U.S. patent number 3,909,854 [Application Number 05/524,708] was granted by the patent office on 1975-10-07 for knee implant prosthesis.
Invention is credited to Ysidore M. Martinez.
United States Patent |
3,909,854 |
Martinez |
October 7, 1975 |
Knee implant prosthesis
Abstract
A knee prosthesis for replacing the functions of the natural
knee including the ability of the natural knee to rotate,
abduct-adduct and flex. The device incorporates spaced pivot
bearings mounted in a pivot body. The pivoting structure is
connected to the natural bone structure by a connector screw
received in the bone, and a connector shield received in a cavity
surgically prepared in the bone. Resilient plastic material
provides a resistance restoring force for the abduction-adduction
and rotation modes.
Inventors: |
Martinez; Ysidore M. (La Mesa,
CA) |
Family
ID: |
26999383 |
Appl.
No.: |
05/524,708 |
Filed: |
November 18, 1974 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
Issue Date |
|
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356816 |
May 3, 1973 |
3848276 |
Nov 19, 1974 |
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Current U.S.
Class: |
623/20.26 |
Current CPC
Class: |
A61F
2/384 (20130101); A61F 2002/30624 (20130101) |
Current International
Class: |
A61F
2/38 (20060101); A61F 2/30 (20060101); A61F
001/24 () |
Field of
Search: |
;3/1,1.9-1.911,22
;128/92C |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Frinks; Ronald L.
Attorney, Agent or Firm: Brown & Martin
Parent Case Text
RELATION TO OTHER APPLICATIONS
This application is a continuation-in-part of patent application,
Ser. No. 356,816, filed May 3, 1973 and issued as U.S. Pat. No.
3,848,276 on Nov. 19, 1974.
Claims
Having described my invention, I now claim:
1. A knee prosthesis comprising joint means for controlled flexion,
rotation, and abduction-adduction movements:
attachment means for securing said joint means between relatively
movable skeletal members,
said joint means comprising two relatively spaced apart flexure
pivot bearings journaled in a common pivot body and upper and lower
pivot roller elements carried by said flexure pivot bearings,
said pivot body and said pivot roller elements having cooperating
arcuate surfaces in relatively sliding engaging relationship,
each of said attachments means being secured to each of said pivot
rollers for a limited relative rotation about an
abduction-adduction axis and a rotation axis, which axes are
mutually orthogonal with the axis of said pivot bearing.
2. The knee prosthesis according to claim 1, further including:
first resilient means for exerting a restoring force against
relative displacement of said attachment means and said pivot
roller element toward misallignment in said abduction-adduction
axis.
3. The knee prosthesis according to claim 2, wherein:
said first resilient means comprises a resilient pad between said
attachment means and said pivot roller element.
4. The knee prosthesis according to claim 1, wherein:
said attachment means is secured to said pivot roller element by an
axial rotation post,
said axial rotation post being pinned by a connector assembly pin
into a recess in said attachment means,
said rotation post having a transverse bore with an asymmetrical
cross-section,
said pivot bearing comprising a pivot pin received through said
transverse bore.
5. The knee prosthesis according to claim 4, further including:
an axial bore extending beyond said transverse bore,
a quantity of resilient material in said bore bearing against pivot
pin.
6. The knee prosthesis according to claim 1, wherein:
said pivot roller element and said pivot body having cooperating
stop members for limiting the maximum arc of relative rotation
between said pivot roller element and said pivot body.
7. The knee prosthesis according to claim 1, further including:
a connector shield secured to said attachment means,
said connector shield having at least one enlargement forming an
interlock for interlocking said connector shield into bone
structure.
8. The knee prosthesis according to claim 7, wherein:
said connector shield includes a depending portion which overlies
and substantially surrounds the frontal and side portions of said
pivot body in the aligned orientation of said pivot roller
elements.
9. The knee prosthesis according to claim 8, wherein:
the lower terminal edges of said depending portion of said
connector shield are in contact in the aligned orientation.
10. The knee prosthesis according to claim 1, wherein:
said attachment means comprises elongated connector screws.
11. The knee prosthesis according to claim 1, wherein:
said attachment means is secured to said pivot roller element
through a connector assembly pin received in a transverse bore in
said attachments means,
said connector assembly pin comprising an elongated pin,
locking means for holding said connector assembly pin within said
transverse bore.
12. The knee prosthesis according to claim 11, wherein:
said locking means comprises at least one transverse recess in the
surface of said connector assembly pin and cooperating biased lock
pawl positioned in said attachment means for engaging said recess
when said connector assembly pin is fully inserted in said
transverse bore.
13. The knee prosthesis according to claim 12, wherein:
said lock pawl is substantially cylindrical.
14. The knee prosthesis according to claim 12, wherein:
said lock pawl is biased by resilient plastic material.
Description
BACKGROUND OF THE INVENTION
Prior art knee implant prosthesis devices have generally not
provided for a natural knee action or have utilized unduly complex
structures to obtain the complex motion that is accomplished by a
natural knee. Further deficiencies of such prior art devices
included their inability to provide for materials and structures
that are compatible with bodily tissues and fluids and which
therefore promote infection and other side effects after
implantation. Such devices have typically not been of sufficient
strength to permit the user to walk normally or to engage in the
other activities that produce substantial stress on the knee joint.
Prior art devices have typically been of such a size that an
excessive amount of bone and surrounding tissue must be removed for
implantation. The trauma from such excessive bone removal can lead
to complications in the operation or to an unsuccessful adaptation
to the prosthesis.
The structures utilized by the prior art are covered in more detail
in the co-pending application identified herein. The background of
the invention is such application as well as the specification
therein are hereby incorporated by reference. One approach to the
problem of body tissue and body fluid contamination and infection
by the knee prosthesis is set forth in this co-pending application.
In this configuration, the knee prosthesis is encapsulated to
prevent the entrance of body tissues and fluids to the joint. Such
a configuration avoids contamination and entrapment of body tissues
during knee flexion, however, encapsulation adds to the overall
size of the device and increases the complexity of its
installation.
It is therefore desirable to have a knee implant prosthesis that
closely duplicates the motions obtainable in a natural knee
especially where such a device may be implanted with a minimum of
disturbance to tissues and bone structure, and wherein the device
will not contaminate the body tissues and fluids nor entrap body
tissues during knee flexion.
SUMMARY OF THE INVENTION
An exemplary embodiment of the invention incorporates a pivot
structure having a relatively large pivot center spacing between
dual pivot bearings but which has a small overall size, so that a
full 135.degree. of knee flexion may be obtained without entrapment
of body tissues. The main flexure pivots are trapped for rotation
against a surface of the pivot body to which they are rotatably
secured thereby increasing the rigidity and stability of the
prosthesis in flexure. The pivot body also cooperates with the
pivot roller elements to form stops in the straight leg and fully
flexed positions.
The attachment means for connecting the pivoting structure to the
natural bone structure includes a connector screw and a connector
shield. The connector screw is self-tapping in the soft central
bone is locked in place by the connector shield. The connector
shield is received in a cavity surgically prepared in the bone to
have a locking undercut. The undercut cooperates with an enlarged
portion on the connector shield to lock the connector shield and
connector screw in position. Adhesives may also be employed to
further secure the attachment means in position.
The movements of the natural knee referred to as rotation and
adduction-abduction are accommodated in the interconnection between
the attachment means and the pivot roller element. The connector
screw and pivot roller element have facing axial bores into which
is received an axial rotation post. The rotation post has
sufficient clearance from the walls of the bore in the connector
screw so that it may rotate about a connector assembly pin. The
connector assembly pin is on a fore and aft transverse axis so that
rotation about the connector assembly pin will be in the
adductionabduction rotational mode. A layer of resilient plastic
material is interposed between the faces of the connector screw and
pivot roller element to accommodate the adduction-abduction
movement and to exert a resilient bias on the joint tending to
restore the joint to its aligned orientation. The inner end of the
rotation post is secured to the roller block element through the
same flexure pivot pin which, in association with the roller block
element, forms the flexure pivot bearing. However, the bore through
the rotation post that receives the flexure pivot pin is enlarged
and asymmetrical. The enlarged opening permits limited relative
rotation about the overall axis of the prosthesis corresponding to
the rotation of the natural knee joint. The asymmetrical
configuration of the hole permitting rotation causes a "screw-in"
action which corresponds to the "screw-in" effect in the natural
knee occuring, for example, during normal walking. Such movement
compresses the resilient plastic material received in an axial bore
in the rotation post. The resilient plastic thereby exerts a
restoring force tending to return the knee to its normal or aligned
rotational position.
The implantation of the device is simplified by a locking mechanism
utilized to secure the connector screw and connector shield to the
pivot structure after the connector screw has been inserted in the
bone. The connector assembly pin includes a pair of transverse
surface recesses near one end. The recesses are positioned to
cooperate with locking pawls in the terminal portion of the
connector screw. The insertion of the pin with a proper rotational
orientation will bias the locking pawls over the surface of the
connector pin. Then, the bias of the pawls will cause the pawls to
be forced into the surface recesses, locking and holding the pin,
connector shield, connector screw, and rotation post in assembled
relations. For removal, the pin is first rotated 90.degree. to bias
the locking pins out of the recesses and then the pin may be
withdrawn.
It is therefore an object of the invention to provide a new and
improved knee implant prosthesis.
It is another object of the invention to provide a new and improved
knee implant prosthesis that reduces the complexity of surgical
implantation.
It is another object of the invention to provide a new and improved
knee implant prosthesis that requires the removal of a relatively
small amount of bone structure.
It is another object of the invention to provide a new and improved
knee implantt prosthesis that protects against entrapment of body
tissues during knee flexion and other movement.
It is another object of the invention to provide a new and improved
knee implant prosthesis that closely duplicates the movement
capabilities of the natural knee.
It is another object of the invention to provide a new and improved
knee implant prosthesis that has high strength.
It is another object of the invention to provide a new and improved
knee implant prosthesis that eliminates voids that could otherwise
promote body fluid contamination.
It is another object of the invention to provide a new and improved
knee implant prosthesis that provides for a natural movement of the
patella and surrounding tendons.
It is another object of the invention to provide a new and improved
knee implant prosthesis that is inert to body fluids and
tissues.
It is another object of the invention to provide a new and improved
knee implant prosthesis that provides for a high strength
interconnection to the natural bone structure.
It is another object of the invention to provide a new and improved
knee implant prosthesis with a high degree of rotational
stability.
Other objects and many attendant advantages of the invention will
become more apparent upon the reading of the following detailed
description together with the drawings in which like reference
numerals refer to like parts throughout and in which:
FIG. 1 is a side elevational view of the improved knee implant
prosthesis.
FIG. 2 is a rear elevational view of the knee implant
prosthesis.
FIG. 3 is a sectional view taken along line 3--3 of FIG. 1.
FIG. 4 is a sectional view taken along line 4--4 of FIG. 4.
FIG. 5 is a view similar to FIG. 4 showing knee flexure action.
FIG. 6 is a sectional view taken along line 6--6 of FIG. 2.
FIG. 7 is a sectional view taken along line 7--7 of FIG. 2.
FIG. 8 is a sectional view taken along line 8--8 of FIG. 1.
Referring now to the drawings there is illustrated a knee implant
prosthesis 10. The pivot structure 12 includes a pivot body 16
which mounts and supports pivot roller elements 18 through pivot
bearings 20. The pivot bearings 20 comprise pivot pins 22 received
through transverse bores 63 in the pivot body 16 and bores 65
through the pivot roller elements 18. The pins 22 are retained by
spring retainer 84. The upper and lower halfs of the prosthesis are
identical except where noted therefore the prosthesis will be
described in connection with the upper portion thereof.
The pivot body 16 and pivot roller element 18 have cooperating
arcuate surfaces 66 and 68 which, in the preferred embodiment are
lapped to closely conform to one another so that the curved
surfaces supplement and stabilize the action of the pivot bearing
20. It should be noted that it is also within the scope of the
invention to incorporate cylindrical bearing rollers in recesses
along the arcuate surfaces 66 or 68.
An axial rotation post 24 is also carried on the pivot pin 22
through an enlarged transverse bore 23. The post 24 interconnects
the pivot structure 12 with the attachment means 14. Post 24 is
received in an axial bore in the connector screw 26 and is pinned,
together with the connector screw 26, and the connector shield 30,
by a connector assembly pin 28. The pin 28 has a head with a flange
98 and is received in a bore 32 through the frontal portion of the
connector shield 30, and through a transverse bore 34 in the
connector screw 26, and transverse bore 36 through the rotation
post 24.
Assembly of the device during implantation is facilitated by the
lock means 38 for the connector assembly pin 28. The connector
assembly pin 28 has a pair of diametrically opposed transversed
recesses 50 and 52 near its end, which recesses receive biased
locking pawls 40 and 42. The pawls are biased into engagement with
the surface of the connector assembly pin 28 by resilient material
44 and 46. The assembly and disassembly of the structure of the
invention through the use of the connector assembly pin 28 and lock
means 38 will be described more fully hereinafter.
The rotation 24, in addition to providing for the structural
interconnection of the attachment means 14 and pivot structure 12,
provides for relative rotation between the femur and tibia
corresponding to the rotation capability of the natural knee. The
rotation is accommodated on the pivot pin 28 through the mechanism
of an enlargement in the transverse bore 23 in the rotation post
24. The enlargement produces an asymmetrical enlargement on the
outer portion 58 of the transverse bore 23. Thus rotation between
the upper and lower leg members will cause a camming action of the
pivot pin 22 on the inclined walls of the transverse bore 23,
drawing the pivot pin 22 up into the enlarged outer portion 58 of
the bore 23, limiting the total rotation, and causing the
compression of a resilient snubber 56. The snubber 56 is received
in a bore in the rotation post 24 and serves the functions of
cushioning the rotation action and providing a resistence to
rotation for the purpose of introducing "feel" to the user, and for
providing a return bias to the aligned orientation. A clearance
space 64 provides necessary axial movement of the rotation post 24
during the aforedescribed rotation.
Rotation about the axis referred to as the adduction-abduction axis
is accomplished through the provision of a resilient pad 60. Pad 60
is positioned between the connector screw 26 and roller block
element 18. A protruding tab 62 is received in a slot on the roller
block element to hold the pad 60 in position. The combined effect
of the upper and lower pads 60 produces the 8.degree. of total
adduction-abduction (left, right rocking motion) which is a
necessary and normal part of natural knee action.
Both adduction-abduction and rotation are accommodated throughout
the range of flexion since the generally spherical (see FIGS. 4 and
7) upper and lower portions of the pivot body 16 cannot be drawn
into conflict with the generally sphereical cavity formed by the
connector shield.
Referring now specifically to FIG. 5, the configuration of the knee
prosthesis during flexion is illustrated. It will be noted that the
arcuate surfaces of the pivot roller element and pivot body have
moved in a sliding frictional engagement to a rotationally
displaced position. The maximum arc of rotation permitted by the
device is determined by the stops 90 and 92 on the pivot roller
element, which cooperate with the stops 94 and 96 on the pivot body
to limit overall rotation. The lower terminal portions of the
connector shield 30 contact during the straight legged or knee
locked position as an additional stop. The total arc of rotation is
limited to 135.degree. which corresponds to that of the normal knee
and which prevents the entrapment of body tissues between the
pivoting structures.
Referring now to specifically to FIGS. 1 through 3, the
installation of the knee prosthesis 10 according to the invention
is illustrated. The prosthesis is illustrated as being implanted in
a femur 80 and tibia 82. The lower pivot shield is locked into the
tibia 82 by the provision of interlock protrusions 100 and 102
which fit into corresponding cavities surgically provided in the
upper portion of the tibia. A connector screw 26 with a straight
shank 78 is received in the soft central portion of the bone and is
locked against rotation by the relationship of tabs 74 on the
connector shield received in corresponding diametrically opposed
slots on the connector screw 26. The installation of the upper
connector screw 26 and connector shield 30 is similar, with the
exception that the upper connector screw 26 has a canted shank 76
to correspond to the inclination of the femur 80. Further, since
the connector shield 30 is nearly totally retained within the lower
terminate portion of the tibia, the use of interlock protrusions is
not required.
OPERATION
In use, the knee prosthesis 10 according to the invention is
implanted by first cutting into the condyles of the tibia and femur
to create a cavity that closely conforms to the exterior
configuration of the connector shield 30. The connector screws 26
are than screwed into the soft central bone structure until they
are fully inserted as illustrated in FIG. 2. The connector shields
30 are then inserted over the connector screws 26, which has the
effect of locking the screws in rotational position by the action
of the tabs 74. The connector assembly pins 28 perform the dual
functions of securing the connector shield-connector screw
relationship, and securing the combinations of connector screw 26
and connector shield 30 forming the attachment means 14 to the
pivot structure 12. The pins 28 are inserted through the bores 32
in the connector shield 30, the transverse bores 34 in the
connector screws and the transverse bores 36 in the rotation posts
24. When the pin 28 encounters the lock means 38 in the form of the
biased pawls 40 and 42 additional pressure will force the pawls
against the bias of the resilient material 44 and 46 and cam the
pawls over the surface of the pin 28 and into the recesses 50 and
52. The rotational orientation of the connector pin is maintained
with the flange 73 in a vertical orientation to align the recesses
50 and 52 with the pawls 40 and 42.
After implantation and convalescense, the patient is able to
utilize the full rnage of normal knee movements without undesirable
affects. The pivot body provides for sufficient spacing between the
pivot axes about the pivot pins 60 so that at the maximum arc of
rotation of 135.degree. there is no pinching of tissue between the
upper and lower portions of the device. At the same time, the use
of the interconnection structure in the form of the rotation post
being received in a female recess in the connector screw minimizes
the overall size of the device so that the strength and resiliency
of the device itself is enhanced by the natural support given by
tendons and muscles. The front face 70 of the connector shield on
the tibia corresponds generally to the surface of the bone
structure removed and thus the connector shield forms a patellar
slide retaining the desirable patellar functions. The smooth
surfaces 70 of the connector shields 30 also serve to provide a
surface on which the tendons may move during flexion of the
knee.
In normal activity such as in walking, which exercises all of the
movements of which a natural knee is capable, the
abduction-adduction, and rotation capabilities of a joint are
utilized. The use of resilient plastic material such as silastic
for the snubber pad and insert 56 and 60 provides a desirable
resistence to movement to give the user a feel for leg position and
also biases the knee joint back to its nominal orientation after
displacement. Plastic resilient material is found to be
advantageous over other resilient means in that it fills voids as
well as providing the resilient effect and thereby avoids excessive
entrapment of body fluids. The joint is designed to provide
sufficient strength without creating concentrated areas of stress
so that the device may be constructed of pyrolytic carbon, silicon
nitride or boron nitride, which materials have the desirable
properties of inertness to the body system, while having high
strength. These materials have a tendency toward brittleness and
could not be employed, where it not for the stress design and
configuration of the device, and the use of snubbers to reduce
impact stresses.
If it should ever become necessary to remove the implanted
prosthesis or to replace it, after the device has been surgically
exposed, the connector assembly pins are merely rotated 90.degree..
The rotation cams the locked pawls 40 and 42 onto the smooth outer
surface of the pin and permits the pin to be withdrawn. The
separate parts can then be disassembled.
* * * * *