Bone fixated, articulated joint load control device

Information

  • Patent Grant
  • 9610103
  • Patent Number
    9,610,103
  • Date Filed
    Friday, April 17, 2009
    14 years ago
  • Date Issued
    Tuesday, April 4, 2017
    6 years ago
  • Inventors
  • Original Assignees
  • Examiners
    • Hoffman; Mary
    Agents
    • Cermak; Adam J.
    • Cermak Nakajima & McGowan LLP
Abstract
A load control device can be attached to bones on either side of an articulated joint in order to control the forces and loads experienced by the joint. The device comprises an apparatus for controlling the load on articular cartilage of a human or animal joint and includes: a first fixation assembly for attachment to a first bone; a second fixation assembly for attachment to a second bone; a link assembly coupled to the first fixation assembly by a first pivot and coupled to the second fixation assembly by a second pivot, the first and second fixation assembly thereby each being angularly displaceable relative to the link assembly. The apparatus enables a clinician to effectively control the environment of cartilage in a joint during a treatment episode.
Description
BACKGROUND

The present invention relates to devices for restricting or controlling the movement or loading levels on joints in the human or animal body.


The human or animal body uses articular cartilage to surface many of its joints. This tissue tolerates relatively high levels of compression while having a low coefficient of friction—approximately that of wet ice on wet ice.


Bone, on which the cartilage is supported, is stiffer and stronger. Away from the joints, bone normally forms in large, thick-walled tubes. However, under the cartilage at the joints, the bone forms a three dimensional mesh of so called “cancellous” bone. Cancellous bone is more compliant than the rest of the bone structure and helps spread the load that the cartilage experiences, thus reducing the peak stresses on the cartilage.


Both cartilage and bone are living tissues that respond and adapt to the loads they experience. There is strong evidence that the loads that joint surfaces experience can be categorised into four regions or “loading zones”.


1. Under-Loading Zone.


If a joint surface remains unloaded for appreciable periods of time the cartilage tends to soften and weaken.


2. Healthy Zone.


Joint surfaces can and do last a lifetime and if they experience healthy levels of load they can be considered to effectively last indefinitely.


3. Tolerant Zone.


As with engineering materials that experience structural loads, both bone and cartilage begin to show signs of failure at loads that are below their ultimate strength. Unlike engineering materials, however, cartilage and bone have some ability to repair themselves, bone more so. There are levels of loading that will cause micro-structural problems and trigger the repair processes. The body can tolerate these load levels as long as it has time to recuperate.


4. Overloaded Zone.


There comes a level of load at which the skeleton will fail catastrophically. If the load level on a joint surface reaches this level even once then there will be severe consequences.


One of the major consequences of excessive loading is osteoarthritis. This loading could be either from a single overload in the overloaded zone or from loading within the tolerant zone too frequently.


The picture of safe joint loading is further complicated by the cascade of events that occur during the onset of osteoarthritis. These events include the break up of the cartilage, and bone sclerosis in which the bone becomes denser and stiffer. This means that the maximum level of loading that can be considered healthy or tolerated falls, almost certainly to levels below that experienced in walking and standing.


Newly implanted grafts or tissue-engineered constructs will also have lower tolerance limits while they are establishing themselves within the joint.


In fact the treatment of osteoarthritis and other conditions is severely hampered when a surgeon is not able to control and prescribe the levels of joint load. Furthermore, bone healing research has shown that some mechanical stimulation can enhance the healing response and it is likely that the optimum regime for a cartilage/bone graft or construct will involve different levels of load over time, eg. during a particular treatment schedule.


There is a need for a device that will facilitate the control of load on a joint undergoing treatment or therapy, to enable use of the joint within the healthy loading zone, or even within the healthy and tolerant loading zones, during the treatment episode.


There is further need for a device to preferably provide such control while allowing full, or relatively full mobility of a patient undergoing the treatment.


Such devices would be desirable particularly during the early treatment of, for example, an osteoarthritic joint. Under an appropriate treatment regime providing controlled loading, the condition of the joint may improve, possibly back to full health.


In the prior art, existing load controlling regimes and devices for use in treatment or therapy of articulating joints include the following.


a) Bed-rest or isolation of a joint is possible but, as indicated above, the long-term consequences of applying no load or generally maintaining the joint in the underloaded zone are not good.


b) Passive movement of a joint has been tried with some success. During this treatment, movement is applied to the joint by an external device while the joint is rested. However, this does not give the opportunity to vary the load levels on the joint, eg. to work the joint within the healthy zone for that joint at any given stage of the treatment program.


c) Traction across a joint has long been used to counteract the compressive loads normally experienced by the joint. This is done either in bed or using an external fixator. Fixators exist which not only apply traction, but also have simple hinges to allow some joint motion.


d) External braces have been used to apply a bending moment across the joint and at 90.degree. to the motion to move the centre of pressure from one part of the joint to another. However, since these braces are not attached directly to the skeleton, control of the applied loads is poor.


According to one aspect, the present invention provides an apparatus for controlling the load on articular cartilage of a human or animal joint comprising:


a first fixation assembly for attachment to a first bone;


a second fixation assembly for attachment to a second bone; and


a link assembly coupled to the first fixation assembly by a first pivot and coupled to the second fixation assembly by a second pivot,


the first and second fixation assembly thereby each being angularly displaceable relative to the link assembly.


According to another aspect, the present invention provides a method of controlling loading on a joint comprising the steps of:


attaching a first fixation assembly to a first bone;


attaching a second fixation assembly to a second bone, the second bone being connected to the second bone by an articulating joint;


coupling said first fixation assembly and said second fixation assembly by way of a link assembly so that said first fixation assembly and said second fixation assembly are each angularly displaceable relative to the link assembly.





BRIEF DESCRIPTION OF THE DRAWINGS


FIG. 1 shows a perspective view of a fixator for controlling loads on articular cartilage according to a preferred embodiment of the present invention;



FIG. 2 shows a perspective view of a pair of fixators of FIG. 2 in a dual sided or bilateral configuration;



FIG. 3 shows perspective views of a selection of central modules suitable for use with the fixators of FIGS. 1 and 2;



FIG. 4 shows a perspective view of an externally powered fixator;



FIG. 5 shows perspective views of a selection of alternative fixation assemblies suitable for use in the fixators of FIGS. 1 and 2;



FIG. 6 shows a plan view of a bilateral configuration of fixators as in FIG. 2, illustrating the effects of unilateral variation in the length of link assembly; and



FIG. 7 shows a parallel-crosswise configuration of link assembly.





DETAILED DESCRIPTION

With reference to FIG. 1, there is shown an articulated joint load controlling device or fixator 10 according to one embodiment of the invention. The fixator 10 comprises a first fixation assembly 11, a second fixation assembly 12 and a link assembly 13 connecting the first and second fixation assemblies 11, 12.


The first and second fixation assemblies 11, 12 are each coupled to the link assembly 13 by a pivot 14, 15 or other equivalent means facilitating angular displacement of the respective fixation assembly to the link assembly. Throughout the present specification, use of the word “pivot” is intended to encompass all such equivalent means for facilitating angular displacement. It will be understood that the first and second fixation assemblies 11, 12 are therefore not only angularly displaceable relative to one another, but are also capable of some relative translational movement subject to the geometric limitations provided by the link assembly 13.


Preferably, the axes of the pivots 14, 15 are parallel so that the first and second fixation assemblies 11, 12 will rotate about the link assembly in the same plane.


In an alternative embodiment, however, the pivots 14 and 15 might not be axially parallel, in order to better follow the three-dimensional movement of a particular joint. In a further embodiment, one or both pivots 14, 15 might be of the universal joint type, such that the pivot allows two degrees of rotational freedom rather than only a single degree of rotational freedom, in order to better follow the three-dimensional movement of, for example, a ball joint.


Each fixation assembly 11, 12 preferably comprises a faceplate 20 having one or more slots 21 defined in the faceplate surface. Coupled to the faceplate 20 is a clamp plate 22 which may be tightened onto the faceplate 20 by way of screws, or other means known in the art. Preferably, the clamp plate includes corresponding slots 23. As shown more clearly in FIG. 2, the face plate 20 and clamp plate 22 together provide an anchorage for one or more bone pins 30 which can be screwed into or otherwise fixed to a bone using known techniques. Other examples of fixation assemblies are illustrated later in connection with FIG. 5.


In the arrangement of FIG. 1, a single load controlling fixator 10 may be attached to an articulating joint by way of first bone pins 30 screwed into one side of a first bone using the first fixation assembly 11, and second bone pins 30 screwed into a corresponding side of a second bone using the second fixation assembly 12. The first and second bones are on either side of an articulating joint to be controlled by the fixator.


In the arrangement of FIG. 2, two load controlling devices or fixators may be used in a bilateral configuration on either side of an articulating joint, the bone pins 30 passing right through the respective first and second bones on either side of the articulating joint. By applying compression in one fixator and tension in the other fixator, it is possible to apply a bending moment to the joint so as to move the centre of pressure within the joint in a controlled manner and so relieve the loads experienced by the areas of concern.


In further embodiments, first and second fixation assemblies 11, 12 of a fixator 10 might be coupled to two or more link assemblies in series or in parallel with one another. For example, as shown in FIG. 7, a fixator 16 comprises a first fixation assembly 11 and a second fixation assembly 12 that are connected by a link assembly that comprises a pair of link members 18, 19 in a parallel-crosswise configuration. Each link member is pivotally anchored to both the first and second fixation assemblies 11, 12 by way of face plates 17, the link members being laterally displaced from one another. In the embodiment shown, the link member 18 and link member 19 are not only laterally displaced from one another, but also angularly displaced from one another, in a crosswise formation. This arrangement provides a controlled, limited degree of freedom of relative movement of the first and second fixation assemblies. By adjusting the position of the two link members it is possible to mimic the movement of the knee.


Referring now to FIG. 3, various arrangements of link assemblies and their respective functions will now be described.


In a first arrangement, labelled FIG. 3A, the link assembly 40 comprises a rigid, fixed length member having a barrel centre section 41 and a pair of lugs 44 extending from each end. Each pair of lugs 44 includes a pair of coaxial apertures or hubs 42, 43 in which can rotate respective pivot pins 14, 15 (FIG. 1). Each pair of lugs 44 define therebetween a slot 45 adapted to receive a corresponding lug 25 (see FIG. 1) of a respective fixation assembly 11 or 12. The link assembly 40 essentially maintains first and second pivots 14 and 15 at a fixed distance of separation.


In a further embodiment, the lug pairs 44 and barrel centre section 41 may be screwed together for quick disassembly and re-assembly, enabling different length barrel centre sections 41 to readily be used to provide a link assembly 40 of an appropriate length to the joint under treatment or therapy and to be changed during a treatment program.


In another arrangement, labelled FIG. 3C, a link assembly 50 provides for a variable distance of separation of pivots 14, 15 in hubs 52, 53. Link assembly 50 comprises a pair of lugs 54 and a pair of lugs 55, each pair being mounted on a central shaft 56 and being axially displaceable therealong. A pair of tension springs 57, 58 provide a means for biasing the distance of separation of the pivots 14, 15 towards a minimum limit of separation of the lug pairs 54, 55 to apply greater compression forces than those normally experienced by the joint.


In another arrangement, labelled FIG. 3D, a link assembly 60 provides for a variable distance of separation of pivots 14, 15 in hubs 62, 63. Link assembly 60 comprises a pair of lugs 64 and a pair of lugs 65, each pair being mounted on a central shaft 66 and being axially displaceable therealong. A compression spring 67 provides a means for biasing the distance of separation of the pivots 14, 15 towards a maximum limit of separation of the lug pairs 64, 65 so as to counteract the natural compressive forces experienced by the joint.


It will be understood that the functions of link assembly 50 and link assembly 60 may be combined to provide bias towards a central position so that there is resistance against movement of the pairs of lugs from a centre position. More generally, this provides means for biasing the first and second pivots towards an intermediate distance of separation between predetermined limits of separation of the lug pairs 54, 55 or 64, 65.


Although not shown in FIG. 3C or 3D, it is also possible to provide a locking member which is axially adjustable along the length of the link assembly to adjust the limit or limits of separation of the lug pairs. The locking member could be provided, for example, by way of a screw-threaded collar on the central shaft 56 or 66 using techniques that will be understood by those skilled in the art.


In another arrangement, labelled as FIG. 3F, the provision of a means for controlling the distance of separation of pivots 14, 15 could be by way of a link assembly 80 that includes a pneumatic or hydraulic cylinder 81, controlled externally by a controller (not shown) connected thereto by two feed pipes 82, 83. The pneumatic or hydraulic cylinder may also provide means for biasing the distance of separation of the first and second pivots to a predetermined position.


It will be understood that the functions of the pneumatic or hydraulic cylinder 81 could be alternatively provided by an electrically driven system.


In another arrangement, labeled FIG. 3E, the link assembly 70 (which may generally correspond with a links 50 or 60 having variable separation members) may also be provided with a mechanism for varying the distance of separation of the pivots 14, 15 according to the angular displacement of the first and/or second fixation assemblies relative to the link assembly. This would enable, for example, the separation to be increased in the last 5° of angular displacement.


In the preferred embodiment shown, a cam surface 76, 77 is provided on the circumferential edge of one or both of the lug pairs 74, 75 including a pair of coaxial apertures or hubs 72, 73. The cam surface bears on a corresponding bearing surface on a respective fixation assembly 11, 12 and is preferably adapted to vary the separation of the fixation assemblies as a function of the angular displacement. As an example, for a fixator attached to a knee joint, the cam surfaces 76, 77 can be arranged so that as the knee is moved to the fully extended condition, the fixator ensures a greater separation of the fixation assemblies 11, 12 thereby reducing pressure on the joint surfaces.


In another arrangement, the cam surfaces 76, 77 could be adapted to limit the angular displacement of that fixation assembly.


In another arrangement, the cam surfaces may be used to provide a varying degree of resistance to angular displacement of the fixation assembly. More generally, the cam surface may be adapted to provide a means for progressively increasing resistance to angular displacement of the fixation assembly relative to the link assembly as a function of the angular displacement from a reference position.


The means for limiting angular displacement could alternatively be provided by a stepped surface on the circumferential edge of the lug in a manner which will be understood by those skilled in the art.


In conjunction with any of the link assemblies described above, a link assembly 90 as shown in FIG. 3B may be provided with means for recording loads applied across the link assembly. The sensor may be adapted to monitor any one or more of the tensile load, the compression load, shear forces or bending forces applied across the link assembly. Preferably the sensor comprises a strain gauge. Such a device makes it possible to determine the load actually being carried by a joint. In the preferred embodiment shown, this is achieved by the installation of strain gauges 92 into the barrel 93 of the link assembly 90.


Separate transducers could be added to monitor angular displacement of the fixation assemblies relative to the link assembly 90.


In another arrangement, as shown in FIG. 4, the angular displacement of the fixation assemblies relative to one another may be controlled externally. This can be achieved by a linear actuator 100 linked to the first and second fixation assemblies 11, 12 by way of brackets 17, 18 each extending from a respective fixation assembly in a direction orthogonal to the pivot axis.


The linear actuator 100 may be powered electrically, pneumatically or hydraulically and enables movement of a joint to be automatically controlled for exercise within the healthy load zone without use of the associated musculature.


Referring back to FIG. 2, it will be noted that when the various link assemblies described in connection with FIG. 3 are used in the bilateral configuration, it is possible, by varying the length of the link assembly 13 independently on either side of the joint, to alter the position of the centre of pressure in the joint. This can be particularly useful in the treatment of knees. An example of the effects of this is illustrated in FIG. 6. In the figure, a bilateral configuration of fixation assemblies is shown similar to that of FIG. 2, viewed from above (ie. generally perpendicular to the pivot axes). In this example, fixation assemblies 11a, 12a and 11b, 12b are respectively connected by link assemblies 13a, 13b. A unilateral adjustment of the length of link assembly 13b results in a relative angular displacement of the bones 4, 5 that varies with articulation of the bones about the axis of the joint, thereby imposing an angulation on the joint. This will tend to have the effect of reducing the load experienced at the joint surface on the side nearest to the lengthened segment.


With reference to FIG. 5, alternative arrangements of fixation assemblies which themselves facilitate further angular degrees of freedom of the fixator are now described. FIG. 5A shows a fixation assembly 110 have a lug 25 for attachment to the various possible link assemblies 13, 40, 50, 60, 70, 80, 90. The body of the fixation assembly includes a plurality of apertures 111a, 111b, 111c each adapted to receive a bone pin 30. In this arrangement, however, each aperture is defined in a corresponding rotatable collar 112a, 112b, 112c such that the angles of the bone pins 30 may be varied on and about the central longitudinal axis of the fixation assembly 110.


The fixation assembly 120 as shown in FIG. 5b is similar to that of FIG. 5a, except that in this case the apertures 121a, 121b, 121c are laterally offset from the central longitudinal axis of the fixation assembly. Each aperture is again defined in a corresponding rotatable collar 122a, 122b, 122c so that the angles of the bone pins 30 may be varied about a longitudinal axis that is laterally displaced from the central longitudinal axis of the fixation assembly 120.


The fixation assembly 130 as shown in FIG. 5c provides a further degree of freedom. In this arrangement, bone pins 30 are located in slots 131 formed between a first clamp plate 132 and a second clamp plate 133. The clamp plates 132, 133 are rotatable about a first axis (transverse to a longitudinal axis of the fixation assembly 130) on pivot 134, and about a second axis (preferably a longitudinal axis of the fixation assembly 130) on pivot 135. Taken together with the pivot through aperture 136, this provides a full three rotational degrees of freedom of the bone relative to a link assembly.


The fixator device embodiments as generally described above therefore provide a means for applying and/or limiting tension, compression, torsion, bending and shear forces to an articulated joint in a controlled manner and provide for some or all of the following treatment regimes either in isolation or in any combination. Also it will be possible to change the regime or combination of regimes easily and without the need for a sterile environment or anaesthesia. It is noted that joints of the skeleton naturally experience compression and the fixators of the present invention can provide amelioration of this by applying tension.


1. Continuous Traction.


The level of tension can be varied according to the length of the link assembly used and this can be further varied according to the bias strengths applied by the springs 57, 58, 67.


2. Partial or Full Support.


Some or all of the compression that would otherwise be carried by the joint may be taken by the device, and this can be a function of the angle of support by control of spring strength and angle of fixation to the bones.


3. Application of a Bending Moment, Torsion or Shear Force.


Application of these loads to the joint allows the clinician to move the centre of pressure within the joint to regions that are healthy.


4. Application of an Externally Powered Loading Regime.


This can occur normally while the subject is at rest at set angles, load levels, loading and unloading rates and frequencies using the powered embodiments described above. Providing a portable power supply will, however, allow the patient to continue to move freely.


5. Allowing the Joint Load to be Gradually Increased.


This may be desirable at the end of a treatment episode. This can be done either by applying additional compression or a bending moment, shear force or torsion in the opposite direction from that described above.


6. Load Measurement.


The device as described in connection with FIG. 3B allows the clinician to detect and record the loads experienced across a joint, and also the load applied across the joint by the device.


The motive forces applied across the joints may be from normal physiological loads of the musculoskeletal system or from an externally applied source such as described with reference to FIG. 4.


It will be noted that the preferred design of the devices described above enable the link assemblies and fixation assemblies to be readily disconnected from the bone pins 30 in order to replace or adjust the devices during a treatment schedule. Still further, in the preferred designs, the link assemblies may be adjusted in situ. Preferably, the devices will be able to be removed in their entirety within an outpatient clinic.


The articulated joint controlling devices of the present invention can be used in the treatment not only of rheumatoid arthritis, but for the treatment of many other conditions such as articular fractures, and following surgical procedures such as osteochondral transfers and joint surface replacement with cartilage graft.


Other embodiments are within the scope of the appended claims.

Claims
  • 1. An apparatus for controlling the load on articular cartilage of a knee joint, the apparatus comprising: a first fixation assembly for attachment to a first bone of the knee joint;a second fixation assembly for attachment to a second bone of the knee joint; anda link assembly including a biasing structure, a first pivot having at least two degrees of rotational freedom, a second pivot, and a rigid central shaft defining an axis, the first and second pivots being axially displaceable along the shaft, the link assembly being coupled to the first fixation assembly by the first pivot and coupled to the second fixation assembly by the second pivot;wherein the first and second fixation assemblies are angularly displaceable relative to the link assembly to allow relatively full mobility of the knee joint in the at least two degrees of freedom when mounted thereto, and wherein the link assembly controls the load on the articular cartilage during articulation of the knee joint while the first and second pivots are freely pivotable during articulation of the knee joint.
  • 2. The apparatus according to claim 1 in which the link assembly includes a variable separation member for permitting the first and second pivots to vary in their distance of separation within predetermined limits.
  • 3. The apparatus according to claim 1 in which the variable separation member includes bias means for biasing the first and second pivots towards a maximum limit of separation distance.
  • 4. The apparatus according to claim 1 in which the variable separation member includes bias means for biasing the first and second pivots towards a minimum limit of separation distance.
  • 5. The apparatus according to claim 1 in which the variable separation member includes bias means for biasing the first and second pivots towards an intermediate distance of separation between said predetermined limits.
  • 6. The apparatus according to claim 1 in which the variable separation member further includes drive means for controllably varying the distance of separation of the first and second pivots.
  • 7. The apparatus according to claim 1 comprising a pair of link assemblies each pivotally anchored to both the first and second fixation assemblies and laterally displaced from one another.
  • 8. An apparatus for controlling the load on articular cartilage of a knee joint, the apparatus comprising: a first fixation assembly for attachment to a first bone of the knee joint;a second fixation assembly for attachment to a second bone of the knee joint; anda link assembly including a biasing structure and being coupled to the first fixation assembly by a first pivot having at least two degrees of rotational freedom and coupled to the second fixation assembly by a second pivot, the first and second fixation assemblies thereby each being angularly displaceable relative to the link assembly to allow relatively full mobility of the knee joint in the at least two degrees of freedom; anda pair of link assemblies each pivotally anchored to both the first and second fixation assemblies and laterally displaced from one another;wherein the pair of link assemblies comprise a first link member and a second link member that are laterally and angularly displaced from one another.
  • 9. The apparatus according to claim 8 in which the first link member and the second link members are disposed in a crosswise formation.
  • 10. The apparatus according to claim 1, wherein the first and second pivots carry load so that the apparatus provides reduction of pressure on the joint when mounted across the knee joint.
  • 11. The apparatus according to claim 1, wherein the first and second pivots are universal joints.
  • 12. The apparatus according to claim 11, wherein the universal joints are ball joints.
  • 13. The apparatus according to claim 1, wherein the biasing structure comprises a compression spring.
  • 14. The apparatus according to claim 13, wherein the compression spring counteracts natural compressive forces experienced by the joint.
  • 15. The apparatus according to claim 1, wherein the link assembly further comprises a mechanism for varying the distance of separation of the pivots according to the angular displacement of the joint.
  • 16. The apparatus according to claim 15, wherein the mechanism for varying the distance of separation is configured such that the separation is increased in the last 5° of angular displacement.
  • 17. The apparatus according to claim 1, wherein the first and second fixation assemblies are configured to be fixed to first and second bones of the knee joint.
  • 18. An apparatus for controlling loading on a knee joint, the knee joint connecting first and second bones, the apparatus comprising: a first fixation assembly configured and arranged for attachment to the knee joint first bone;a second fixation assembly configured and arranged for attachment to the knee joint second bone; anda link assembly including a biasing structure, a first pivot having at least two degrees of rotational freedom, a second pivot, and a rigid central shaft defining an axis, the first and second pivots being axially displaceable along the shaft, the link assembly;wherein said first fixation assembly and said second fixation assembly are each angularly displaceable relative to the link assembly so that there is at least two degrees of rotational freedom between the link assembly and the first fixation assembly and relatively full mobility of the knee joint in the at least two degrees of freedom, and wherein the link assembly controls the load on the knee joint during articulation of the knee joint while the first and second pivots are freely pivotable during articulation of the knee joint when the apparatus is mounted across the knee joint.
  • 19. An apparatus for controlling the load on articular cartilage of a knee joint, the apparatus comprising: a first fixation assembly for attachment to a first bone of the knee joint;a second fixation assembly for attachment to a second bone of the knee joint; anda link assembly including a biasing structure, a first pivot having at least two degrees of rotational freedom, a second pivot, and a central shaft defining an axis, the first and second pivots being axially displaceable along the shaft, the link assembly being coupled to the first fixation assembly by the first pivot and coupled to the second fixation assembly by the second pivot;wherein the first and second fixation assemblies are angularly displaceable relative to the link assembly to allow relatively full mobility of the knee joint in the at least two degrees of freedom when mounted thereto, and wherein the link assembly controls the load on the articular cartilage during articulation of the knee joint while the first and second pivots are freely pivotable during articulation of the knee joint.
Priority Claims (1)
Number Date Country Kind
0107708.8 Mar 2001 GB national
Parent Case Info

This application is a divisional of, and claims priority under 35 U.S.C. §120 to, U.S. application Ser. No. 10/675,855, filed on Sep. 25, 2003, which was a Continuation of and claims benefit to, International Application No. PCT/GB02/00844, filed Feb. 27, 2002, the entire disclosures of which are expressly incorporated herein by reference.

US Referenced Citations (143)
Number Name Date Kind
2632440 Hauser Mar 1953 A
2877033 Koetke Mar 1959 A
3242922 Thomas Mar 1966 A
3648294 Shahrestani Mar 1972 A
3681786 Lynch Aug 1972 A
3779654 Horne Dec 1973 A
3875594 Swanson Apr 1975 A
3902482 Taylor Sep 1975 A
3976061 Volkov Aug 1976 A
3985127 Volkov Oct 1976 A
3988783 Treace Nov 1976 A
4187841 Knutson Feb 1980 A
4246660 Wevers Jan 1981 A
4308863 Fischer Jan 1982 A
4353361 Foster Oct 1982 A
4488542 Helland Dec 1984 A
4501266 McDaniel Feb 1985 A
4570625 Harris Feb 1986 A
4576158 Boland Mar 1986 A
4621627 DeBastiani et al. Nov 1986 A
4628922 Dewar Dec 1986 A
4637382 Walker Jan 1987 A
4696293 Ciullo Sep 1987 A
4759765 Van Kampen Jul 1988 A
4776851 Bruchman et al. Oct 1988 A
4846842 Connolly et al. Jul 1989 A
4871367 Christensen et al. Oct 1989 A
4883486 Kapadia et al. Nov 1989 A
4919119 Jonsson et al. Apr 1990 A
4923471 Morgan May 1990 A
4942875 Hlavacek et al. Jul 1990 A
4947835 Hepburn et al. Aug 1990 A
4988349 Pennig Jan 1991 A
5002574 May et al. Mar 1991 A
5011497 Persson et al. Apr 1991 A
5019077 De Bastiani et al. May 1991 A
5026372 Sturtzkopf et al. Jun 1991 A
5041112 Mingozzi et al. Aug 1991 A
5092867 Harms et al. Mar 1992 A
5100403 Hotchkiss et al. Mar 1992 A
5103811 Crupi Apr 1992 A
5121742 Engen Jun 1992 A
5122140 Asche et al. Jun 1992 A
5152280 Danieli Oct 1992 A
5207676 Canadell et al. May 1993 A
5352190 Fischer Oct 1994 A
5352224 Westermann Oct 1994 A
5375823 Navas Dec 1994 A
5405347 Lee et al. Apr 1995 A
5415661 Holmes May 1995 A
5456733 Hamilton, Jr. Oct 1995 A
5540688 Navas Jul 1996 A
5575819 Amis Nov 1996 A
5578038 Slocum Nov 1996 A
5624440 Huebner Apr 1997 A
5662648 Faccioli et al. Sep 1997 A
5662650 Bailey et al. Sep 1997 A
5681313 Diez Oct 1997 A
5695496 Orsak et al. Dec 1997 A
5733284 Martin Mar 1998 A
5803924 Oni et al. Sep 1998 A
5873843 Draper Feb 1999 A
5928234 Manspeizer Jul 1999 A
5944719 Leban Aug 1999 A
5976125 Graham Nov 1999 A
5976136 Bailey et al. Nov 1999 A
6036691 Richardson Mar 2000 A
6113637 Gill et al. Sep 2000 A
6162223 Orsak et al. Dec 2000 A
6176860 Howard Jan 2001 B1
6193225 Watanabe Feb 2001 B1
6203548 Helland Mar 2001 B1
6248106 Ferree Jun 2001 B1
6264696 Reigner et al. Jul 2001 B1
6273914 Papas Aug 2001 B1
6277124 Haag Aug 2001 B1
6355037 Crosslin et al. Mar 2002 B1
6409729 Martinelli et al. Jun 2002 B1
6482232 Boucher et al. Nov 2002 B1
6494914 Brown et al. Dec 2002 B2
6527733 Ceriani et al. Mar 2003 B1
6540708 Manspeizer Apr 2003 B1
6572653 Simonson Jun 2003 B1
6626909 Chin Sep 2003 B2
6663631 Kuntz Dec 2003 B2
6692495 Zacouto Feb 2004 B1
6752831 Sybert et al. Jun 2004 B2
6966910 Ritland Nov 2005 B2
6972020 Grayson et al. Dec 2005 B1
7029475 Panjabi Apr 2006 B2
7141073 May et al. Nov 2006 B2
7188626 Foley et al. Mar 2007 B2
7201728 Sterling Apr 2007 B2
7235102 Ferree et al. Jun 2007 B2
7241298 Nemec et al. Jul 2007 B2
7252670 Morrison et al. Aug 2007 B2
7261739 Ralph et al. Aug 2007 B2
7282052 Mullaney Oct 2007 B2
7282065 Kirschman Oct 2007 B2
7291150 Graf Nov 2007 B2
7306605 Ross Dec 2007 B2
7361196 Fallin Apr 2008 B2
7608074 Austin Oct 2009 B2
20010020143 Stark et al. Sep 2001 A1
20020029039 Zucherman et al. Mar 2002 A1
20020095154 Atkinson et al. Jul 2002 A1
20020107524 Magana Aug 2002 A1
20020120270 Trieu et al. Aug 2002 A1
20020133155 Ferree Sep 2002 A1
20020151978 Zacouto et al. Oct 2002 A1
20030216809 Ferguson Nov 2003 A1
20030220643 Ferree Nov 2003 A1
20040002708 Ritland Jan 2004 A1
20040138659 Austin et al. Jul 2004 A1
20040260302 Manspeizer Dec 2004 A1
20040267179 Lerman Dec 2004 A1
20050049708 Atkinson et al. Mar 2005 A1
20050085754 Werding Apr 2005 A1
20050085815 Harms et al. Apr 2005 A1
20050119744 Buskirk et al. Jun 2005 A1
20050154390 Biedermann et al. Jul 2005 A1
20050192674 Ferree Sep 2005 A1
20050261680 Draper Nov 2005 A1
20060064169 Ferree Mar 2006 A1
20060155279 Ogilvie Jul 2006 A1
20060178744 de Villiers et al. Aug 2006 A1
20070043354 Koo Feb 2007 A1
20070043356 Timm et al. Feb 2007 A1
20070106299 Manspeizer May 2007 A1
20070161993 Lowery et al. Jul 2007 A1
20070168033 Kim et al. Jul 2007 A1
20070168036 Ainsworth et al. Jul 2007 A1
20070198088 Biedermann et al. Aug 2007 A1
20070198091 Boyer et al. Aug 2007 A1
20070244483 Winslow et al. Oct 2007 A9
20070244488 Metzger et al. Oct 2007 A1
20070288014 Shadduck et al. Dec 2007 A1
20080015593 Pfefferle et al. Jan 2008 A1
20080071373 Molz et al. Mar 2008 A1
20080071375 Carver et al. Mar 2008 A1
20080097434 Moumene et al. Apr 2008 A1
20080097441 Hayes et al. Apr 2008 A1
20080275571 Clifford et al. Nov 2008 A1
Foreign Referenced Citations (51)
Number Date Country
1205602 Jun 1986 CA
19855254 Jun 2000 DE
0383419 Aug 1990 EP
0953317 Apr 1999 EP
1770302 Apr 2007 EP
1005290 Feb 2008 EP
1468655 May 2008 EP
1507953 Apr 1978 GB
2223406 Apr 1990 GB
2250919 Oct 1993 GB
59-131348 Jul 1984 JP
7-100159 Apr 1995 JP
2532346 Apr 1995 JP
2000-503865 Apr 2000 JP
2001-145647 Apr 2000 JP
2003-102744 May 2001 JP
2006-280951 Oct 2006 JP
2007-167318 Jul 2007 JP
2007-167319 Jul 2007 JP
2007-170969 Jul 2007 JP
1186204 Oct 1985 RU
1251889 Aug 1986 RU
1588404 Aug 1990 RU
2085148 Jul 1994 RU
2217105 Nov 2003 RU
2241400 Sep 2004 RU
578063 Nov 1977 SU
578957 Nov 1977 SU
624613 Aug 1978 SU
640740 Jan 1979 SU
704605 Dec 1979 SU
719612 Mar 1980 SU
741872 Jul 1980 SU
1316666 Jun 1987 SU
1699441 Dec 1991 SU
1769868 Oct 1992 SU
WO9107137 May 1991 WO
WO9406364 Mar 1994 WO
WO9619944 Jul 1996 WO
WO2004019831 Mar 2004 WO
WO2004024037 Mar 2004 WO
WO2007056645 May 2005 WO
WO2006045091 Apr 2006 WO
WO2006049993 May 2006 WO
WO2006110578 Oct 2006 WO
WO2007090009 Aug 2007 WO
WO2007090015 Aug 2007 WO
WO2007090017 Aug 2007 WO
WO2007114769 Oct 2007 WO
WO2007117571 Oct 2007 WO
WO2008006098 Jan 2008 WO
Non-Patent Literature Citations (28)
Entry
Yamamoto, Ei et al.; “Effects of Stress Shielding on the Transverse Mechanical Properties of Rabbit Patellar Tendons”; Journal of Biomechanical Engineering, 2000, vol. 122, pp. 608-614.
Tomita, Naohide, “Development of Treatment Devices for Cartilage Regeneration”, BME vol. 16, No. 2.
Lentsner, A.A., et al., “Device for Functional Relief of Hip Joint in Cotyloid Cavity Fracture Cases”, Ortop Travmatol Protez. Apr. 1990 (4) 44-6.
Nagai, et al., “B109 Mobility Evaluation of Hip-Joint Nonweight-Bearing Device”, The Japan Society of Mechanical Engineers No. 02-26.
Lapinskaya, V.S., et al., “An Endoapparatus for Restoration of the Hip Joint”, Writers Collective, 2008, UDK 615.472.03:616,728.2-089.28.
Wilkins, Ross M., M.D. et al.; “The Phenix Expandable Prosthesis”; Clinical Orthopaedics and Related Research, No. 382, pp. 51-58.
Weisstein, Jason S., M.D. et al.; “Oncologic Approaches to Pediatric Limb Preservation”; Journal of the American Academy of Orthopaedic Surgeons; vol. 13, No. 8, Dec. 2005.
Uchikura, C. et al.; “Comparative study of nonbridging and bridging external fixators for unstable distal radius fractures”; Journal of Orthopaedic Science, 2004, vol. 9, pp. 560-565.
Sommerkamp, G. et al.; “Dynamic external fixation of unstable reatures of the distal part of the radius”; The Journal of Bone and Joint Surgery; 1994, vol. 76-A, No. 8, pp. 1149-1161.
Madey, S. et al; Hinged external fixation of the elbow: optimal axis alignment to minimize motion resistance; Journal of Orthopaedic Trauma, 2000, vol. 14, No. 1, pp. 41-47.
Neel, Michael D., M.D.; “Repiphysis—Limb Salvage System for the Skeletally Immature”; Wright Medical Techology, Repiphysis Limb Salvage System, 2001, pp. 1-8.
Neel, Michael D. M.D. et al.; “Early Multicenter Experience With a Noninvasive Expandable Prosthesis”; Clinical Orthopaedics and Related Research, 2003, No. 415, pp. 72-81.
Nockels, Russ P.; “Dynamic Stabilization in the Surgical Management of Painful Lumbar Spinal Disorders”; Spine, 2005, vol. 30, No. 16S, pp. S68-S72.
ORTHOFIX; “Xcaliber Articulated Ankle”; advertising brochure, May 2004.
ORTHOFIX; “Gentle Limb Deformity Correction”, website pages, http://www.eight-plate.com/, 2008.
Perry, Clayton R. et al.; “Patellar Fixation Protected with a Load-Sharing Cable: A Mechanical and Clinical Study”: Journal of Orthopaedic Trauma, 1988, vol. 2, No. 3, pp. 234-240.
Pollo, Fabian E. et al.; “Reduction of Medical Compartment Loads With Valgus Bracing of the Osteoarthritic Knee”; American Journal Sports Medicine, vol. 30, No. 3, 2002; pp. 414-421.
Aldegheri, Roberto, M.D. et al.; “Articulated Distraction of the Hip—Conservative Surgery for Arthritis in Young Patients”, Clinical Orthopaedics and Related Research, No. 301, pp. 94-101.
Benzel, Edward; “Qualititive Attributes of Spinal Implants”; in: Biomechanics of Spine Stabilization, 1995.
Buckwalter, Joseph A,: “Joint distraction for osteoarthritis”; The Lancet, Department of Orthopaedic Surgery, University of Iowa Hospitals and Clinics, vol. 347, Feb. 3, 1996, pp. 279-280.
Deie, Masataka, M.D. et al.; “A new Articulated Distraction Arthrosplasty Device for Treatment of the Osteoarthritic Knee Joint: A Preliminary Report”; Arthroscopy: The Journal of Arthoscopic and Related Surgery; vol. 23, No. 8 Aug. 2007: pp. 833-838.
Dienst, M. et al.; “Dynamic external fixation for distal radius fractures”; Clinical Orthopaedics and Related Research, 1997, vol. 338, pp. 160-171.
Hall, J. et al.; “Use of a hinged external fixator for elbow instability after severe distal humeral fracture”; Journal of Orthopaedic Trauma, 2000, vol. 14, No. 6 pp. 442-448.
Klein, D. et al.; “Percutaneous treatment of carpal, metacarpal, and phalangeal injuries”; Clinical Orthopaedics and Related Research, 200, vol. 375, pp. 116-125.
Krakauer, J. et al.; “Hinged device for fractures involving the proximal interphalangeal joint”; Clinical Orthopaedics and Related Research, 1996, vol. 327, pp. 29-37.
Lafeber et al., Unloading Joints to Treat Osteoarthritis, Including Joint Distraction, Current Opinion in Rheumatology 2006, 18; 519-525.
European Search Report for European Patent App. No. 08169426.7 (Jul. 22, 2014).
Office Action from co-pending U.S. Appl. No. 12/628,866 dated May 9, 2014.
Related Publications (1)
Number Date Country
20090248026 A1 Oct 2009 US
Divisions (1)
Number Date Country
Parent 10675855 Sep 2003 US
Child 12425969 US
Continuations (1)
Number Date Country
Parent PCT/GB02/00844 Feb 2002 US
Child 10675855 US