U.S. patent application number 13/467931 was filed with the patent office on 2012-08-30 for bone fixated, articulated joint load control device.
This patent application is currently assigned to MOXIMED, INC.. Invention is credited to Edward Draper.
Application Number | 20120221121 13/467931 |
Document ID | / |
Family ID | 9911714 |
Filed Date | 2012-08-30 |
United States Patent
Application |
20120221121 |
Kind Code |
A1 |
Draper; Edward |
August 30, 2012 |
BONE FIXATED, ARTICULATED JOINT LOAD CONTROL DEVICE
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.
Inventors: |
Draper; Edward;
(Buckinghamshire, GB) |
Assignee: |
MOXIMED, INC.
Hayward
CA
|
Family ID: |
9911714 |
Appl. No.: |
13/467931 |
Filed: |
May 9, 2012 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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12628866 |
Dec 1, 2009 |
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13467931 |
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12425969 |
Apr 17, 2009 |
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12628866 |
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10675855 |
Sep 25, 2003 |
7763020 |
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12425969 |
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Current U.S.
Class: |
623/46 ;
623/13.11 |
Current CPC
Class: |
A61B 2017/606 20130101;
A61B 17/6416 20130101; A61B 17/6425 20130101; A61B 17/6441
20130101 |
Class at
Publication: |
623/46 ;
623/13.11 |
International
Class: |
A61F 2/64 20060101
A61F002/64; A61F 2/08 20060101 A61F002/08 |
Foreign Application Data
Date |
Code |
Application Number |
Mar 28, 2001 |
GB |
0107708.8 |
Feb 27, 2002 |
GB |
PCT/GB02/00844 |
Claims
1. A device for controlling load on a knee joint, the device
comprising: first and second fixation assemblies configured for
attachment to a side of a knee joint; a link assembly connectable
to the first and second fixation assemblies at first and second
pivots respectively, wherein the link assembly is configured to
provide a variable distance of separation of the first and second
pivots; wherein the link assembly comprises a spring; and wherein
the spring is arranged in the link assembly to bias the first and
second pivots away from one another.
2. The device of claim 1, wherein the first and second pivots
comprise articulating surfaces.
3. The device of claim 1, wherein the link assembly is configured
to be positioned entirely outside of the articular surfaces of the
knee joint.
4. The device of claim 1, further comprising a first fastener
configured to extend through the first fixation assembly and into
the femur; and a second fastener configured to extend through the
second fixation assembly and into the tibia.
5. The device of claim 1, wherein the spring comprises a coil
spring.
6. The device of claim 1, wherein the link assembly is configured
to act in compression to counteract the natural compressive forces
experienced by the knee joint.
7. The device of claim 1, wherein the link assembly comprises means
to apply a force in a direction of distraction of the knee
joint.
8. The device of claim 1, wherein the link assembly comprises a
central shaft.
9. The device of claim 8, wherein the link assembly comprises a hub
mounted to the central shaft and configured to contact an end of
the spring.
10. The device of claim 8, wherein the central shaft extends
through the spring.
11. A device for controlling load on a joint, the device
comprising: first and second fixation assemblies configured for
attachment to a side of a joint; a link assembly connectable to the
first and second fixation assemblies at first and second pivots
respectively, wherein the link assembly is configured to provide a
variable distance of separation of the first and second pivots;
wherein the link assembly comprises a spring; and wherein the
spring is arranged in the link assembly to bias the first and
second pivots away from one another.
12. The device of claim 11, wherein the first and second pivots
comprise articulating surfaces.
13. The device of claim 11, wherein the link assembly is configured
to be positioned entirely outside of the articular surfaces of the
joint.
14. The device of claim 11, further comprising a first fastener
configured to extend through the first fixation assembly and into a
first bone of the joint; and a second fastener configured to extend
through the second fixation assembly and into a second bone of the
joint.
15. The device of claim 11, wherein the spring comprises a coil
spring.
16. The device of claim 11, wherein the link assembly is configured
to act in compression to counteract the natural compressive forces
normally experienced by the joint.
17. The device of claim 11, wherein the link assembly comprises
means to apply a force in a direction of distraction of the
joint.
18. The device of claim 11, wherein the link assembly comprises a
central shaft.
19. The device of claim 18, wherein the link assembly comprises a
hub mounted to the central shaft and configured to contact an end
of the spring.
20. The device of claim 18, wherein the central shaft extends
through the spring.
21. A device for controlling load on a joint, the device
comprising: first and second fixation assemblies configured for
attachment to a side of a joint; a link assembly connectable to the
first and second fixation assemblies at first and second pivot
means respectively, wherein the link assembly is configured to
provide a variable distance of separation of the first and second
pivot means; wherein the link assembly comprises a means for
biasing; and wherein the means for biasing is arranged in the link
assembly to bias the first and second pivot means away from one
another.
22. The device of claim 21, wherein the first and second pivot
means comprise articulating surfaces.
23. The device of claim 21, wherein the link assembly is configured
to be positioned entirely outside of the articular surfaces of the
joint.
24. The device of claim 21, further comprising a first fastener
means configured to extend through the first fixation assembly and
into the femur; and a second fastener means configured to extend
through the second fixation assembly and into the tibia.
25. The device of claim 21, wherein the means for biasing comprises
a coil spring.
26. The device of claim 21, wherein the link assembly is configured
to act in compression to counteract the natural compressive forces
experienced by the joint.
27. The device of claim 21, wherein the link assembly comprises
means to apply a force in a direction of distraction of the
joint.
28. The device of claim 21, wherein the link assembly comprises a
central shaft.
29. The device of claim 28, wherein the link assembly comprises a
hub mounted to the central shaft and configured to contact an end
of the means for biasing.
30. The device of claim 28, wherein the central shaft extends
through the means for biasing.
Description
CROSS REFERENCE TO RELATED APPLICATIONS
[0001] This application is a continuation of U.S. Ser. No.
12/628,866, filed Dec. 1, 2009, which is a continuation of U.S.
Ser. No. 12,425,969, filed on Apr. 17, 2009, which is a divisional
of 10/675,855, filed on Sep. 25, 2003, now U.S. Pat. No. 7,763,020
and claims benefit to International Application No. PCT/GB02/00844,
filed Feb. 27, 2002 the entire disclosure of which is expressly
incorporated herein by reference.
BACKGROUND
[0002] The present invention relates to devices for restricting or
controlling the movement or loading levels on joints in the human
or animal body.
[0003] 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.
[0004] 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.
[0005] 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".
[0006] 1. Under-Loading Zone.
[0007] If a joint surface remains unloaded for appreciable periods
of time the cartilage tends to soften and weaken.
[0008] 2. Healthy Zone.
[0009] Joint surfaces can and do last a lifetime and if they
experience healthy levels of load they can be considered to
effectively last indefinitely.
[0010] 3. Tolerant Zone.
[0011] 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.
[0012] 4. Overloaded Zone.
[0013] 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.
[0014] 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.
[0015] 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.
[0016] Newly implanted grafts or tissue-engineered constructs will
also have lower tolerance limits while they are establishing
themselves within the joint.
[0017] 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.
[0018] 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.
[0019] 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.
[0020] 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.
[0021] In the prior art, existing load controlling regimes and
devices for use in treatment or therapy of articulating joints
include the following. [0022] 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. [0023] 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. [0024] 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. [0025] 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.
[0026] According to one aspect, the present invention provides an
apparatus for controlling the load on articular cartilage of a
human or animal joint comprising: [0027] a first fixation assembly
for attachment to a first bone; [0028] a second fixation assembly
for attachment to a second bone; and [0029] a link assembly coupled
to the first fixation assembly by a first pivot and coupled to the
second fixation assembly by a second pivot, [0030] the first and
second fixation assembly thereby each being angularly displaceable
relative to the link assembly.
[0031] According to another aspect, the present invention provides
a method of controlling loading on a joint comprising the steps of:
[0032] attaching a first fixation assembly to a first bone; [0033]
attaching a second fixation assembly to a second bone, the second
bone being connected to the second bone by an articulating joint;
[0034] 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
[0035] FIG. 1 shows a perspective view of a fixator for controlling
loads on articular cartilage according to a preferred embodiment of
the present invention;
[0036] FIG. 2 shows a perspective view of a pair of fixators of
FIG. 2 in a dual sided or bilateral configuration;
[0037] FIG. 3 shows perspective views of a selection of central
modules suitable for use with the fixators of FIGS. 1 and 2;
[0038] FIG. 4 shows a perspective view of an externally powered
fixator;
[0039] FIG. 5 shows perspective views of a selection of alternative
fixation assemblies suitable for use in the fixators of FIGS. 1 and
2;
[0040] 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
[0041] FIG. 7 shows a parallel-crosswise configuration of link
assembly.
DETAILED DESCRIPTION
[0042] 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.
[0043] 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.
[0044] 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.
[0045] 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.
[0046] 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.
[0047] 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.
[0048] 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.
[0049] 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.
[0050] Referring now to FIG. 3, various arrangements of link
assemblies and their respective functions will now be
described.
[0051] 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.
[0052] 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.
[0053] 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.
[0054] 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.
[0055] 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.
[0056] Although not shown in FIGS. 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.
[0057] 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.
[0058] It will be understood that the functions of the pneumatic or
hydraulic cylinder 81 could be alternatively provided by an
electrically driven system.
[0059] In another arrangement, labelled 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.degree. of angular displacement.
[0060] 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.
[0061] In another arrangement, the cam surfaces 76, 77 could be
adapted to limit the angular displacement of that fixation
assembly.
[0062] 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.
[0063] 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.
[0064] 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.
[0065] Separate transducers could be added to monitor angular
displacement of the fixation assemblies relative to the link
assembly 90.
[0066] 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.
[0067] 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.
[0068] 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 111b, 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.
[0069] 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.
[0070] 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.
[0071] 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.
[0072] 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.
[0073] 1. Continuous Traction.
[0074] 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.
[0075] 2. Partial or Full Support.
[0076] 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.
[0077] 3. Application of a Bending Moment, Torsion or Shear
Force.
[0078] Application of these loads to the joint allows the clinician
to move the centre of pressure within the joint to regions that are
healthy.
[0079] 4. Application of an Externally Powered Loading Regime.
[0080] 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.
[0081] 5. Allowing the Joint Load to be Gradually Increased.
[0082] 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.
[0083] 6. Load Measurement.
[0084] 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.
[0085] 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.
[0086] 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.
[0087] 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.
[0088] Other embodiments are within the scope of the appended
claims.
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