US3800333A - Artificial leg - Google Patents

Artificial leg Download PDF

Info

Publication number
US3800333A
US3800333A US00208325A US3800333DA US3800333A US 3800333 A US3800333 A US 3800333A US 00208325 A US00208325 A US 00208325A US 3800333D A US3800333D A US 3800333DA US 3800333 A US3800333 A US 3800333A
Authority
US
United States
Prior art keywords
section
ankle
calf
shank
foot
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
Application number
US00208325A
Inventor
K Friberg
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
FRIBERG K AB
Original Assignee
FRIBERG K AB
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by FRIBERG K AB filed Critical FRIBERG K AB
Application granted granted Critical
Publication of US3800333A publication Critical patent/US3800333A/en
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50Prostheses not implantable in the body
    • A61F2/60Artificial legs or feet or parts thereof
    • A61F2/604Joints for artificial legs

Definitions

  • the shank section is formed with an [52] US. Cl 3/21, 3/1.2, 3/23, an l to which is j rn lled a foo ction.
  • a mecha- 3/27 nism is provided to bring about controls over the [51] Int. Cl.
  • A6lf 1/08 h nk i n m ions, s i mechanism being housed [58] Field of Search 3/22 29, 1.2, 'in a shell-shaped calf section constituting the upper 1 3/2] part of the shank.
  • the ankle has a cylindrical top portion received in a sleeve in the lower portion of the [56] References Cited calf section for securing and adjusting said ankle rela- UNTED STATES PATENTS tively the calf section.
  • Rcgnell 3 1.2 also arranged a base fies'gned and Semng to ceive and secure a fork-llke attachment means in 2,692,392 10/1954 Bennington et al 3/21 UX which the lower end of said mechanism is oumalled.
  • 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 calfsection shaped-as a shell and in the interior of which said mechanism or unit controlling the knee joint functions as defined above is enclosed.
  • 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.
  • 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.
  • 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.
  • 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.
  • 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 present invention eliminates the abovementioned 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 shellshaped 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.
  • 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;
  • knee joint mechanisms of various types for swing and for stance control may be mounted in the shank section, and
  • the leg may be given a shape corresponding to the shape of the sound leg.
  • 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 relatively FIG. 1,
  • FIG. 3 illustrates on an enlarged scale a horizontal longitudinal section along linge IIIIII 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
  • FIG. 7 is an end view of the fork member of FIG. 6.
  • the upper leg or thigh socket l 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 shellshaped calf section 3' at the lower portion of which an ankle 4 is attached so as to be articulated to an artificial foot 5.
  • 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.
  • valve housing 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 ofa 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 fonned 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.
  • 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 l fitting the femoral stump 40 of an amputee.
  • the same calf section 3' may be used for practically all aboveknee amputees.
  • 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,-fllowed 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 invention is not either limited to the construction 5 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.
  • ankle section a horizontal shaft, a lower foot plate ar-.
  • 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
  • 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.

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.

Description

United States Patent 1191 Friberg 51 Apr. 2, 1974 1 1 ARTIFICIAL LEG 120,893 12 1959 u.s.s.R 3/21 {75] Inventor: Karl Axel Friberg, Oskarshanin,
Swede" Primary Examiner-Richard A. Gaudct Assistant Examiner-Ronald L. Frinks 73 Ass1 n Aktl bol t K.A. I be V' l l g u swcjcn age n rg dxjo Attorney, Agent, or FirmHarncss, Dickey & Pierce [22] Filed: Dec. 15, 197] 21 Appl. No.: 208,325 15 1 AB TRACT An artificial leg of modular structure for above- [30] Foreign Application Priority Data knee amputees comprising a thigh section, a shank .Ian. 7, 1971 Sweden 94 71 section, and a knee joint connecting the thigh and shank sections. The shank section is formed with an [52] US. Cl 3/21, 3/1.2, 3/23, an l to which is j rn lled a foo ction. A mecha- 3/27 nism is provided to bring about controls over the [51] Int. Cl. A6lf 1/08 h nk i n m ions, s i mechanism being housed [58] Field of Search 3/22 29, 1.2, 'in a shell-shaped calf section constituting the upper 1 3/2] part of the shank. The ankle has a cylindrical top portion received in a sleeve in the lower portion of the [56] References Cited calf section for securing and adjusting said ankle rela- UNTED STATES PATENTS tively the calf section. At the lower end of the calf sec- 2,671,224 3/1954 Rcgnell 3 1.2 also arranged a base fies'gned and Semng to ceive and secure a fork-llke attachment means in 2,692,392 10/1954 Bennington et al 3/21 UX which the lower end of said mechanism is oumalled. FOREIGN PATENTS OR APPLICATIONS 87,730 8/1959 Denmark 3/25 3 Claims, 7 Drawing Figures 1 ARTIFICIAL LEG 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 calfsection 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 toreplace 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 prefabricated 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 theprosthesis. 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 severaldefects 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, c0-
ordination 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 teams 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 forswing and stance control available today is capable of performing.
SUMMARY OF THE INVENTION The present invention eliminates the abovementioned 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 shellshaped 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 relatively FIG. 1,
FIG. 3 illustrates on an enlarged scale a horizontal longitudinal section along linge IIIIII 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 l 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 shellshaped 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 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 ofa 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 ofa 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 fonned 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.
5 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 l fitting the femoral stump 40 of an amputee. The same calf section 3' may be used for practically all aboveknee 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,-fllowed 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 andthe invention is not limited to the embodiment disclosed.
The invention is not either limited to the construction 5 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.
ankle section, a horizontal shaft, a lower foot plate ar-.
ticulated 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.

Claims (3)

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.
US00208325A 1971-01-07 1971-12-15 Artificial leg Expired - Lifetime US3800333A (en)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
SE00094/71A SE348934B (en) 1971-01-07 1971-01-07

Publications (1)

Publication Number Publication Date
US3800333A true US3800333A (en) 1974-04-02

Family

ID=20256028

Family Applications (1)

Application Number Title Priority Date Filing Date
US00208325A Expired - Lifetime US3800333A (en) 1971-01-07 1971-12-15 Artificial leg

Country Status (13)

Country Link
US (1) US3800333A (en)
JP (1) JPS5646852B1 (en)
AT (1) AT336771B (en)
AU (1) AU461646B2 (en)
CA (1) CA968902A (en)
DE (1) DE2200561A1 (en)
DK (1) DK129383B (en)
ES (1) ES398654A1 (en)
FR (1) FR2119441A5 (en)
GB (1) GB1380428A (en)
IL (1) IL38365A (en)
IT (1) IT943394B (en)
SE (1) SE348934B (en)

Cited By (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4065815A (en) * 1976-09-28 1978-01-03 Sen Jung Chen Hydraulically controlled artificial leg
US5593455A (en) * 1994-05-27 1997-01-14 Phillips; Van L. Plug mounted prosthesis
US6478826B1 (en) 1998-04-10 2002-11-12 Van L. Phillips Shock module prosthesis
US6511512B2 (en) 1998-04-10 2003-01-28 Ossur Hf Active shock module prosthesis
US20050071017A1 (en) * 2003-09-30 2005-03-31 Lecomte Christophe Guy Low profile active shock module prosthesis
US20050203638A1 (en) * 2004-03-01 2005-09-15 Slemker Tracy C. Modular stance flexion component for a prosthetic limb
US20090299491A1 (en) * 2004-03-01 2009-12-03 Slemker Tracy C Modular shock absorbers for prosthetic limbs

Families Citing this family (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3950808A (en) * 1974-05-03 1976-04-20 Sorenson Hugh Buoyancy circular water ski
TW238244B (en) * 1992-03-24 1995-01-11 Lehn Phillips Van
US6106560A (en) * 1999-03-30 2000-08-22 Michael O'Byrne Hydraulic knee joint
EP4003240A1 (en) 2019-07-30 2022-06-01 College Park Industries, Inc. Hydraulic prosthetic knee with resistance change mechanism at hyperextension

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2671224A (en) * 1951-07-02 1954-03-09 Carl E Regnell Artificial leg
US2692392A (en) * 1951-04-05 1954-10-19 Modern Limb Supply Co Inc Artificial limb
SU120893A1 (en) * 1958-12-26 1959-11-30 Г.А. Дегтярев Educational and therapeutic hip prosthesis

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2692392A (en) * 1951-04-05 1954-10-19 Modern Limb Supply Co Inc Artificial limb
US2671224A (en) * 1951-07-02 1954-03-09 Carl E Regnell Artificial leg
SU120893A1 (en) * 1958-12-26 1959-11-30 Г.А. Дегтярев Educational and therapeutic hip prosthesis

Cited By (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4065815A (en) * 1976-09-28 1978-01-03 Sen Jung Chen Hydraulically controlled artificial leg
US5593455A (en) * 1994-05-27 1997-01-14 Phillips; Van L. Plug mounted prosthesis
US5888238A (en) * 1994-05-27 1999-03-30 Phillips; Van L. Plug mounted prosthesis
US20050209707A1 (en) * 1998-04-10 2005-09-22 Phillips Van L Active shock module prosthesis
US6511512B2 (en) 1998-04-10 2003-01-28 Ossur Hf Active shock module prosthesis
US20040068325A1 (en) * 1998-04-10 2004-04-08 Phillips Van L. Shock module prosthesis
US6887279B2 (en) 1998-04-10 2005-05-03 össur hf Active shock module prosthesis
US6478826B1 (en) 1998-04-10 2002-11-12 Van L. Phillips Shock module prosthesis
US7169190B2 (en) 1998-04-10 2007-01-30 Van L. Phillips Active shock module prosthesis
US20050071017A1 (en) * 2003-09-30 2005-03-31 Lecomte Christophe Guy Low profile active shock module prosthesis
US6969408B2 (en) 2003-09-30 2005-11-29 Ossur Engineering, Inc. Low profile active shock module prosthesis
US20060004467A1 (en) * 2003-09-30 2006-01-05 Lecomte Christophe G Low profile active shock module prosthesis
US7371262B2 (en) 2003-09-30 2008-05-13 össur hf Low profile active shock module prosthesis
US20050203638A1 (en) * 2004-03-01 2005-09-15 Slemker Tracy C. Modular stance flexion component for a prosthetic limb
US20090299491A1 (en) * 2004-03-01 2009-12-03 Slemker Tracy C Modular shock absorbers for prosthetic limbs

Also Published As

Publication number Publication date
DE2200561A1 (en) 1972-07-20
ATA14172A (en) 1976-09-15
AT336771B (en) 1977-05-25
IT943394B (en) 1973-04-02
FR2119441A5 (en) 1972-08-04
IL38365A (en) 1975-02-10
DK129383B (en) 1974-10-07
CA968902A (en) 1975-06-10
ES398654A1 (en) 1976-03-01
JPS5646852B1 (en) 1981-11-06
SE348934B (en) 1972-09-18
IL38365A0 (en) 1972-02-29
AU461646B2 (en) 1975-06-05
AU3716571A (en) 1973-06-28
GB1380428A (en) 1975-01-15
DK129383C (en) 1975-02-24

Similar Documents

Publication Publication Date Title
US6908488B2 (en) Support device replacing the existence or function of a limb
US6482236B2 (en) Prosthetic ankle joint mechanism
RU2113192C1 (en) Device for obtaining of reciprocal rotary joint of orthopedic apparatus parts
US7942935B2 (en) Device and system for prosthetic knees and ankles
US3824630A (en) Prosthetic joint for total knee replacement
US3800333A (en) Artificial leg
JP5336386B2 (en) Artificial ankle joint mechanism
US5895430A (en) Prosthesis for long femur and knee disarticulation amputation
EP1954217B1 (en) An adjustment device for a lower limb prosthesis
JPH05146A (en) Rotatably movable joined body
US4442554A (en) Biomechanical ankle device
US7153329B2 (en) Prosthetic hip joint with side pivot
Fridman et al. The influence of prosthetic foot alignment on trans-tibial amputee gait
US20220054284A1 (en) Prosthetic joint with a mechanical response system to position and rate of change
US4614518A (en) Artificial limb with automatic release for free rotation
US3800334A (en) Arrangement in feet for leg prostheses
RU2055548C1 (en) Knee unit with automatic fixation
US4149280A (en) Structure of a stabilized artificial limb
GB2274994A (en) Assessment prosthesis and prosthetic leg
Angarami et al. An efficient low cost prosthetic structural system
James Principles of limb fitting and prostheses.
EP0244493A1 (en) Artificial limb with automatic release for free rotation
Hirons et al. The prosthetic treatment of lower limb deficiency
WO2021154183A1 (en) A rotation adapter to be used for prostheses
Holmgren The interface between the body and the above-knee prosthesis