PROSTHESIS SYSTEM

Abstract

In the case of known prosthesis systems and socket supplies, the transmission of force is a critical issue. The inventive prosthesis system shall improve known prosthesis systems. According to the invention, a prosthesis system for human limbs is provided, which comprises an implant (101) having at least two joint parts which are movable relative to each other, wherein the first joint part (110) can be connected to a bone part (131, 132) and the second joint part (120) comprises a subcutaneously arrangeable end part (124) on the side being remote from the joint. The invention further relates to a prosthesis system comprising a subcutaneous implant and a socket (170).

Claims

1. A prosthesis system for human limbs, the prosthesis system comprising: an implant having at least two mutually movable joint members, wherein the first joint member can be connected to a bone portion; and the second joint member has an end portion which is intended to be arranged subcutaneously at the side thereof remote from the joint.

2. The prosthesis system according to claim 1, wherein the end portion is constructed in a plate-like manner.

3. The prosthesis system according to claim 1, wherein the end portion has a convex-curved outer face.

4. The prosthesis system according to claim 1, wherein the first joint member is in the form of an articular head and the second joint member is in the form of an articular socket.

5. The prosthesis system according to claim 1, wherein the first joint member is constructed in a hollow manner and has fixing means for connection to the bone portion which are selected from the group consisting of bone-forming material, bone cement and adhesive.

6. The prosthesis system according claim 1, wherein the first joint member can be connected to a bone portion via a medullary pin and/or a screw unit.

7. The prosthesis system according to claim 1, wherein the end portion has a radially peripheral edge region.

8. The prosthesis system according claim 1, wherein the end portion of the second joint member has faces and/or material for connecting muscles.

9. The prosthesis system according to claim 1, further having a shaft which at least partially surrounds the limb stump of the prosthesis user in order to be connected to extracorporeal prosthesis mechanisms.

10. The prosthesis system according to claim 9, wherein the shaft has a counter-plate, the form of which is adapted to the outer form of the second joint member.

11. The prosthesis system according to claim 9, wherein the shaft is in the form of a frame shaft.

12. The prosthesis system according to claim 9, wherein the shaft has a band extending in a circular manner as a retention device for the shaft.

13. The prosthesis system according to claim 1, wherein there is provided at least one external measurement system which has measurement sensors for detecting the position of the second joint member.

14. The prosthesis system according to claim 13, wherein the at least one external measurement system is constructed as a counter-plate and/or pipe element.

15. The prosthesis system according to claim 1, wherein at least one internal measurement system is provided in order to detect at least one of the position and loading of at least the second joint member.

16. The prosthesis system according to claim 13, further having a control unit, wherein extracorporeal prosthesis mechanisms can be controlled on the basis of the measurement signals detected.

17. A method for controlling a prosthesis system according to claim 1, the method comprising: connecting muscles of the prosthesis user to the end portion of the second joint member; and controlling movements of the second joint member by the muscles.

18. The method according to claim 17, comprising: providing a measurement system in order to detect the position of the second joint member via measurement sensors; and controlling extracorporeal prosthesis mechanisms via a control unit on the basis of the measurement signals detected.

Description

BRIEF DESCRIPTION OF THE FIGURES

[0055] Additional advantages and features of the invention will be appreciated from the following description of embodiments with reference to the Figures. In the drawings:

[0056] FIG. 1 is a cross-section of a prosthesis system for an upper leg;

[0057] FIG. 2 shows another embodiment of a femur prosthesis system comprising a medullary pin;

[0058] FIG. 3 shows another embodiment of a femur prosthesis system comprising a medullary pin;

[0059] FIG. 4 shows another embodiment of the prosthesis system for a lower leg;

[0060] FIG. 5 shows another embodiment of a femur prosthesis system;

[0061] FIG. 6 shows another embodiment of a femur prosthesis system comprising a shaft;

[0062] FIG. 7 is a cross-section of another embodiment of a femur prosthesis system comprising a shaft having an external measurement system with sensors for detecting the position and loading the subcutaneous joint member of the implant;

[0063] FIG. 8 is a cross-section of another embodiment of a prosthesis system having another external measurement system which is fitted under the shaft; and

[0064] FIG. 9 is a schematic plan view of an external measurement system in the form of a counter-plate.

DETAILED DESCRIPTION OF THE FIGURES

[0065] The illustrations are schematic and are not necessarily true to scale. Furthermore, they do not show all details but are instead limited to the depiction of the inventively significant details and additional features which make it easier to explain and describe the invention. The same elements in the different Figures are indicated with the same reference numerals.

[0066] Embodiments of the invention are explained in greater detail below with reference to the drawings.

[0067] FIG. 1 shows a prosthesis system 100 in the form of an upper leg prosthesis. The upper leg 142 has an amputated femur bone 130. The sectioned surface of the bone shaft 132 is located at the distal shaft end 131. The femur head 133 is supported in the hip socket which is not shown. The femur bone 130 is surrounded by a soft part mantle 140.

[0068] The implant 101 is arranged exclusively intracorporeally, wherein the first joint member 110 is connected to the distal shaft end 131 with bone cement or in a cement-free manner. The first joint member 110 is constructed as an articular head with a convex sliding face 111. The sliding face 111 of the articular head is in contact with the sliding face 121 of the second joint member 120. The second joint member 120 can be moved around the articular head of the first joint member 110 so that the second joint member 120 can take up different positions.

[0069] At the side remote from the joint, the second joint member has an outer face 122 which is arranged subcutaneously. The outer face 122 is convex-curved and can take up pressure or weight forces. The skin can readily slide over the end portion as a result of the curvature.

[0070] The second joint member 120 has an integral end portion 124. The implant components can be constructed from different suitable implant materials. In this case, the materials may be rigid and/or flexible. A flexible construction of the radial edge region of the end portion 124 can damp impacts which occur in this region. Furthermore, the entire end portion 124 can be constructed as a shock absorber in order to be able to damp impacts which occur at the distal amputation stump end 141.

[0071] FIG. 2 shows another embodiment of a femur prosthesis system 200, wherein the first joint member 110 is anchored via a medullary pin 160 with respect to the femur bone 130. In this instance, the medullary pin 160 is introduced into the bone channel of the sectioned bone shaft 132. The connection with respect to the bone can be produced in a cement-free manner or with suitable fixing means.

[0072] The joint of the implant has a spherical sliding face 111, about which the second joint member 120 can move with three degrees of freedom. In other words, the second joint member 120 can be freely moved on the articular head of the first joint member 110. The movement is not limited until the radially peripheral edge region strikes the medullary pin 160. This movability can be further limited depending on the extent of the soft part tissue (not shown in FIG. 2).

[0073] FIG. 3 shows a femur prosthesis system 300 with a medullary pin 160, the proximal medullary pin end 162 of which has been inserted in an upper leg 142 of a patient. The proximal medullary pin end 162 can be introduced in a natural femur bone 130. The bone shaft 132 can be connected at the proximal side 132 thereof to a hip endoprosthesis (not shown). The still-intact bone shaft 132 may have a natural connection of the muscles so that movements, for example of the hips, can still be carried out.

[0074] The distal medullary pin end 161 is securely connected to the first joint member 110. Muscles still present for extending and bending the leg can be connected to the second joint member 120 at a plurality of locations in order to be able to produce inclination movements of the end portion 124.

[0075] If the end portion 124 which is located substantially perpendicularly to the medullary pin is loaded with weight after an exoprosthesis (not shown) has been connected, the second joint member 120 can tilt so that the end portion takes up a substantially horizontal position and consequently compensates for the natural oblique position of the femur bone shaft 132. However, a rigid end plate would produce pressure in the event of loading at the lowest point so that undesirable pressure sores can occur as a result of the point-like loading. If the end portion 124 is orientated substantially horizontally, the forces can be taken up by the joint member 120 in a planar manner. Since the load is distributed over the entire outer face 122, pressure sores can effectively be prevented.

[0076] FIG. 4 shows a prosthesis system 400 for a lower leg. There are schematically shown under the upper leg 142 a knee-cap 134 and adjoining low leg bones, the tibia 135 and fibula 136. The distal tibia shaft end 131 is connected to a medullary pin 160. The medullary pin can in this case be fitted in or on the distal end of the tibia because the loading is primarily transmitted via the stronger tibia bone. In the embodiment shown, the distal fibula shaft end 137 is not directly connected to the prosthesis system. The radially peripheral edge region 125 is configured in such a manner that the edge of the second joint member 120 projects beyond the fibula 136. Depending on the length of the fibula bone, the end plate may alternatively to the embodiment shown also be smaller and may not extend beyond the end of the fibula. Both an inclination and a rotation of the end plate can also be brought about here as a result of the musculature being connected.

[0077] FIG. 5 shows an upper leg stump having a prosthesis system 500, wherein the sliding face 121 has an annular projection 123 as an articular socket edge. This projection 123 can be constructed in such a manner that the articular socket of the second joint member 120 and the joint ball of the first joint member 110 form a releasable plug type connection. To this end, the projection 123 is preferably constructed in a flexible manner and/or with resilient means. After the joint ball has been snap-fitted in the articular socket, the movability of the second joint member is not limited.

[0078] FIG. 5 further shows a peripheral band 150 for fixing a shaft (not shown). The band can be constructed from skin-compatible materials, such as fabric, silicone or other suitable materials. Preferably, there are used materials which adhere to the skin in order to improve the retention. The band 150 can be tightened similarly to a bandage in order to connect a shaft to the stump in a manner which is as stable as possible.

[0079] The band further has retention projections 151 and retention recesses 152 as retention means in order to be releasably connectable to the frame construction of a shaft. There can be used as retention means conventional forms which can be brought into engagement with a corresponding counter-form in the shaft (for example, teeth, grooves). The band and the retention means are used, in engagement with the corresponding retention devices on the shaft, to produce a rotation stability of the tightened shaft.

[0080] FIG. 6 shows a frame shaft 170 for a femur prosthesis system 600. The circular band 150 shown in FIG. 5 is not shown for greater clarity of the shaft prosthesis system. The band 150 can, for example, be fixed to the retention means 152 shown in FIG. 6 on the arm 172 of the frame shaft 170. Additional arms 171 and 172 can be used to fix the shaft 170 to the band 150 (not shown) in a stable manner. Furthermore, a peripheral shaft edge 174 which can be constructed to be rigid, flexible or also partially flexible is provided for proximally fixing the frame shaft 170.

[0081] The open shaft concept with a frame construction and individual arms 171, 172 and 173 allows an exchange of air and temperature with the natural environment. This increases the wearing comfort for the user in comparison with shaft systems which are largely or completely closed. The open shaft does not limit the user in terms of his movement either as a result of material or cutting unlike conventional closed shaft systems.

[0082] A counter-plate 175 which is adapted to the outer form of the second joint member 120 is arranged in the lower region of the frame shaft. The counter-plate 175 allows a precisely fitting shaft. An optimum retention can thereby be achieved, wherein the risks of pressure sores and wound locations are reduced. This is particularly significant for the care of diabetes patients who require amputations. Furthermore, the prosthesis system can also be used in the case of bone cancer patients if a portion of a bone has to be removed. A loss of comfort as a result of a scoliotic pelvis or wear of clothing by an increased structural complexity can be generally prevented by means of the distal load transmission via the counter-plate 175 for prosthesis users.

[0083] FIG. 7 shows another embodiment of the femur prosthesis system 700, wherein the system 700 is shown as a cross-section from the side. The section is shown by a medullary pin 160 which is anchored in a femur bone shaft and/or in a hip endoprosthesis (not shown).

[0084] In the sectional view shown, muscles which are relevant for controlling the movements of an extracorporeal prosthesis (not shown) are schematically shown. Stretching muscles 143 are located at the front side of the upper leg 142 while bending muscles 144 are schematically shown at the rear side of the lower leg. These muscle groups 143 and 144 can be fixed by means of suitable retention devices or by means of holes to the radial edge region 125 of the second joint member 120. The muscles 143, 144 can be sewn, for example, to the lower side of the radial edge region 125. To this end, holes can be formed in the radial edge region 125. Depending on the muscle position, a suitable hole for connection can be selected in order to receive a muscular attachment. Alternatively or additionally to sewing, the musculature can also grow on surfaces suitable therefor or fuse with a suitable material.

[0085] The muscles can deliberately be tensioned by the prosthesis user so that an inclination of the second joint member 120 is brought about. This inclination can be detected by the measurement sensors 176. If the end plate 124 tilts, for example, by tensioning the rear muscle 144 upwards at the rear and downwards at the front, pressure is applied to the front pressure sensor 176. In this manner, the position of the second joint member 120 can be established. The detected measurement signals are forwarded via connection lines which are preferably integrated in the shaft to a control unit 180. In this manner, a bending of the knee of an extracorporeal leg prosthesis can be controlled.

[0086] The control unit 180 has at least one microprocessor and a transmission unit 182. Alternatively to a transmission unit, the signal for control can be transmitted to the control unit via a cable connection or other suitable means. The components shown are not illustrated so as to be true to scale by way of illustration and are dimensioned for use so that they can be integrated in the shaft or the exoprosthesis. On the basis of the measurement data detected, control signals can be transmitted to components of an extracorporeal prosthesis. The transmission of the measurement data can also be brought about wirelessly via conventional transmission and receiving devices instead of via signal lines 181. Conventional actuators such as valves or motors can be used for moving the controlled extracorporeal prosthesis elements.

[0087] FIG. 8 is a lateral cross-section of an additional embodiment of a prosthesis system 800 with a frame shaft 170 together with a plan view of an external measurement system which is fitted under the shaft. The measurement system is constructed in the form of a pipe element 178, wherein the pipe element 178 can receive a pin 179 which is connected to the counter-plate 175. The movement of the counter-plate 175 located in the shaft between the stump and frame can be measured by means of suitable sensors 176. As illustrated in the schematic plan view in FIG. 8, the pipe element 178 may have a plurality of measurement sensors 176.

[0088] This measurement system constitutes an alternative or additional measurement method for the movements of the end plate 124. In this case, the movement of the end plate 124 is transmitted to the counter-plate 175 which acts as an intermediate plate. The external measurement system can thereby measure the movement of a movable portion in the shaft—in this case, the counter-plate 175—and/or the loading of the prosthesis.

[0089] FIG. 8 shows a femur prosthesis system, wherein the position of the shaft edge 174 which extends round the upper thigh is schematically indicated. The femur bone 130 with the femur head 133 is located in the soft part mantle 140 of the upper leg.

[0090] The first joint member 110 is located as the articular head in the articular socket of the second joint member 120. The articular socket is delimited by the annular projection 123. Furthermore, the second joint member 120 has a radially peripheral edge region 125. The counter-plate 175 is adapted to the outer form of the subcutaneous second joint member 120.

[0091] FIG. 9 is a detailed view of an external measurement system in the form of a counter-plate 175 (cf. FIG. 7). Pressure sensors are arranged in the radial edge region of the counter-plate 175 in order to be able to detect the position or positional changes of the second joint member 120. Axial forces can be measured at the centre 177. Where applicable, an exoprosthesis can be connected via the centre 177 of the counter-plate (cf. pin 179 in FIG. 8) and where applicable signal lines can be directed to controllable components.

[0092] The invention is not limited to the embodiments shown but can instead also be used for other amputated or exarticulated limbs.

LIST OF REFERENCE NUMERALS

[0093] 100 Prosthesis system [0094] 101 Implant [0095] 110 First joint member [0096] 111 Sliding face of first joint member [0097] 120 Second joint member [0098] 121 Sliding face of second joint member [0099] 122 Outer face of end portion [0100] 123 Annular projection [0101] 124 End portion of second joint member [0102] 125 Radially peripheral edge region [0103] 130 Femur bone [0104] 131 Distal shaft end [0105] 132 Bone shaft [0106] 133 Femur head [0107] 134 Knee-cap [0108] 135 Tibia [0109] 136 Fibula [0110] 137 Distal fibula shaft end [0111] 140 Soft part mantle [0112] 141 Distal amputation stump end [0113] 142 Upper leg [0114] 143 Stretching muscles [0115] 144 Bending muscles [0116] 150 Peripheral band [0117] 151 Retention projections [0118] 152 Retention recesses [0119] 160 Medullary pin [0120] 161 Distal medullary pin end [0121] 162 Proximal medullary pin end [0122] 170 Frame shaft [0123] 171 Arm of frame shaft [0124] 172 Additional arm of frame shaft [0125] 173 Additional arm [0126] 174 Peripheral shaft edge [0127] 175 Counter-plate [0128] 176 Measurement sensors [0129] 177 Centre of counter-plate [0130] 178 Pipe element [0131] 179 Pin [0132] 180 Control unit [0133] 181 Signal line [0134] 182 Transmission unit [0135] 200 Prosthesis system with medullary pin [0136] 300 Femur prosthesis system [0137] 400 Tibia prosthesis system [0138] 500 Band for a femur prosthesis system [0139] 600 Prosthesis system with shaft [0140] 700 Additional prosthesis system with shaft [0141] 800 Additional prosthesis system with shaft