |
US6368325B1 (en) | 1998-05-27 | 2002-04-09 | Nuvasive, Inc. | Bone blocks and methods for inserting bone blocks into intervertebral spaces |
US6132465A (en) | 1998-06-04 | 2000-10-17 | Raymedica, Inc. | Tapered prosthetic spinal disc nucleus |
US6296664B1 (en) | 1998-06-17 | 2001-10-02 | Surgical Dynamics, Inc. | Artificial intervertebral disc |
US6136031A (en) | 1998-06-17 | 2000-10-24 | Surgical Dynamics, Inc. | Artificial intervertebral disc |
DE19829637C2 (en) | 1998-07-02 | 2000-10-19 | Implex Hear Tech Ag | Medical implant |
US6231609B1 (en) | 1998-07-09 | 2001-05-15 | Hamid M. Mehdizadeh | Disc replacement prosthesis |
US5928284A (en) | 1998-07-09 | 1999-07-27 | Mehdizadeh; Hamid M. | Disc replacement prosthesis |
US6063121A (en) | 1998-07-29 | 2000-05-16 | Xavier; Ravi | Vertebral body prosthesis |
CA2342633C (en) | 1998-09-04 | 2007-11-13 | Spinal Dynamics Corporation | Peanut spectacle multi discoid thoraco-lumbar disc prosthesis |
US6059784A (en) | 1998-10-08 | 2000-05-09 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Capacitive extensometer particularly suited for measuring in vivo bone strain |
FR2784891B1 (en) | 1998-10-22 | 2001-01-26 | Hassan Razian | INTERSOMATIC CAGE WITH HOLDING DEVICE |
US6039763A (en) | 1998-10-27 | 2000-03-21 | Disc Replacement Technologies, Inc. | Articulating spinal disc prosthesis |
US6193757B1 (en) | 1998-10-29 | 2001-02-27 | Sdgi Holdings, Inc. | Expandable intervertebral spacers |
FR2787017B1 (en) | 1998-12-11 | 2001-04-27 | Dimso Sa | INTERVERTEBRAL DISC PROSTHESIS WITH IMPROVED MECHANICAL BEHAVIOR |
FR2787016B1 (en) | 1998-12-11 | 2001-03-02 | Dimso Sa | INTERVERTEBRAL DISK PROSTHESIS |
FR2787019B1 (en) * | 1998-12-11 | 2001-03-02 | Dimso Sa | INTERVERTEBRAL DISC PROSTHESIS WITH IMPROVED MECHANICAL BEHAVIOR |
US6115636A (en) | 1998-12-22 | 2000-09-05 | Medtronic, Inc. | Telemetry for implantable devices using the body as an antenna |
US6447448B1 (en) * | 1998-12-31 | 2002-09-10 | Ball Semiconductor, Inc. | Miniature implanted orthopedic sensors |
US6206923B1 (en) | 1999-01-08 | 2001-03-27 | Sdgi Holdings, Inc. | Flexible implant using partially demineralized bone |
US6368350B1 (en) | 1999-03-11 | 2002-04-09 | Sulzer Spine-Tech Inc. | Intervertebral disc prosthesis and method |
US6170488B1 (en) | 1999-03-24 | 2001-01-09 | The B. F. Goodrich Company | Acoustic-based remotely interrogated diagnostic implant device and system |
US6216537B1 (en) | 1999-03-31 | 2001-04-17 | Medtronic, Inc. | Accelerometer for implantable medical device |
US6110210A (en) | 1999-04-08 | 2000-08-29 | Raymedica, Inc. | Prosthetic spinal disc nucleus having selectively coupled bodies |
AU4810800A (en) | 1999-04-26 | 2000-11-10 | Li Medical Technologies, Inc. | Prosthetic apparatus and method |
US6579321B1 (en) | 1999-05-17 | 2003-06-17 | Vanderbilt University | Intervertebral disc replacement prosthesis |
US6419704B1 (en) | 1999-10-08 | 2002-07-16 | Bret Ferree | Artificial intervertebral disc replacement methods and apparatus |
US6491724B1 (en) | 1999-08-13 | 2002-12-10 | Bret Ferree | Spinal fusion cage with lordosis correction |
US6366206B1 (en) * | 1999-06-02 | 2002-04-02 | Ball Semiconductor, Inc. | Method and apparatus for attaching tags to medical and non-medical devices |
US6520996B1 (en) * | 1999-06-04 | 2003-02-18 | Depuy Acromed, Incorporated | Orthopedic implant |
CA2376097A1 (en) | 1999-06-04 | 2000-12-14 | Sdgi Holdings, Inc. | Artificial disc implant |
CA2391330C (en) | 1999-07-02 | 2008-11-18 | Spine Solutions Inc. | Intervertebral implant |
WO2002009626A1 (en) | 1999-07-26 | 2002-02-07 | Advanced Prosthetic Technologies, Inc. | Improved spinal surgical prosthesis |
NL1012719C1 (en) | 1999-07-28 | 2001-01-30 | Veldhuizen Dr Ag | Spine prosthesis. |
US20040249461A1 (en) | 1999-08-13 | 2004-12-09 | Ferree Bret A. | Coupled artificial disc replacements methods and apparatus |
US7201776B2 (en) | 1999-10-08 | 2007-04-10 | Ferree Bret A | Artificial intervertebral disc replacements with endplates |
US7507243B2 (en) | 1999-08-18 | 2009-03-24 | Gregory Lambrecht | Devices and method for augmenting a vertebral disc |
JP4247519B2 (en) | 1999-08-18 | 2009-04-02 | イントリンジック セラピューティックス インコーポレイテッド | Apparatus and method for nucleus augmentation and retention |
US6264695B1 (en) | 1999-09-30 | 2001-07-24 | Replication Medical, Inc. | Spinal nucleus implant |
US7060100B2 (en) | 1999-10-08 | 2006-06-13 | Ferree Bret A | Artificial disc and joint replacements with modular cushioning components |
US7201774B2 (en) | 1999-10-08 | 2007-04-10 | Ferree Bret A | Artificial intervertebral disc replacements incorporating reinforced wall sections |
US20040260286A1 (en) | 1999-10-08 | 2004-12-23 | Ferree Bret A. | Intradiscal devices with anti-extrusion keels |
US20050273111A1 (en) | 1999-10-08 | 2005-12-08 | Ferree Bret A | Methods and apparatus for intervertebral disc removal and endplate preparation |
US6878167B2 (en) | 2002-04-24 | 2005-04-12 | Bret A. Ferree | Methods and apparatus for placing intradiscal devices |
US20050256582A1 (en) | 1999-10-08 | 2005-11-17 | Ferree Bret A | Spinal implants, including devices that reduce pressure on the annulus fibrosis |
US6436101B1 (en) * | 1999-10-13 | 2002-08-20 | James S. Hamada | Rasp for use in spine surgery |
JP4326134B2 (en) | 1999-10-20 | 2009-09-02 | ウォーソー・オーソペディック・インコーポレーテッド | Method and apparatus for performing a surgical procedure |
US6592625B2 (en) | 1999-10-20 | 2003-07-15 | Anulex Technologies, Inc. | Spinal disc annulus reconstruction method and spinal disc annulus stent |
US20030153976A1 (en) | 1999-10-20 | 2003-08-14 | Cauthen Joseph C. | Spinal disc annulus reconstruction method and spinal disc annulus stent |
US7004970B2 (en) | 1999-10-20 | 2006-02-28 | Anulex Technologies, Inc. | Methods and devices for spinal disc annulus reconstruction and repair |
US6830570B1 (en) | 1999-10-21 | 2004-12-14 | Sdgi Holdings, Inc. | Devices and techniques for a posterior lateral disc space approach |
US6764491B2 (en) | 1999-10-21 | 2004-07-20 | Sdgi Holdings, Inc. | Devices and techniques for a posterior lateral disc space approach |
WO2001028469A2 (en) | 1999-10-21 | 2001-04-26 | Sdgi Holdings, Inc. | Devices and techniques for a posterior lateral disc space approach |
US6245109B1 (en) | 1999-11-18 | 2001-06-12 | Intellijoint Systems, Ltd. | Artificial joint system and method utilizing same for monitoring wear and displacement of artificial joint members |
RU2264787C2 (en) * | 1999-11-24 | 2005-11-27 | Инновэйтив Девелопмент Энд Маркетинг Ас | Method and device for training pelvic fundus muscles |
US6395034B1 (en) | 1999-11-24 | 2002-05-28 | Loubert Suddaby | Intervertebral disc prosthesis |
US6592624B1 (en) | 1999-11-24 | 2003-07-15 | Depuy Acromed, Inc. | Prosthetic implant element |
DE10011564C1 (en) | 2000-03-09 | 2001-09-27 | Goldschmidt Ag Th | Process for the preparation of polyorganosiloxane emulsions |
FR2805985B1 (en) | 2000-03-10 | 2003-02-07 | Eurosurgical | INTERVERTEBRAL DISK PROSTHESIS |
US6805695B2 (en) | 2000-04-04 | 2004-10-19 | Spinalabs, Llc | Devices and methods for annular repair of intervertebral discs |
ATE390099T1 (en) | 2000-04-04 | 2008-04-15 | Link Spine Group Inc | INTERVERBEL PLASTIC IMPLANT |
US6350283B1 (en) | 2000-04-19 | 2002-02-26 | Gary K. Michelson | Bone hemi-lumbar interbody spinal implant having an asymmetrical leading end and method of installation thereof |
US6482234B1 (en) | 2000-04-26 | 2002-11-19 | Pearl Technology Holdings, Llc | Prosthetic spinal disc |
US6851430B2 (en) | 2000-05-01 | 2005-02-08 | Paul M. Tsou | Method and apparatus for endoscopic spinal surgery |
AU2001261969A1 (en) | 2000-05-25 | 2001-12-03 | Neurortho Implants Design, Llc | Inter-vertebral disc prosthesis for rachis for an anterior surgery thereof |
DE60141964D1 (en) | 2000-06-29 | 2010-06-10 | Mount Sinai Hospital Corp | LUMBAR |
FR2811540B1 (en) | 2000-07-12 | 2003-04-25 | Spine Next Sa | IMPORTING INTERVERTEBRAL IMPLANT |
US6610093B1 (en) | 2000-07-28 | 2003-08-26 | Perumala Corporation | Method and apparatus for stabilizing adjacent vertebrae |
US7601174B2 (en) | 2000-08-08 | 2009-10-13 | Warsaw Orthopedic, Inc. | Wear-resistant endoprosthetic devices |
CA2424553C (en) * | 2000-08-25 | 2008-01-29 | The Cleveland Clinic Foundation | Apparatus and method for assessing loads on adjacent bones |
US6620196B1 (en) | 2000-08-30 | 2003-09-16 | Sdgi Holdings, Inc. | Intervertebral disc nucleus implants and methods |
AU2001293581A1 (en) | 2000-09-26 | 2002-04-08 | Neurortho Implants Design, Llc | Inter-vertebral disc prosthesis for lumbar rachis through posterior surgery thereof |
CA2323252C (en) | 2000-10-12 | 2007-12-11 | Biorthex Inc. | Artificial disc |
US6764446B2 (en) | 2000-10-16 | 2004-07-20 | Remon Medical Technologies Ltd | Implantable pressure sensors and methods for making and using them |
US6733531B1 (en) | 2000-10-20 | 2004-05-11 | Sdgi Holdings, Inc. | Anchoring devices and implants for intervertebral disc augmentation |
ATE417577T1 (en) | 2000-10-24 | 2009-01-15 | Warsaw Orthopedic Inc | DEVICES FOR SPINAL FUSION |
US6692528B2 (en) | 2000-11-09 | 2004-02-17 | The Polymer Technology Group Incorporated | Devices that change size/shape via osmotic pressure |
US6579319B2 (en) | 2000-11-29 | 2003-06-17 | Medicinelodge, Inc. | Facet joint replacement |
US6773460B2 (en) | 2000-12-05 | 2004-08-10 | Roger P. Jackson | Anterior variable expandable fusion cage |
US6565605B2 (en) | 2000-12-13 | 2003-05-20 | Medicinelodge, Inc. | Multiple facet joint replacement |
US6692501B2 (en) | 2000-12-14 | 2004-02-17 | Gary K. Michelson | Spinal interspace shaper |
FR2818530B1 (en) | 2000-12-22 | 2003-10-31 | Spine Next Sa | INTERVERTEBRAL IMPLANT WITH DEFORMABLE SHIM |
US6468311B2 (en) | 2001-01-22 | 2002-10-22 | Sdgi Holdings, Inc. | Modular interbody fusion implant |
FR2819715B1 (en) | 2001-01-25 | 2004-01-02 | Cousin Biotech | BONE REPAIR DEVICE |
US6863689B2 (en) | 2001-07-16 | 2005-03-08 | Spinecore, Inc. | Intervertebral spacer having a flexible wire mesh vertebral body contact element |
US6607559B2 (en) | 2001-07-16 | 2003-08-19 | Spine Care, Inc. | Trial intervertebral distraction spacers |
US6764515B2 (en) | 2001-02-15 | 2004-07-20 | Spinecore, Inc. | Intervertebral spacer device utilizing a spirally slotted belleville washer and a rotational mounting |
US6669730B2 (en) | 2001-02-15 | 2003-12-30 | Spinecore, Inc. | Intervertebral spacer device utilizing a spirally slotted belleville washer having radially extending grooves |
US7563285B2 (en) | 2001-07-16 | 2009-07-21 | Spinecore, Inc. | Artificial intervertebral disc utilizing a ball joint coupling |
US6673113B2 (en) | 2001-10-18 | 2004-01-06 | Spinecore, Inc. | Intervertebral spacer device having arch shaped spring elements |
US7235081B2 (en) | 2001-07-16 | 2007-06-26 | Spinecore, Inc. | Wedge plate inserter/impactor and related methods for use in implanting an artificial intervertebral disc |
US6989032B2 (en) | 2001-07-16 | 2006-01-24 | Spinecore, Inc. | Artificial intervertebral disc |
WO2002098332A1 (en) | 2001-02-16 | 2002-12-12 | Sulzer Spine-Tech Inc. | Bone implants and methods |
JP4790917B2 (en) | 2001-02-23 | 2011-10-12 | 独立行政法人科学技術振興機構 | Artificial vertebral body |
US6652585B2 (en) | 2001-02-28 | 2003-11-25 | Sdgi Holdings, Inc. | Flexible spine stabilization system |
US6478822B1 (en) | 2001-03-20 | 2002-11-12 | Spineco, Inc. | Spherical spinal implant |
US6368351B1 (en) | 2001-03-27 | 2002-04-09 | Bradley J. Glenn | Intervertebral space implant for use in spinal fusion procedures |
WO2002085261A1 (en) * | 2001-04-20 | 2002-10-31 | Douglas Stafford Maclennan | Intervertebral disc implant device |
US6607558B2 (en) | 2001-07-03 | 2003-08-19 | Axiomed Spine Corporation | Artificial disc |
US6468310B1 (en) | 2001-07-16 | 2002-10-22 | Third Millennium Engineering, Llc | Intervertebral spacer device having a wave washer force restoring element |
US6890356B2 (en) | 2001-07-16 | 2005-05-10 | Spinecore, Inc. | Surgical method of treating scoliosis |
US7153310B2 (en) | 2001-07-16 | 2006-12-26 | Spinecore, Inc. | Vertebral bone distraction instruments |
US7160327B2 (en) | 2001-07-16 | 2007-01-09 | Spinecore, Inc. | Axially compressible artificial intervertebral disc having limited rotation using a captured ball and socket joint with a solid ball and compression locking post |
US6471725B1 (en) | 2001-07-16 | 2002-10-29 | Third Millenium Engineering, Llc | Porous intervertebral distraction spacers |
US6436102B1 (en) | 2001-07-16 | 2002-08-20 | Third Millennium Engineering, Llc | Method of distracting vertebral bones |
IL159459A0 (en) | 2001-07-16 | 2004-06-01 | Spinecore Inc | Artificial intervertebral disc having a wave washer force restoring element |
US6447548B1 (en) | 2001-07-16 | 2002-09-10 | Third Millennium Engineering, Llc | Method of surgically treating scoliosis |
US6527806B2 (en) | 2001-07-16 | 2003-03-04 | Third Millennium Engineering, Llc | Intervertebral spacer device having a spiral wave washer force restoring element |
US7182784B2 (en) | 2001-07-18 | 2007-02-27 | Smith & Nephew, Inc. | Prosthetic devices employing oxidized zirconium and other abrasion resistant surfaces contacting surfaces of cross-linked polyethylene |
US6610096B2 (en) | 2001-08-22 | 2003-08-26 | Macdonald Stuart G. | Prosthetic implants having enhanced utility |
ATE398430T1 (en) | 2001-08-24 | 2008-07-15 | Zimmer Gmbh | ARTIFICIAL DISC |
EP1287795B1 (en) | 2001-08-24 | 2008-06-18 | Zimmer GmbH | Artificial spinal disc |
US20040024463A1 (en) | 2001-08-27 | 2004-02-05 | Thomas James C. | Expandable implant for partial disc replacement and reinforcement of a disc partially removed in a discectomy and for reduction and maintenance of alignment of cancellous bone fractures and methods and apparatuses for same |
ATE318558T1 (en) | 2001-08-28 | 2006-03-15 | Johannes Schroeder | SPINE IMPLANT WITH ADJUSTABLE HEIGHT |
DE20115281U1 (en) | 2001-09-10 | 2001-11-22 | Aesculap Ag & Co Kg | Implant |
JP4394441B2 (en) | 2001-10-02 | 2010-01-06 | レックス メディカル リミテッド パートナーシップ | Spinal implant |
US7179295B2 (en) | 2001-10-05 | 2007-02-20 | Nebojsa Kovacevic | Prosthetic shock absorber |
US20030069644A1 (en) | 2001-10-05 | 2003-04-10 | Nebojsa Kovacevic | Dual-tray teletibial implant |
WO2003032801A2 (en) | 2001-10-18 | 2003-04-24 | Third Millennium Engineering Llc | Artificial intervertebral disc having a spider spring force restoring element |
US7025787B2 (en) | 2001-11-26 | 2006-04-11 | Sdgi Holdings, Inc. | Implantable joint prosthesis and associated instrumentation |
FR2832917B1 (en) | 2001-11-30 | 2004-09-24 | Spine Next Sa | ELASTICALLY DEFORMABLE INTERVERTEBRAL IMPLANT |
US7052515B2 (en) | 2001-12-07 | 2006-05-30 | Simonson Rush E | Vertebral implant with dampening matrix adapted for posterior insertion |
US6572653B1 (en) | 2001-12-07 | 2003-06-03 | Rush E. Simonson | Vertebral implant adapted for posterior insertion |
JP3553919B2 (en) | 2001-12-12 | 2004-08-11 | コーリンメディカルテクノロジー株式会社 | Lower limb artery stenosis diagnostic device |
US6740118B2 (en) | 2002-01-09 | 2004-05-25 | Sdgi Holdings, Inc. | Intervertebral prosthetic joint |
FR2835739B1 (en) | 2002-02-11 | 2004-05-14 | Spinevision | SYSTEM FOR FIXING A WORKPIECE ON A BONE BODY |
US20030181982A1 (en) | 2002-03-04 | 2003-09-25 | Spineology, Inc. | No-profile, lumbo-sacral fixation device and method |
WO2003077808A2 (en) | 2002-03-11 | 2003-09-25 | Spinal Concepts, Inc. | Instrumentation and procedure for implanting spinal implant devices |
RU2303422C2 (en) | 2002-03-12 | 2007-07-27 | Сервитек Инк. | Intervertebral prosthesis and system of intervertebral prostheses, in peculiar case, for cervical department of vertebral column |
EP1344508B1 (en) | 2002-03-12 | 2007-06-06 | Cervitech, Inc. | Intervertebral prosthesis especially for the cervical spine |
EP1344507A1 (en) | 2002-03-12 | 2003-09-17 | Waldemar Link (GmbH & Co.) | Intervertebral prosthesis for the cervical spine |
US20030176921A1 (en) | 2002-03-13 | 2003-09-18 | Lawson Kevin Jon | Two-part prosthetic nucleus replacement for surgical reconstruction of intervertebral discs |
FR2837094B1 (en) | 2002-03-15 | 2004-11-26 | Fixano | INTERVERTEBRAL IMPLANT |
US6991653B2 (en) | 2002-03-21 | 2006-01-31 | Sdgi Holdings, Inc. | Vertebral body and disc space replacement devices |
US6726720B2 (en) | 2002-03-27 | 2004-04-27 | Depuy Spine, Inc. | Modular disc prosthesis |
EP2246012A2 (en) | 2002-03-30 | 2010-11-03 | Infinity Orthopaedics Company, Ltd. | Intervertebral Device |
US20030195630A1 (en) | 2002-04-10 | 2003-10-16 | Ferree Bret A. | Disc augmentation using materials that expand in situ |
US20080027548A9 (en) | 2002-04-12 | 2008-01-31 | Ferree Bret A | Spacerless artificial disc replacements |
US20030195631A1 (en) | 2002-04-12 | 2003-10-16 | Ferree Bret A. | Shape-memory spacers for artificial disc replacements |
US8038713B2 (en) | 2002-04-23 | 2011-10-18 | Spinecore, Inc. | Two-component artificial disc replacements |
US20060106462A1 (en) * | 2002-04-16 | 2006-05-18 | Tsou Paul M | Implant material for minimally invasive spinal interbody fusion surgery |
US6706068B2 (en) | 2002-04-23 | 2004-03-16 | Bret A. Ferree | Artificial disc replacements with natural kinematics |
US20030233148A1 (en) | 2002-04-23 | 2003-12-18 | Ferree Bret A. | Modular components to improve the fit of artificial disc replacements |
DE10218093B4 (en) | 2002-04-23 | 2005-04-07 | Signus Medizintechnik Gmbh | spinal implant |
US20030233097A1 (en) | 2002-04-23 | 2003-12-18 | Ferree Bret A. | Artificial disc replacement (ADR) distraction sleeves and cutting guides |
US20040030390A1 (en) | 2002-04-23 | 2004-02-12 | Ferree Bret A. | Intradiscal component installation apparatus and methods |
US7156848B2 (en) | 2002-04-24 | 2007-01-02 | Ferree Bret A | Check reins for artificial disc replacements |
US20040030391A1 (en) | 2002-04-24 | 2004-02-12 | Bret Ferree | Artificial intervertebral disc spacers |
US7179294B2 (en) | 2002-04-25 | 2007-02-20 | Warsaw Orthopedic, Inc. | Articular disc prosthesis and method for implanting the same |
JP4315816B2 (en) | 2002-04-25 | 2009-08-19 | ブラックストーン メディカル,インコーポレーテッド | Artificial disc |
US7338525B2 (en) | 2002-04-30 | 2008-03-04 | Ferree Bret A | Methods and apparatus for preventing the migration of intradiscal devices |
US7386351B2 (en) * | 2002-04-30 | 2008-06-10 | Medtronic, Inc. | Method and apparatus for placing a coronary sinus/cardiac vein pacing and defibriliation lead with adjustable electrode spacing |
DE10220139A1 (en) | 2002-05-06 | 2003-11-20 | Tutogen Medical Gmbh | Bone material implant |
US20040024461A1 (en) | 2002-05-10 | 2004-02-05 | Ferree Bret A. | Spring and spherical joint artificial disc replacements |
US7066958B2 (en) | 2002-05-10 | 2006-06-27 | Ferree Bret A | Prosthetic components with partially contained compressible resilient members |
US7235102B2 (en) | 2002-05-10 | 2007-06-26 | Ferree Bret A | Prosthetic components with contained compressible resilient members |
US7291171B2 (en) | 2002-05-10 | 2007-11-06 | Ferree Bret A | Artificial disc replacement (ADR) using elastic tether member |
US7223227B2 (en) | 2002-05-13 | 2007-05-29 | Pflueger D Russell | Spinal disc therapy system |
US20040010318A1 (en) | 2002-05-15 | 2004-01-15 | Ferree Bret A. | Conformable endplates for artificial disc replacement (ADR) devices and other applications |
US6689132B2 (en) | 2002-05-15 | 2004-02-10 | Spineco, Inc. | Spinal implant insertion tool |
US6840944B2 (en) | 2002-05-21 | 2005-01-11 | Loubert Suddaby | Vertebral body end plate cutter |
US7001433B2 (en) | 2002-05-23 | 2006-02-21 | Pioneer Laboratories, Inc. | Artificial intervertebral disc device |
US20040049283A1 (en) | 2002-06-04 | 2004-03-11 | Tushar Patel | Medical implant and method of reducing back pain |
US6770095B2 (en) | 2002-06-18 | 2004-08-03 | Depuy Acroned, Inc. | Intervertebral disc |
FR2841123B1 (en) | 2002-06-25 | 2004-08-27 | Hassan Razian | IMPROVED INTERVERTEBRAL CAGE |
US7033393B2 (en) | 2002-06-27 | 2006-04-25 | Raymedica, Inc. | Self-transitioning spinal disc anulus occulsion device and method of use |
US6981991B2 (en) | 2002-06-27 | 2006-01-03 | Ferree Bret A | Arthroplasty devices configured to reduce shear stress |
AU2003253746A1 (en) | 2002-06-27 | 2004-01-19 | Bret A. Ferree | Arthroplasty devices for improved bone ingrowth |
US6793678B2 (en) | 2002-06-27 | 2004-09-21 | Depuy Acromed, Inc. | Prosthetic intervertebral motion disc having dampening |
US6682564B1 (en) | 2002-07-02 | 2004-01-27 | Luis Duarte | Intervertebral support device and related methods |
US20040010312A1 (en) | 2002-07-09 | 2004-01-15 | Albert Enayati | Intervertebral prosthesis |
US7101400B2 (en) | 2002-08-19 | 2006-09-05 | Jeffery Thramann | Shaped memory artificial disc and methods of engrafting the same |
US6958078B2 (en) | 2002-08-19 | 2005-10-25 | The University Of Toledo | Bioartificial intervertebral disc |
US20040049270A1 (en) | 2002-09-10 | 2004-03-11 | Gewirtz Robert J. | Bone graft device |
DE10242329B4 (en) | 2002-09-12 | 2005-03-17 | Biedermann Motech Gmbh | Disc prosthesis |
US20040054413A1 (en) | 2002-09-16 | 2004-03-18 | Howmedica Osteonics Corp. | Radiovisible hydrogel intervertebral disc nucleus |
JP4210648B2 (en) | 2002-09-18 | 2009-01-21 | ジンテーズ ゲゼルシャフト ミト ベシュレンクテル ハフツング | Implant with a two-part joint |
WO2004026190A2 (en) | 2002-09-18 | 2004-04-01 | Sdgi Holdings, Inc. | Natural tissue devices and methods of implantation |
US20040054414A1 (en) | 2002-09-18 | 2004-03-18 | Trieu Hai H. | Collagen-based materials and methods for augmenting intervertebral discs |
US6932843B2 (en) | 2002-09-25 | 2005-08-23 | Medicinelodge, Inc. | Apparatus and method for the in-situ formation of a structural prosthesis |
US6899735B2 (en) | 2002-10-02 | 2005-05-31 | Sdgi Holdings, Inc. | Modular intervertebral prosthesis system |
US20040106998A1 (en) | 2002-10-04 | 2004-06-03 | Ferree Bret A. | Multiaxial artificial disc replacements |
US20040068321A1 (en) | 2002-10-04 | 2004-04-08 | Ferree Bret A. | Reduced-friction artificial disc replacements |
US20040068320A1 (en) | 2002-10-04 | 2004-04-08 | Robie Bruce H. | Prosthetic disc and vertebral body replacement device having pyrolytic carbon bearing members |
US7156876B2 (en) | 2002-10-09 | 2007-01-02 | Depuy Acromed, Inc. | Intervertebral motion disc having articulation and shock absorption |
DE10247762A1 (en) | 2002-10-14 | 2004-04-22 | Waldemar Link (Gmbh & Co.) | Intervertebral prosthesis |
US7267688B2 (en) | 2002-10-22 | 2007-09-11 | Ferree Bret A | Biaxial artificial disc replacement |
JP4654125B2 (en) | 2002-10-29 | 2011-03-16 | スパインコア,インコーポレイテッド | Instruments, methods, and functions for use in implanting an artificial disc |
US6966929B2 (en) | 2002-10-29 | 2005-11-22 | St. Francis Medical Technologies, Inc. | Artificial vertebral disk replacement implant with a spacer |
AU2003287370B2 (en) | 2002-10-31 | 2009-05-07 | Zimmer Spine, Inc. | Movable disc implant |
FR2846550B1 (en) | 2002-11-05 | 2006-01-13 | Ldr Medical | INTERVERTEBRAL DISC PROSTHESIS |
US20040093087A1 (en) | 2002-11-05 | 2004-05-13 | Ferree Bret A. | Fluid-filled artificial disc replacement (ADR) |
US6733533B1 (en) | 2002-11-19 | 2004-05-11 | Zimmer Technology, Inc. | Artificial spinal disc |
US20040186471A1 (en) | 2002-12-07 | 2004-09-23 | Sdgi Holdings, Inc. | Method and apparatus for intervertebral disc expansion |
US7169181B2 (en) * | 2002-12-10 | 2007-01-30 | Axiomed Spine Corporation | Artificial disc |
US7204852B2 (en) | 2002-12-13 | 2007-04-17 | Spine Solutions, Inc. | Intervertebral implant, insertion tool and method of inserting same |
US7004971B2 (en) | 2002-12-31 | 2006-02-28 | Depuy Acromed, Inc. | Annular nucleus pulposus replacement |
WO2004089240A2 (en) | 2003-04-04 | 2004-10-21 | Theken Disc, Llc | Artificial disc prosthesis |
WO2004098466A2 (en) | 2003-05-02 | 2004-11-18 | Smart Disc, Inc. | Artificial spinal disk |
JP2007511746A (en) | 2003-05-29 | 2007-05-10 | アップチャーチ・サイエンティフィック・インコーポレイテッド | Improved apparatus and method for electrospray applications |
US7048766B2 (en) | 2003-06-06 | 2006-05-23 | Ferree Bret A | Methods and apparatus for total disc replacements with oblique keels |
US7008452B2 (en) | 2003-06-26 | 2006-03-07 | Depuy Acromed, Inc. | Dual durometer elastomer artificial disc |
US20040267367A1 (en) | 2003-06-30 | 2004-12-30 | Depuy Acromed, Inc | Intervertebral implant with conformable endplate |
US20050015150A1 (en) | 2003-07-17 | 2005-01-20 | Lee Casey K. | Intervertebral disk and nucleus prosthesis |
US7153325B2 (en) | 2003-08-01 | 2006-12-26 | Ultra-Kinetics, Inc. | Prosthetic intervertebral disc and methods for using the same |
US7695517B2 (en) | 2003-12-10 | 2010-04-13 | Axiomed Spine Corporation | Apparatus for replacing a damaged spinal disc |
US7556651B2 (en) | 2004-01-09 | 2009-07-07 | Warsaw Orthopedic, Inc. | Posterior spinal device and method |
US7794499B2 (en) * | 2004-06-08 | 2010-09-14 | Theken Disc, L.L.C. | Prosthetic intervertebral spinal disc with integral microprocessor |
WO2006017130A2 (en) * | 2004-07-09 | 2006-02-16 | Pioneer Laboratories, Inc. | Skeletal reconstruction device |
US7172628B2 (en) | 2004-07-27 | 2007-02-06 | Lonnie Jay Lamprich | Spinal disc prosthesis and methods |
US7419506B2 (en) | 2005-11-18 | 2008-09-02 | Zimmer Spine, Inc. | Artificial spinal discs and methods |
-
2004
- 2004-04-02 WO PCT/US2004/010000 patent/WO2004089240A2/en active Application Filing
- 2004-04-02 EP EP04758711A patent/EP1610740A4/en not_active Withdrawn
- 2004-04-02 US US10/552,094 patent/US7771478B2/en not_active Expired - Fee Related
-
2006
- 2006-02-24 US US11/361,621 patent/US20060149384A1/en not_active Abandoned
- 2006-02-24 US US11/362,424 patent/US7763076B2/en not_active Expired - Fee Related
- 2006-02-24 US US11/361,880 patent/US7771480B2/en not_active Expired - Fee Related
- 2006-02-24 US US11/361,733 patent/US7806935B2/en not_active Expired - Fee Related
- 2006-02-24 US US11/361,895 patent/US20060259145A1/en not_active Abandoned
- 2006-02-24 US US11/361,131 patent/US7763075B2/en not_active Expired - Fee Related
Non-Patent Citations (1)
Title |
---|
See references of EP1610740A4 * |
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US7850697B2 (en) | 2004-12-06 | 2010-12-14 | Axiomed Spine Corporation | Method and apparatus for replacing a spinal disc |
EP1824430A2 (en) * | 2004-12-06 | 2007-08-29 | Axiomed Spine Corporation | Method and apparatus for replacing a spinal disc |
CN101111208A (en) * | 2004-12-06 | 2008-01-23 | 公理医学脊骨公司 | Method and apparatus for replacing a spinal disc |
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EP1824430A4 (en) * | 2004-12-06 | 2012-10-24 | Axiomed Spine Corp | Method and apparatus for replacing a spinal disc |
EP1928362A4 (en) * | 2005-09-01 | 2009-08-26 | Spinal Kinetics Inc | Prosthetic intervertebral discs |
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US8187333B2 (en) | 2008-09-18 | 2012-05-29 | Mayer Peter L | Intervertebral disc prosthesis and method for implanting and explanting |
US8814937B2 (en) | 2008-09-18 | 2014-08-26 | Peter L. Mayer | Intervertebral disc prosthesis, method for assembling, method for implanting prosthesis, and method for explanting |
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US10238382B2 (en) | 2012-03-26 | 2019-03-26 | Engage Medical Holdings, Llc | Blade anchor for foot and ankle |
US9393126B2 (en) | 2012-04-20 | 2016-07-19 | Peter L. Mayer | Bilaterally placed disc prosthesis for spinal implant and method of bilateral placement |
US10390955B2 (en) | 2016-09-22 | 2019-08-27 | Engage Medical Holdings, Llc | Bone implants |
US10456272B2 (en) | 2017-03-03 | 2019-10-29 | Engage Uni Llc | Unicompartmental knee arthroplasty |
Also Published As
Publication number | Publication date |
---|---|
US7771478B2 (en) | 2010-08-10 |
US7763076B2 (en) | 2010-07-27 |
EP1610740A4 (en) | 2009-04-08 |
EP1610740A2 (en) | 2006-01-04 |
WO2004089240A3 (en) | 2007-11-01 |
US20060136061A1 (en) | 2006-06-22 |
US20060259146A1 (en) | 2006-11-16 |
US20060149377A1 (en) | 2006-07-06 |
US7771480B2 (en) | 2010-08-10 |
US20060142860A1 (en) | 2006-06-29 |
US20060259143A1 (en) | 2006-11-16 |
US7763075B2 (en) | 2010-07-27 |
US20060259145A1 (en) | 2006-11-16 |
US7806935B2 (en) | 2010-10-05 |
US20060149384A1 (en) | 2006-07-06 |
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