U.S. patent number 3,800,333 [Application Number 05/208,325] was granted by the patent office on 1974-04-02 for artificial leg.
This patent grant is currently assigned to Aktiebolaget K.A. Friberg. Invention is credited to Karl Axel Friberg.
United States Patent |
3,800,333 |
Friberg |
April 2, 1974 |
ARTIFICIAL LEG
Abstract
An artificial leg -- of modular structure -- for above-knee
amputees comprising a thigh section, a shank section, and a knee
joint connecting the thigh and shank sections. The shank section is
formed with an ankle to which is journalled a foot section. A
mechanism is provided to bring about controls over the shank
section motions, said mechanism being housed in a shell-shaped calf
section constituting the upper part of the shank. The ankle has a
cylindrical top portion received in a sleeve in the lower portion
of the calf section for securing and adjusting said ankle
relatively the calf section. At the lower end of the calf section
is also arranged a base designed and serving to receive and secure
a fork-like attachment means in which the lower end of said
mechanism is journalled.
Inventors: |
Friberg; Karl Axel (Oskarshamn,
SW) |
Assignee: |
Aktiebolaget K.A. Friberg
(Vaxjo, SW)
|
Family
ID: |
20256028 |
Appl.
No.: |
05/208,325 |
Filed: |
December 15, 1971 |
Foreign Application Priority Data
Current U.S.
Class: |
623/38; 623/40;
623/26; 623/44 |
Current CPC
Class: |
A61F
2/604 (20130101) |
Current International
Class: |
A61F
2/60 (20060101); A61f 001/08 () |
Field of
Search: |
;3/22-29,1.2,21 |
References Cited
[Referenced By]
U.S. Patent Documents
Foreign Patent Documents
|
|
|
|
|
|
|
87,730 |
|
Aug 1959 |
|
DK |
|
120,893 |
|
Dec 1959 |
|
SU |
|
Primary Examiner: Gaudet; Richard A.
Assistant Examiner: Frinks; Ronald L.
Attorney, Agent or Firm: Harness, Dickey & Pierce
Claims
What I claim is:
1. In an improved artifical leg, particularly intended for
above-knee amputees, comprising a thigh section, a shank section, a
knee joint shaft articulating said thigh section to said shank
section, an ankle section on said shank section, said ankle section
comprising an upper ankle plate forming the upper portion of said
ankle section, a horizontal shaft, a lower foot plate articulated
at the forward end of said ankle plate by means of said horizontal
shaft, and a spring being mounted between said foot plate and said
ankle plate behind said horizontal shaft for forcing them apart, an
artifical foot, means pivotally connecting said artificial foot to
said foot plate, a mechanism for controlling the knee joint
functions, said shank section comprising a calf section enclosing
said knee joint function controlling mechanism, a cylindrical tube
portion affixed to and extending upwardly from said upper ankle
plate within the lower end of said calf section, clamping means at
the lower end of said calf section for enabling adjustment of said
cylindrical tube portion and said ankle section relative to said
calf section and for securing said ankle section to said calf
section, a base portion at the lower end of said calf section above
said cylindrical tube portion, an opening formed in said base
portion, said horizontal shaft being located ahead of the
prosthesis weight supporting line passing through said thigh
section, said knee joint shaft and said ankle section, a vertical
bore in said upper ankle plate, a clamping element displaceable in
said bore, an elongate member clamped by said element, extending in
part through said base portion opening and being provided to
actuate said knee-joint function controlling mechanism as a result
of the vertical displacement of the clamping element in said bore,
and a shoulder at the upper end of said bore for holding said
spring in a compressed state between said shoulder and said
clamping element.
2. An improved artificial leg as set forth in claim 1 wherein the
clamping means comprises a clamping sleeve integral with the calf
section, said ankle section being rotatably mounted in said
clamping sleeve for setting the desired foot angle.
3. An improved artificial leg as set forth in claim 1 wherein the
elongate member comprises a flexible transmitter.
Description
BACKGROUND OF THE INVENTION
The present invention relates to artificial legs and particularly
to above-knee prostheses comprising an upper leg component or thigh
section which by means of a knee joint shaft is pivotally connected
to a lower leg component or shank section having an ankle portion
to which an artificial foot is preferably pivotally connected, and
also comprising a mechanism or unit controlling the shank section
motions, i.e., knee flexion or knee extension, during the swing
phase and/or stance phase. The shank section comprises a
calf-section shaped as a shell and in the interior of which said
mechanism or unit controlling the knee joint functions as defined
above is enclosed.
In establishing which qualities and functions are to be imparted to
an artificial leg it is of utmost importance to doctors and
prosthetists that they are able to observe the ability of the
amputee to take advantage of these qualities and functions. The
majority of the observations must be carried out in connection with
studies during the walk training exercises or other kinesiotherapy
exercises of the amputee. This is true both in the case of patients
who have previously been amputated and who want to replace an
out-of-date prosthesis by a more modern and multifunctional one as
in the case of recent amputees.
It is highly desirable that the kinesiotherapy starts as soon as
possible after the amputation as an early start has a decisive
influence on the obtainment of optimum recovery of the convalescent
as well as of optimum conditioning of his leg stump. In order to be
able to start the therapy early it is necessary that a temporary
prosthesis is immediately available. This temporary prosthesis must
be multifunctional, i.e., it must be capable of performing all the
functions required to enable the patient at the earliest possible
stage of his walking training to achieve good posture and the best
possible gait and ambulatory capability.
A leg prosthesis which does not meet these requirements constitutes
and impediment to the patient and in the long run may even be
harmful to him. At the same time such a faulty prosthesis deprives
the rehabilitation team (including doctors and prosthetists) of the
advantages of acquiring an extensive basis for their evaluation and
prescription of the permanent prosthesis. The prescription of a leg
prosthesis is difficult enough even without such lack of an
adequate evaluation basis.
Hitherto commercially available and partly mounted fittings of wood
-- so called set-ups -- are not suitable for use as temporary
prostheses. The reason therefor is that they are heavy and that
they are not suited for or do not lend themselves to be simply and
quickly mounted. Even less do they permit selection among a
plurality of available mechanisms for controlling for instance the
knee joint functions of one particular mechanism which may be
especially well suited in the individual case. Consequently, it
becomes impossible to reproduce many of the various functions which
must be studied and considered before the design of the final and
permanent prosthesis most adequate for the patient can be decided
upon.
In this connection it should be remembered that in recent years the
possibilities of rehabilitating amputees have improved considerably
in as much as a new technique is now being used. This new technique
accentuates the need of immediate access to a temporary prosthesis
and emphasizes the need for a system of pre-fabricated and
precision-made prosthetic components which allow themselves to be
quickly and simply assembled into a multifunctional, temporary
prosthesis which may be completed or converted to form a permanent
(final) prosthesis providing all the functions which in the
individual case are desirable in order to meet high demands on
comfort, cosmesis and ambulatory capability. To use provisional
components and maybe components chosen at random for the temporary
prosthesis is undesirable as such components will impede rather
than further a correct composition of the prosthesis and make it
impossible to achieve an acceptable biomechanical function. The use
of such makeshift prosthetic parts has hitherto been allowed too
extensively to attain the per se desirable rapid start of the
kinesiotherapy for recent amputees. Almost without exceptions the
consequence has been an artificial gait which far from resembles
the best possible gait that the patient may achieve. In addition to
mounted set-ups of wood intended for so called conventional
prostheses and which are not suited for making up a temporary
prosthesis, a multitude of types and brands of components are
available on the market which are constructed for -- and in shape
and design limited to -- one particular device or mechanism for
controlling the knee joint during the swing or stance phases. These
components are completely adjusted to the functions of the
mechanism in question. The mechanism is often bulky and as a result
the minimum dimensions of the finished prosthesis do not permit the
configuration and shape of the prosthesis to simulate those of the
natural leg. For this reason it becomes impossible to fully meet
the demands on function and cosmesis, i.e., on good design and
adequate performance. Further disadvantages are the heavy weight
and the length of time necessary to assemble the prosthesis. The
above-mentioned drawbacks apply to recent amputees as well as to
prior amputees.
These last-mentioned constructions thus are definitely unsuitable
as temporary prostheses. As they are limited by the functions of a
particular mechanism they do not offer a broad and adequate basis
for the evaluation by the rehabilitation team. Their inadequacy as
temporary prostheses also makes them less fit for use as permanent
or final prostheses. The reason herefor is that the patient would
be forced to readjust the motion pattern adopted during the
training with the aid of the temporary prosthesis, the latter
serving the double purpose -- in the case of recent amputees -- of
providing an adequate conditioning of the stump and -- in the case
of both recent amputees and prior amputees -- of providing for
optimum ambulatory capability and walking technique. A permanent
prosthesis which does not perform the functions which during the
kinesiotherapy have been found suitable and fitting for a
particular amputee patient naturally cannot be prescribed or
accepted by the modern rehabilitation technique.
Also other types have been used as temporary artificial legs. Most
of them do, however, suffer from several defects largely reducing
their suitability as prostheses for temporary or permanent use.
It is thus important that the temporary prosthesis lends itself to
reproducing a plurality of various functions concerning knee joint
control, ankle function, coordination between knee and feet
motions, and so on. Obvious reasons speak for constructing the
temporary prosthesis in a way enabling it to be easily and
advantageously completed and converted into a multifunctional and
permanent prosthesis. The types of prostheses now available do not
fulfil these fundamental demands. They suffer from one or several
of the following drawbacks:
1. They reduce the prosthetic team's observations on the amputee
into one type only of a friction during the swing phase -- most
often the mechanical friction which is far from acceptable from a
biomechanical point of view;
2. they are reduced to use in connection with one single mechanism
for controlling the knee joint functions;
3. they presuppose the use of maybe one single type of artificial
foot, it being then indirectly -- but inacceptably so -- assumed
that this foot and its particular alignment is a good choice for
all amputees;
4. they do not enable obtainment of acceptable cosmesis, nor do
they offer adequate protection of the mounted mechanism for swing
and/or stance control (this is true of the few types constructed
for such mounting), and
5. without exceptions they suffer from the severe limitation of not
providing means or devices to coordinate the knee joint function
with that of the ankle and foot. Such coordination is an absolute
requirement if one is to simulate with any degree of success the
function of the natural leg in this respect, which simulation at
least one mechanism for swing and stance control available today is
capable of performing.
SUMMARY OF THE INVENTION
The present invention eliminates the above-mentioned drawbacks and
makes it possible to convert in a simple way a temporary prosthesis
into a permanent one. The invention is characterised in that the
ankle at least at its upper end is in the shape of a cylindrical
tube and that the lower end of the shell-shaped calf section is
provided with a clamping means adapted to enable vertical
adjustment of the ankle relatively to the shell-shaped calf section
and to secure said ankle to said calf section, and in that the
lower end of the shell-shaped calf section is provided with a base
portion serving to secure an attachment means to which the lower
end of the knee function controlling mechanism is preferably
hingedly connected.
Among the advantages obtained by means of the invention may be
mentioned the following:
The length of the prosthesis may be altered in a simple an quick
way, which is important for children and teen-agers during their
growth period;
Simplified storage of prosthesis components with the surgical
prosthetist or in clinics, as the shank, the knee joint mechanism,
the ankle and the artificial foot may be standardized and only the
ankle needs be cut into the correct length before mounting,
knee joint mechanisms of various types for swing and for stance
control may be mounted in the shank section, and
by means of cosmetic covers of foam plastic the leg may be given a
shape corresponding to the shape of the sound leg.
BRIEF DESCRIPTION OF THE DRAWINGS
The invention will be described more in detail in the following
with reference to the accompanying drawings wherein
FIG. 1 is a vertical longitudinal section through an artificial leg
in accordance with the invention,
FIG. 2 is a similar longitudinal section as seen when the leg is
turned over 90.degree. relatively FIG. 1,
FIG. 3 illustrates on an enlarged scale a horizontal longitudinal
section along linge III--III in FIG. 2,
FIG. 4 is a side view showing partly in longitudinal section an
upright incorporated in the ankle part,
FIG. 5 is a plan view of the upright in FIG. 4,
FIG. 6 is a side view of a fork member incorporated in the shank
section, and
FIG. 7 is an end view of the fork member of FIG. 6.
DETAILED DESCRIPTION OF A PREFERRED EMBODIMENT
The upper leg or thigh socket 1 is as shown in FIG. 1 connected to
the lower leg component or shank section 3 by means of a shaft 2
forming the articulated knee joint. The shank section 3 comprises a
shell-shaped calf section 3' at the lower portion of which an ankle
4 is attached so as to be articulated to an artificial foot 5. From
the thigh socket 1 projects forwardly an arm 6 which by means of a
pivot 7 is connected to the upper end of an hydraulic mechanism 8
providing swing and stance phase control and permitting rotational
movement of the shank section 3 relatively the thigh socket 1
within an angle of about 130.degree.. In accordance with the
embodiment illustrated, the hydraulic mechanism 8 comprises two
cylinders 9, 10 which contain liquid and are positioned co-axially
in the longitudinal direction relatively each other and have one
displaceable piston (not shown) each. These pistons are rigidly
attached on a common piston rod 11. Reference number 12 designates
the attachment loop of the lower cylinder 10. The piston rod 11
extends through a bushing in a valve housing 13 positioned between
the cylinders 9, 10. In the valve housing is inserted a valve (not
shown) provided with a valve arm 14 by means of which a channel
communicating the interiors of the two cylinders 9, 10 may be
closed off to block the knee joint in a particular position. The
valve is turned to closing position by means of a traction spring
15.
The mechanism 8 controlling the knee joint functions, i.e., the
swing and stance phases, is hingedly connected at its lower end by
means of a bolt 16 to a forklike member 17 which by means of a
bayonet catch 18 is detachably secured in a base portion 19 at the
lower end of the calf section 3'. The base portion 19 preferably
may be made integral with the rest of the calf section 3'. In the
fork member 17 is journalled by means of a pin 20 (or bolt) one end
of a lever 21, the opposite end 22 of which is connected by means
of a thread-like link 23 to the lower portion 24 of the valve arm
14. A coupling wire 26 is attached at its upper end 25 to the lever
21, said coupling wire passing freely through a vertical channel 27
formed in the fork member 17. The lower end of the coupling wire 26
is by means of a chuck 28 attached to a regulating member 29 which
is operated by the vertical movements of the artificial foot and is
vertically displaceable in the ankle portion 4.
The ankle portion 4 comprises an ankle plate 31 which by means of a
horizontal shaft 30 is articulated to the artificial foot 5, a
tube-like upright 33 having a flange 32 thereon being attached to
said plate 31. The upper end 34 of the upright 33 is insertable in
a clamping sleeve 35, said sleeve extending downwardly from the
base portion 19. The clamping sleeve 35 is provided with a
vertically extending slit 36 and clamping sleeve portions 37 and 38
on either side of said slit 36 may be tightened about ankle means
89 the upper end 34 of the upright by means of a clamping screw
39.
Obviously, the calf section 3' together with its associated control
mechanism 8 and the parts pertaining thereto may be stored in for
instance a clinic in a mounted condition ready for application in
the socket 1 fitting the femoral stump 40 of an amputee. The same
calf section 3' may be used for practically all above-knee
amputees. Also the artificial foot 5 in a few various sizes thereof
may be stored in a mounted condition, ready for use, the ankle
portion 4 including the ankle plate 31 being, if desired, also
mounted on the artificial foot. After measuring the length of the
sound leg of the amputee the length of the artificial leg is
established and the upright 33 on the ankle 4 is shortened to the
correct length. The coupling wire 26 is attached by means of its
lower end to the chuck 28 and the upper upright end 34 is by means
of the clamping screw 39 secured after setting of the correct foot
angle by turning the upright 33 in the clamping sleeve 35. The
artificial leg is thereafter ready for application, followed by
adjustment, if needed, and is then fit for use.
The artificial leg may easily be surrounded by sections made of
plastics or enclosed in plastics to impart to the prosthesis a
configuration which as closely as possible simulates the
configuration of the sound leg.
The embodiment as illustrated and described is to be regarded as an
example only and the various parts of the prosthesis may be
constructively altered in various ways within the scope of the
appended claims. Instead of the hydraulic mechanism 8 a purely
mechanical device may be used. It is evident that the shank section
3 may house any suitable mechanism of this kind and the invention
is not limited to the embodiment disclosed. The invention is not
either limited to the construction of the artificial foot 5
illustrated in the drawings. The fork member 17 may be attached to
the base portion 19 in some other way than by means of a bayonet
catch, for instance by means of a threaded pin.
* * * * *