U.S. patent number 3,744,061 [Application Number 05/179,912] was granted by the patent office on 1973-07-10 for artificial hip joint and method of implanting in a patient.
Invention is credited to Harold M. Frost.
United States Patent |
3,744,061 |
Frost |
July 10, 1973 |
ARTIFICIAL HIP JOINT AND METHOD OF IMPLANTING IN A PATIENT
Abstract
An artificial hip joint having a cup-shaped acetabular component
and a femoral component carrying a ball in which the acetabular
component when inserted into the acetabulum of a patient shifts
about a controlled axis of rotation. The ball of the femoral
component fits within the socket of the acetabular component and
makes rolling contact with the socket wall spaced from the axis of
rotation of the acetabular component during walking movement of the
femur.
Inventors: |
Frost; Harold M. (Bloomfield
Hills, MI) |
Family
ID: |
22658491 |
Appl.
No.: |
05/179,912 |
Filed: |
September 13, 1971 |
Current U.S.
Class: |
623/22.11 |
Current CPC
Class: |
A61F
2/32 (20130101); A61F 2/3676 (20130101); A61F
2002/3414 (20130101); A61F 2002/3631 (20130101); A61F
2/367 (20130101); A61F 2002/30937 (20130101); A61F
2310/00029 (20130101); A61F 2/36 (20130101); A61F
2002/3446 (20130101); A61F 2230/0034 (20130101); A61F
2/3662 (20130101); A61F 2002/3429 (20130101); A61F
2002/3066 (20130101); A61F 2002/30187 (20130101); A61F
2002/3495 (20130101); A61F 2002/30639 (20130101); A61F
2002/368 (20130101); A61F 2002/3611 (20130101); A61F
2002/30785 (20130101); A61F 2002/30878 (20130101) |
Current International
Class: |
A61F
2/32 (20060101); A61F 2/00 (20060101); A61F
2/30 (20060101); A61F 2/34 (20060101); A61F
2/36 (20060101); A61f 001/24 () |
Field of
Search: |
;3/1
;128/92C,92CA,92R,92F |
References Cited
[Referenced By]
U.S. Patent Documents
Other References
"Arthroplasty of the Hip Using Foreign Materials: A History" by J.
T. Scales, Proceedings The Instution of Mechanical Engineers, Vol.
181, Part 3J, 1966-1967, pages 72 and 80-81 relied upon. .
"Teflon Hip Prostheses in Dogs" by J. D. Leidholt et al., Journal
of Bone & Joint Surgery, Vol. 47-A, No. 7, pp. 1414-1420, Oct.
1965. .
Richards Manufacturing Co. (catalog), Memphis, Tenn., 1966,
Smith-Peterson Smo Hip Cups, page 147. .
Richards Bechtol Femoral Prosthesis, (Advertisement), Richards
Manufacturing Co., Memphis, Tenn., Received Aug. 24, 1966..
|
Primary Examiner: Gaudet; Richard A.
Assistant Examiner: Frinks; Ronald L.
Claims
What I claim is: What I claim is:
1. An artificial hip joint comprising a cup adapted to be inserted
into the pelvis and a ball having means adapted to be secured to
the femur, said cup having an axis of rotation and an inner
substantially spherical surface which defines a socket symmetrical
about said axis and an outer surface of revolution formed
symmetrically about said axis, said cup outer surface define means
for guiding shiftable movement of said cup about its axis of
rotation when inserted within said pelvis, said ball including a
substantially spherical surface having a radius which is less than
the radius of said cup inner surface, said ball fitting within said
socket and contacting said cup inner surface at locations spaced
from the axis of rotation of said cup in all positions of said ball
during normal fore and aft walking movement of said femur, whereby
said movement of the femur causes rolling movement of said ball
relative to said cup and correlative shiftable movement of said cup
about its axis of rotation.
2. The hip joint of claim 1 wherein said cup includes an annular
outturned lip defining a circular ball-receiving opening into said
socket, said lip being symmetrical about said axis of rotation of
said cup.
3. The hip joint of claim 2 wherein said cup outer surface defines
a stem projecting in the opposite direction of said cup opening and
along said axis.
4. The hip joint of claim 3 wherein said stem is tapered.
5. The hip joint of claim 3 wherein said stem is separated from
said cup lip by an annular shoulder defined by said cup outer
surface, said shoulder and lip defining load bearing surfaces for
contacting said pelvis.
6. The hip joint of claim 1 wherein said cup inner surface is
interrupted by an indentation formed at the axis of rotation of
said cup.
7. An artificial hip joint comprising an artificial acetabular
component and an artificial femoral component, said acetabular
component constituting a cup having an axis of rotation and an
inner substantially spherical surface defining a socket symmetrical
about said axis and an outer surface of revolution formed
symmetrically about said axis, said outer surface including means
for guiding shiftable movement of said cup about its axis of
rotation when inserted into the acetabulum of a patient's pelvis,
said femoral component including a stem adapted for insertion into
the shaft of the femur after removal of the femoral head therefrom,
said stem carrying a ball, said ball having a substantially
spherical surface the radius of which is less than the radius of
the inner surface of said acetabular component, said ball fitting
within said socket and contacting the inner surface of said
acetabular component at locations spaced from the axis of rotation
of said cup in all positions of said ball during normal fore and
aft walking movement of said femur whereby said movement of the
femur will cause shiftable movement of said cup about its axis of
rotation and rolling movement of said ball relative to said cup
when said cup and ball are implanted within the acetabulum and
femur of said patient.
8. The hip joint of claim 7 and an outturned annular lip defined by
said cup outer surface, said lip defining a circular ball-receiving
opening into said socket.
9. The hip joint of claim 8 wherein said cup outer surface defines
a stem which projects in the opposite direction of said cup opening
and along said axis.
10. The hip joint of claim 9 wherein said cup stem is tapered.
11. The hip joint of claim 9 wherein said cup stem is separated
from said lip by an annular shoulder constituting a part of said
cup outer surface, said shoulder and lip defining load bearing
surfaces adapted to contact the pelvis of said patient.
12. An artificial hip joint comprising an artificial acetabular
component and an artificial femoral component, said acetabular
component constituting a cup having an axis of rotation and an
inner substantially spherical surface defining a socket symmetrical
about said axis and an outer surface of circular shape on all
planes normal to said axis and concentric with said axis, said
outer cup surface including means for guiding rotation of said cup
about said axis when positioned in the acetabulum of a patient's
pelvis with said axis at an angle to the normal direction of weight
transfer from the pelvis to the femur when a patient stands erect,
said femoral component including a stem adapted for insertion into
the shaft of the femur after removal of the femoral head therefrom,
said stem carrying a ball, said ball having a substantially
spherical surface whose radius is slightly less than the radius of
the inner surface of said acetabular component, said ball fitting
within said socket and contacting a limited area of the inner
surface of said acetabular component at a location spaced from the
axis of rotation of said cup in all positions of said ball during
normal fore and aft walking movement of said femur, whereby walking
movement of the femur causes rotative movement of said cup about
its axis and rolling movement of said ball relative to said
cup.
13. The hip joint of claim 12 wherein said cup includes an
outwardly projecting annular flange defining a lip at the mouth of
said cup.
14. The hip joint of claim 13 wherein said cup outer surface
defines a stem which projects coaxially of said cup opposite said
mouth.
15. The hip joint of claim 14 wherein said cup stem is tapered.
16. The hip joint of claim 14 wherein said cup stem is separated
from said flange by an annular shoulder constituting a part of said
cup outer surface, said shoulder and flange defining load bearing
surfaces adapted to contact the pelvis of said patient.
17. A hip prosthesis comprising interfitting acetabular and femoral
components; said acetabular component having a spherical socket and
an external configuration including a guide portion for maintaining
said acetabular component in predetermined orientation in an
acetabular recess of a pelvis during use; said acetabular component
having an axis relative to which and on all planes normal to which
all internal and all external surfaces are circular and concentric
to facilitate rotation in said recess; said femoral component
including an elongated stem, a spherical head and a reduced
diameter neck portion between said stem and head; said stem
anchoring said femoral component in a femur during use; said head
and neck having an axis relative to which and on all planes normal
to which all surfaces of said head are circular and concentric;
said head having a radius slightly less than the radius of said
acetabular socket whereby weight transfer contact between said
parts occurs only at a limited area of each; said components being
designed for installation in an orientation in which said axes are
disposed at an angle in all normal usage in standing and walking
whereby said limited area of weight transfer contact in said socket
occurs spaced from the axis of said acetabular component.
18. The hip prosthesis of claim 17 wherein said head is offset an
approximate 25.degree. angle from the longitudinal axis of said
elongated stem.
19. A method of providing an artificial hip joint for a patient
comprising the steps:
a. separating the head of a patient's femur from the patient's
pelvic acetabulum;
b. providing an artificial acetabular component having an axis of
rotation, an outer surface of revolution formed concentrically
about said axis, and an inner surface defining a socket concentric
with said axis;
c. reshaping the acetabulum of said patient to complementally
receive with rotative clearance said acetabular component with said
axis of rotation extending obliquely to the direction in which said
femur is pivoted during normal fore and aft walking movement of
said patient;
d. positioning said acetabular component within said reshaped
acetabulum for rotation about said axis of rotation and obliquely
to said direction of pivotal femur movement;
e. surgically removing the head of the patient's femur from the
shaft of the femur;
f. providing an artificial femoral component having a stem carrying
a ball slightly smaller than the socket of said acetabular
component;
g. anchoring said stem in the femoral shaft with said femoral ball
projecting from the end of the femur; and
h. fitting said ball into the socket of said acetabular component
and causing said ball to contact a limited area of the inner
surface of said acetabular component spaced from said axis of
rotation.
20. The method of claim 19 wherein steps e, f and g precede steps
b, c and d.
Description
BACKGROUND OF THE INVENTION
This invention relates to the field of orthopaedic surgery and has
particular application to a total artificial hip joint and the
implantation thereof.
A means of total surgical correction of a deteriorated or otherwise
malfunctioning hip joint is to replace the femoral head and neck
with an artificial ball which fits within an artificial cup
inserted into the acetabulum of the patient. The artificial ball
and cup are generally constructed from a hard material, such as a
cobalt-chromium alloy, which is biologically acceptable to the
patient. It has heretofore been the general practice either to
cement the acetabular component to the pelvic bone, such as in the
manner described in U.S. Pat. No. 3,521,302, or to provide the
acetabular component with retainer means, such as the spikes found
in U.S. Pat. No. 2,910,978, for anchoring the acetabular component
to the pelvic bone. When the artificial ball carried by the femur
of the patient is inserted into an artificial cup which is rigidly
attached to the pelvic bone and walking movement of the femur takes
place, there is sliding or rubbing action between the ball and cup
of the hip joint which creates wear of the components and a
resulting deposit of minute fragments from the cup and ball about
the joint area. This rubbing action between the cup and ball not
only creates undesirable wear pockets on the ball and within the
socket of the cup, but the deposit of the cup and ball fragments
about the joint area can cause inflammation of the joint and
discomfort to the patient. Even in the type of surgery in which a
Smith-Peterson type acetabular cup is inserted into the acetabulum
of the patient and not attached to the pelvic bone there still
exists a sliding motion between the implanted cup and ball which
creates an undesirable wear effect upon the artificial hip joint
and the deposit of wear fragments about the joint area.
In this invention, the artificial cup and ball of the hip joint are
designed to materially reduce wear between the components.
SUMMARY OF THE INVENTION
In this invention, the acetabular component of the artificial hip
joint includes a cup which is designed so that when inserted into
the acetabulum of the patient it will rotate freely about a
controlled axis of rotation. The femoral component of this
invention includes a ball which is designed so as to fit with
slight clearance within the socket of the acetabular cup and there
contact the inner surface of the cup at all times during fore and
aft walking movement of the femur at points spaced from the axis of
rotation of the cup. This structural relationship between the
acetabular cup and the femoral ball of the artificial hip joint
permits the ball to experience rolling action relative to the cup
during walking movement of the femur, thus materially reducing wear
between the cup and ball which, in turn, reduces the deposit of
fragments from the artificial components about the joint area.
The artificial acetabular and femoral components of this invention
are of a sufficient strength so as to minimize the risk of fatigue
failure of the components after extended periods of use. Also the
components of this invention can be implanted within the patient by
persons skilled in orthopaedic surgery in less time and with less
tissue manipulation than the standard prior art hip arthroplasty
devices utilized presently. Additionally, the acetabular component
of this invention because of its large area of surface contact with
the pelvic bone serves to reduce the concentration of hip load
forces at the acetabulum, thus minimizing any tendency for the
component to migrate into the pelvic bone and further minimizing
the bursting loads acting upon the pelvis about the area of the
acetabular component.
The design of the femoral component of this artificial hip joint
serves to position the femoral shaft more nearly under the
acetabulum of the hip, thereby causing a shortening of the abductor
and obturator muscles of the hip which in turn weakens such muscles
and reduces the total load upon the corrected hip. Additionally, by
moving the shaft of the femur more nearly under the acetabulum of
the patient, the hip loads are directed more closely along the
shank of the femur, thereby reducing any tendency for the stem of
the femoral component to wiggle or experience a "toggle" motion
when seated within the femur.
Accordingly, it is an object of this invention to provide an
artificial hip joint having an acetabular component carried by the
pelvis and a femoral component which is received within the
acetabular component and secured to the femur and which upon
walking motion of the femur causes the acetabular component to
experience shiftable movement within the pelvis about an axis of
rotation.
Another object of this invention is to provide a hip joint
replacement having an acetabular component and a femoral component
in which the femoral and acetabular components experience rolling
movement relative to each other upon fore and aft walking movement
of the femur which carries the femoral component.
Another object of this invention is to provide an artificial hip
joint having a long useful life while providing minimal patient
discomfort.
It is a further object of this invention to provide an artificial
hip joint having an acetabular component which in cooperating with
an artificial femoral component of the joint is designed to
distribute the hip load over the pelvic bone area which receives
the acetabular component, thereby reducing the unit load and
bursting force to which the pelvic bone is subjected during use of
the joint.
Still another object of this invention is to describe a method for
providing an artificial hip joint for a patient.
And still another object of this invention is to provide a
prosthesis for the femoral head and neck which reduces the
operational load upon the hip joint.
Further objects of this invention will become apparent upon a
reading of the invention's description.
BRIEF DESCRIPTION OF THE DRAWINGS
FIG. 1 is a perspective view of one embodiment of the artificial
hip joint of this invention showing the acetabular and femoral
components of the joint implanted in their respective body parts
but in separated form for purposes of illustration.
FIG. 2 is a sectional view of the hip joint illustrated in FIG. 1
showing the acetabular and femoral components in engagement.
FIG. 3A is illustrative of the hip joint of FIG. 1 showing the
acetabular and femoral components of the joint in one operative
position.
FIG. 3B is a view taken along line 3B--3B of FIG. 3A.
FIG. 4A is a perspective view of the acetabular and femoral
components shown in FIG. 3A showing the stem of the femoral
component pivoted forwardly as if the leg were swung forwardly in a
walking motion.
FIG. 4B is a view taken along line 4B--4B of FIG. 4A.
FIG. 5A is a perspective view of the acetabular and femoral
components of FIG. 3A showing the stem of the femoral component
pivoted rearwardly as if the leg were swung rearwardly in a walking
motion.
FIG. 5B is a view taken along FIG. 5B--5B of FIG. 5A.
FIG. 6 is a side view of the femoral component of the hip joint
illustrated in FIG. 1.
FIG. 7 is a cross sectional view taken along line 7--7 of FIG.
6.
FIG. 8 is a fragmentary perspective view of another embodiment of
the hip joint of this invention.
DESCRIPTION OF THE PREFERRED EMBODIMENTS
The preferred embodiments illustrated are not intended to be
exhaustive or to limit the invention to the precise forms
disclosed. They are chosen and described in order to best explain
the principles of the invention and its application and practical
use to thereby enable others skilled in the art to best utilize the
invention.
Referring to FIGS. 1 and 2, numeral 10 represents the pelvis and
numeral 12 represents the femur of a patient. The acetabular
component 14 of the embodiment of the artificial hip joint shown in
FIGS. 1 and 2 is of a cup-shaped configuration having an inner
spherical surface 16 which defines a socket 18. Component 14
includes an axis of rotation, designated by line 22 in FIG. 2,
about which inner surface 16 is symmetrically formed and an outer
surface 20 of revolution formed symmetrically about axis 22.
Surfaces 16 and 20 are circular and concentric in all planes normal
to axis 22. The opening or mouth of socket 18 is defined by a
coaxial annular outturned flange or lip 24 which forms a part of
outer surface 20. Outer surface 20 of component 14 defines a
coaxial stem 26 which extends rearwardly of socket 18. Stem 26 is
preferably tapered and is separated from lip 24 by an annular
coaxial shoulder 28 which forms a part of outer surface 20.
With the patient under anesthetic and the hip joint exposed with
the femoral head separated from acetabulum 30 of pelvis 10, a
reamer or similar bone cutting tool is utilized to reshape
acetabulum 30 to complementally receive the acetabular component
14. A hole is selectively punched in the bone shell in the
acetabulum. The acetabular component 14 is then inserted up into
the reshaped acetabulum with stem 26 entering the hole punched
therein and thereafter being urged into the cancellous pelvic bone
just above the acetabulum. The reformed acetabulum 30 is preferably
sized so as to be one to two millimeters larger than the acetabular
component for the purpose of permitting fibro cartilage 32 to
post-operatively form between the acetabular component and pelvic
bone. Outer surface 20 of component 14 is of a smooth finish so as
to permit unrestricted rotative movement of the component about its
axis of rotation when in acetabulum 30. Lip 24 and shoulder 28
including to a limited extent stem 26 of component 14 serve by
engaging pelvis 10 to minimize wobbling or similar movement of the
component within the acetabulum and thus control the position of
the axis 22 of rotation of the component and guide the component's
movement. Additionally, lip 24 and shoulder 28 provide large bone
contact surfaces which serve to widely distribute the hip joint
load to the pelvic bone and thus reduce the concentration of
bursting forces transmitted to the bone structure of the
acetabulum. For an acetabular component 14 having an outer diameter
of 57 mm as measured across lip 24, there will be a load carrying
cross sectional area of approximately 25.6 cm.sup.2. Approximately
90 percent, or 23 cm.sup.2, of this area will make effective bone
contact to distribute the hip joint load.
The femoral component 34 of the artificial hip joint illustrated in
FIGS. 1 and 2 includes a stem 36, which may be the standard
Austin-Moore type if desired, a platform 38 carried at the expanded
end of stem 36, and a head or ball 40 which is connected to
platform 38 by a neck 39. Ball 40 has a spherical surface 41.
Femoral component 34 is inserted into femur 12 by first surgically
removing the head and preferably also the neck of the femur. Stem
36 of component 34 is then driven downwardly through the
approximate center of shaft 62 of the femur until platform 38 is
brought into contact with the trochanter-defining shoulders 64 of
the femur as shown in FIGS. 1 and 2. Ball 40 of femoral component
34 is designed to have a smaller radius than the radius of socket
18 of acetabular component 14. The difference in radial dimension
between ball 40 and socket 18 is preferably between 0.003 and
0.0003 inches. Referring to FIG. 6, dimension A which represents
the angle head ball 40 makes relative to the vertical axis of stem
36 is preferably 25.degree.. This dimension varies from the
35.degree. similar angle in other types of prior art femoral
components and the normal 35.degree. to 40.degree. angle that the
femoral head makes relative to the shank of the femur in a human.
Dimension B in FIG. 6 represents the angle platform 38 makes
relative to a horizontal line intersecting the axis of stem 36.
Dimension B is preferably 25.degree. which varies from the
35.degree. to 40.degree. angle commonly used in prior art femoral
components. The purposes of these angular relationships of ball 40
and platform 38 will be explained later. Acetabular component 14
and femoral component 34 are formed of a hardened, biologically
acceptable metal, such as a cobalt-chromium-molybdenum alloy, or a
plastic.
In the operative procedure, ball 40 of femoral component 34 is
inserted by a surgeon into socket 18 in acetabular component 14 and
thereafter is held therein by the muscles of the hip joint. Since
ball 40 is of a smaller dimension than socket 18, the ball will
contact inner surface 16 of the acetabular component at a location
42 for a given position of stem 36. The term "contact" as used in
the description and claims of this invention includes not only load
transferring relationships where components 14 and 34 actually
physically touch but also those load transferring relationships
where ball 40 is slightly separated from inner surface 16 of socket
18 at the point of load transfer by a thin layer of body fluid.
Both surface 41 of ball 40 and inner surface 16 of the acetabular
component are polished and have a cofficient of friction
therebetween which exceeds the cofficient of friction between outer
surface 20 of the acetabular component and fibro cartilage 32
formed in the pelvis about the acetabular component. In a
construction of this invention in which components 14 and 34 are
constructed of a cobalt-chromium-molybdenum composition, the
cofficient of friction between surface 41 of ball 40 and the inner
surface 16 of component 14 will be approximately 0.2 or 0.3 while
the cofficient of friction between the outer surface 20 of the
acetabular component and cartilage 32 will be approximately 0.01.
As femur 12 in FIG. 2 is swung in a plane normal to the viewing
surface of the figure, ball 40 of component 34 will roll over inner
surface 16 of the acetabular component as component 14 is caused to
rotate about its axis 22 of rotation. This movement is illustrated
in FIGS. 3A-5B. In FIGS. 3A and 3B, the femoral component 34 is
shown with its stem 36 in a generally vertical position, such as
when the leg is held in a straight standing position. As shown in
FIGS. 4A and 4B, when stem 36 of femoral component 34 is swung
forwardly, as when the leg is pivoted in a forward direction,
rolling movement takes place between ball 40 of the femoral
component and inner surface 16 of acetabular component 14 which
causes the acetabular component to shift about its axis of rotation
within the patient's acetabulum in the direction shown by arrow 44.
As shown in FIGS. 5A and 5B, when the stem 36 of the femoral
component is swung rearwardly, as when the leg is pivoted in a
rearward direction, rolling movement in the reverse direction takes
place between ball 40 of component 34 and inner surface 16 of
component 14 which causes the acetabular component to shift about
its axis of rotation in the direction of arrow 46.
It is to be noted from FIGS. 3A-5B that the location 42 of the
regions or areas of contact between ball 40 and inner surface 16 of
component 14 as stem 36 of the femoral component 34 is pivoted fore
and aft do not coincide with the axis of rotation 22 of acetabular
component 14 but are spaced from axis 22. Therefore, it is
important when inserting the acetabular component 14 into the
acetabulum of the patient that component 14 be so situated that its
axis of rotation 22 will not coincide with the area of contact
between ball 40 and inner surface 16 of components 34 and 14 during
fore and aft walking movement of the femur. Should the area or
place of contact between ball 40 and inner surface 16 so coincide
with the axis of rotation of acetabular component 14, sliding, not
rolling, motion with increased wear will take place between
components 14 and 34.
By designing femoral component 34 with ball 40 thereof being offset
from the axis of stem 36 at an angle of approximately 25.degree.
(Dimension A in FIG. 6), the lateral displacement of femur 12 from
the acetabulum 30 of the patient is reduced approximately 17 mm
from the normal displacement of the femur when a prior art femoral
component having a 35 degree ball angle is used. By so locating the
femur more nearly under the acetabulum, the abductor and obturator
muscles are shortened and the unit load upon the artificial hip
joint is reduced so as to act as a safety feature against fracture
of the artificial joint components or the pelvic bone or femur.
While it is not necessary to construct the femoral component with
any specific ball-to-stem axis angle to practice this invention,
the utilization of a 25 degree ball angle instead of the normal 35
degree ball angle used in prior art femoral component constructions
will, in locating the femur more nearly under the acetabulum of the
pelvis reduce the tendency for the location of ball-to-socket inner
surface contact to coincide with the axis of rotation of the
acetabular component. Inner surface 16 of acetabular component 14
may be interrupted by a small indentation 48 formed about the axis
of rotation 22. Indentation 48 will serve to maintain some degree
of rotative movement of the acetabular component 14 should the area
of ball-to-socket inner surface contact closely approach
coincidence with the axis of rotation of component 14.
As illustrated in FIG. 7, the lower end portion of stem 36 of
femoral component 34 is of a flattened cross sectional form at face
part 35 which when inserted into femoral shaft 62 reduces the
tendency for the stem to oscillate or shift laterally within the
femur. Thickness C (See FIGS. 3B and 7) of stem 36 preferably
progressively increases in size from platform 38 to opposite end 37
of the stem. This increase in thickness or flare of stem 36 reduces
the tendency for the stem to wobble within the femur. Additionally,
by reducing the angle of platform 38 of femoral component to
25.degree. (Dimension B in FIG. 6) from the normal 35.degree. to
40.degree. platform angle utilized in the prior art femoral
components, there is also a reduction in the tendency for the
femoral component to shift laterally within the femur.
FIG. 8 is illustrative of another embodiment of the artificial hip
joint of this invention. Acetabular component 50 of this embodiment
is of a dome shape having an inner spherical surface 52 which
defines a socket 54 and an outer spherical surface 56. The opening
into socket 54 is defined by an annular outturned flange or lip 58.
Acetabular component 50 is designed to be utilized in those
patients having a pelvic bone structure which will not permit the
utilization of the larger stem-type acetabular component 14 above
described. The method of implantation of acetabular component 50 is
similar to that described for acetabular component 14. Component 50
also has an axis of revolution 22' about which inner surface 52 and
outer surface 56 are symmetrically formed. Lip 58 serves in
contacting the pelvic bone 59 to minimize wobbling movement of
component 50 within the acetabulum 60 and thus control the position
of the axis of rotation 22' of the component and guide the
component's movement. Femoral component 34 above described is
utilized in this embodiment of the hip joint. Ball 40 of the
femoral component 34 is slightly smaller than socket 54 of
acetabular component 50. The manner of operation and the relative
rolling movement between components 34 and 50 are similar to that
described for the embodiment of the hip joint illustrated in FIGS.
1-7.
When the artificial hip joint of this invention is in use, a wedge
of body fluid may be formed between the acetabular and femoral
components within the socket 18 or 54 of the acetabular component.
Due to the fit between ball 40 or femoral component 34 and inner
surfaces 16 and 52 of the acetabular components 14 and 50
respectively, the drag of the mating surfaces of the ball 40 and
socket 54 or 18 over the body fluid may cause the ball to climb
into a wedge of fluid created between the surfaces and thus be
lubricated during its rolling motion relative to the acetabular
component, thereby further reducing the wear between the femoral
and acetabular components 34, 50 and 14.
It is to be understood that this invention is for use in the
general healing arts and may be used by veterinarians as well as
medical doctors. Additionally, it is to be understood that this
invention is not to be limited to the details herein given but may
be modified within the scope of the appended claims.
* * * * *