Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS 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
  • A61F2/00—Filters 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
  • A61F2/50—Prostheses not implantable in the body
  • A61F2/60—Artificial legs or feet or parts thereof
  • A61F2/64—Knee joints
  • A61F2/642—Polycentric joints, without longitudinal rotation
  • A61F2/644—Polycentric joints, without longitudinal rotation of the single-bar or multi-bar linkage type
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS 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
  • A61F2/00—Filters 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
  • A61F2/50—Prostheses not implantable in the body
  • A61F2/68—Operating or control means
  • A61F2/70—Operating or control means electrical
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS 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
  • A61F2/00—Filters 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
  • A61F2/50—Prostheses not implantable in the body
  • A61F2/68—Operating or control means
  • A61F2/74—Operating or control means fluid, i.e. hydraulic or pneumatic
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS 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
  • A61F2/00—Filters 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
  • A61F2/50—Prostheses not implantable in the body
  • A61F2/68—Operating or control means
  • A61F2/74—Operating or control means fluid, i.e. hydraulic or pneumatic
  • A61F2/748—Valve systems
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS 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
  • A61F2/00—Filters 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
  • A61F2/50—Prostheses not implantable in the body
  • A61F2/68—Operating or control means
  • A61F2/74—Operating or control means fluid, i.e. hydraulic or pneumatic
  • A61F2/741—Operating or control means fluid, i.e. hydraulic or pneumatic using powered actuators, e.g. stepper motors or solenoids
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS 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
  • A61F2/00—Filters 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
  • A61F2/50—Prostheses not implantable in the body
  • A61F2002/5003—Prostheses not implantable in the body having damping means, e.g. shock absorbers
  • A61F2002/5004—Prostheses not implantable in the body having damping means, e.g. shock absorbers operated by electro- or magnetorheological fluids
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS 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
  • A61F2/00—Filters 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
  • A61F2/50—Prostheses not implantable in the body
  • A61F2002/5007—Prostheses not implantable in the body having elastic means different from springs, e.g. including an elastomeric insert
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS 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
  • A61F2/00—Filters 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
  • A61F2/50—Prostheses not implantable in the body
  • A61F2002/5072—Prostheses not implantable in the body having spring elements
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS 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
  • A61F2/00—Filters 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
  • A61F2/50—Prostheses not implantable in the body
  • A61F2/68—Operating or control means
  • A61F2/70—Operating or control means electrical
  • A61F2002/707—Remote control
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS 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
  • A61F2/00—Filters 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
  • A61F2/50—Prostheses not implantable in the body
  • A61F2/76—Means for assembling, fitting or testing prostheses, e.g. for measuring or balancing, e.g. alignment means
  • A61F2002/7615—Measuring means
  • A61F2002/7625—Measuring means for measuring angular position

Definitions

• the invention relates to a prosthetic knee joint with an upper part which has a fastening device for receiving a leg stump, and with a lower part which is pivotally connected to the upper part by a joint device.
• the invention relates to a geriatric prosthetic knee joint, wherein geriatric patients are usually understood to mean older people who have lost a large part of their physical capacities and usually have restrictions with regard to their kinesthetic sensitivity and mental capabilities.
• prosthetic knee joints on the market that are advertised as being suitable for geriatric patients.
• all prosthetic knee joints follow the same concept, namely a simple connection of the upper part and lower part without devices for controlling the oscillation phase, with the exception of the friction that is always present, with a mechanical lock that automatically locks the knee joint in the extended position.
• the knee joint By actuating a release cable, the knee joint is unlocked and allows sitting in a bent position of the prosthetic knee joint, the position of the leg stump receiving the artificial lower leg generally being 90 °.
• a disadvantage of the above-described concept is the fact that the patient can only load the prosthesis when it is fully extended '.- _ and locked.
• the energy required to get up has to be applied through the muscles of the healthy leg, more or less supported by the shoulder and arm muscles, if walking aids or armrests can be used to get up. Adequate stability is only available when the movement is complete, i.e. when you have risen from your seat and your leg is fully extended.
• Another disadvantage is that when the knee joint is unlocked, it can immediately become unstable since the knee joint no longer offers any resistance.
• a controlled transfer to the sitting position also requires a powerful use of the healthy leg or leg muscles, which is not particularly pronounced in older patients. In practice, this means that the patient falls more or less into a sitting position.
• the object of the present invention is to provide a prosthetic knee joint which ensures improved safety for the prosthesis user.
• the disadvantages described above are to be eliminated and easy standing up and safe seating on a chair are to be made possible.
• the knee joint should be stable and lockable while standing and walking in order to provide the geriatric patient with maximum safety.
• this object is basically achieved in that a delay, in extreme cases a blocking of a movement over a certain angular range, is provided, so that an uncontrolled setting movement cannot occur or a falling back into the sitting position is avoided.
• this object is achieved in that the joint device has a resistance device which acts as a lock and which blocks flexion (pivoting of the lower part counter to the normal running direction) within a definable angular range, the lower part being freely pivotable during flexion outside the definable angular range.
• the resistance device is thus designed as a stand-up aid, which prevents the articulation device from being bent within the definable angular range.
• the knee joint can be stretched when standing up, without having to work against any appreciable resistance, however, the resistance device, which works as a locking device, continuously blocks against a flexion movement, so that the prosthesis user can gradually rise from the sitting position without running the risk of falling back into the sitting position. Instead, the prosthesis user can gradually stand up.
• the resistance device which prevents swiveling back, can also be switched over, which means that, when the knee joint is appropriately angular, a switch is made to the mode with increased resistance, which means that the body is gently lowered into the seated position Position enabled.
• the resistance device is thus designed to be switchable, and the resistance can both be reduced and increased to the level of a lock. Delaying the fallback movement to zero prevents the prosthesis user from falling abruptly and uncontrollably on the chair or on the floor.
• a locking device which locks the joint in the extended position.
• a locking device for forming a locking knee joint is usually a mechanical lock, although other constructions of a lock are also conceivable, by means of which the prosthetic knee joint is locked in the extended position, so that the prosthesis user, in particular the geriatric prosthesis user, can stand and walk safely ,
• the locking device can only be switched between the "locked” and “released”states; regulation or intermediate stages of the resistance are not provided.
• the locking device is unlocked via an actuating device and locked automatically or manually.
• the resistance device in addition to the locking device
• the effect is that when the user of the prosthesis is seated, the user is gently transferred from the standing position to the seated position without the stability suddenly being released when the knee joint is unlocked.
• the knee joint can be blocked by the locking device, possibly supported by the resistance device, and provides sufficient stability.
• the resistance device and thus the knee joint exerts an adjustable, high resistance to a flexion movement, so that the transition to a sitting position takes place gently, in a controlled manner and over a longer period of time.
• this high resistance which is exerted over a definable angular range, is automatically reduced or switched off and the knee joint can perform bending and stretching movements over a small angular range, which are usually carried out in the sitting position.
• the locking device or the resistance and locking device can be actuated in any angular position of the lower part relative to the upper part via an actuating device, which means that in any position of the knee joint a flexion movement is prevented by the locking device, but the stretching movement, that is the pivoting of the lower leg in the running direction is still possible. It is also provided that the locking device and the resistance device can be switched in any position, that is to say can also be released or reduced in resistance, so that a prosthesis user actively reduces or releases the resistance or locking in every phase of getting up or sitting down can to get into the sitting position.
• the actuating device for locking or unlocking the locking device is operated manually or by motor.
• the actuating device In order to be able to activate the actuating device also from a knee position, it has a cable pull which is coupled to the slide, to the rotary member or to a lever.
• This cable can be passed through the clothing along the thigh and can be attached relatively inconspicuously to a waistband or inside a pocket.
• the actuation device has a motor, a power supply device, a transmission and a control unit which is connected to a switch via a remote control.
• the actuating device can thus move a slide along a front articulated lever by pressing a button or a remote control and effect the locking or resistance setting, so that manual actuation of the actuating device in the region of the knee joint is no longer necessary. This is particularly advantageous for those people who cannot easily reach the knee joint.
• the manual module can be exchanged for a motor module, since the external dimensions and the mechanical couplings are preferably compatible with levers and the like.
• the remote control and the actuating device for the resistance or locking device or also in connection with the locking device can refer to all lockable knee joints and can be used in combination with these.
• Remote controls are considered in particular IR, radio or acoustic remote controls, but not a so-called “satellite” switch ", ie mechanical switches coupled to the respective device via a cable or Bowden cable.
• a delay element which is assigned to the actuating device or to the resistance or locking device, enables the prosthesis user to first unlock the knee joint in a secured position and to return to the locking or locking position after a predeterminable period of time when the Prosthesis user has not set in this period. This prevents the geriatric patient who has forgotten to unlock or was distracted from standing on an unlocked, easily movable knee joint without being aware of it. Such a condition can lead to serious injuries if, when unlocked, the prosthesis user wants to make a walking movement and bends the knee.
• the delay element ensures that the knee joint remains locked for a predetermined period of time or that a high resistance is applied.
• the user of the prosthesis can then, for example, straighten up after unlocking with a stable knee or use the hand used for actuation for support before the knee joint is initiated.
• Electronic devices such as delay circuits for motors or valves can be used as the delay element; Relays, elastic elements with rheological properties as well as circuits with actuators or mechanical delay elements can also be provided.
• dene control device In order to switch the resistance device depending on the angular position of the upper part relative to the lower part, one is connected to the upper part. dene control device, preferably provided mechanical control device which is coupled to the resistance device. In this way it is achieved with simple means that a corresponding resistance is provided within a predetermined angular range.
• the resistance device is advantageously designed as a hydraulic or pneumatic unit, a friction clutch or an electromagnetic clutch in order to provide a controllable resistance.
• One embodiment of the invention provides that in a configuration as a hydraulic or pneumatic unit there is a controllable valve system which is arranged within a piston guided in a cylinder.
• the piston forms part of the resistance device.
• the combination and arrangement of the valve system within the piston results in a particularly compact design, with the valve system being connected to the mechanical control device for cost-effective implementation of the prosthetic knee joint, which, depending on the angular position of the upper part to the lower part, switches the resistance device in such a way that via a certain angular range there is increased resistance. If this angular range is exceeded, there is no longer any resistance to a further bend in the running direction, with bending being able to be prevented at any time by appropriate locking means, on the other hand an unimpeded stretching against the running direction is possible at any time.
• This control device is arranged around the axis of rotation which is formed by the upper part and the piston rod attached to it, which enables a particularly simple assignment of the control device to the piston rod and the control rod guided therein.
• the control device has a first cam, which acts on the control rod and is connected in a rotationally fixed manner to the upper part or, alternatively, is carried along via a driver which is fastened to the upper part, the first cam being connected in an angle-dependent manner via the driver or the drivers becomes. If the first cam is rotatably mounted on the upper part, at least one driver which is effective in the bending direction is required, which rotates the cam when a certain bending angle is reached in such a way that a valve is opened so that the knee joint can move freely without resistance.
• a prosthetic knee joint with an upper part, which has a fastening device for receiving a leg stump, and a lower part, which is pivotally connected to the upper part via a joint device, and with a locking device for locking the prosthetic knee joint in the extended position, the locking device being provided by a loading device.
• Actuating device can be locked and unlocked, has an actuating device which is controlled via a remote control for easier operability.
• the remote control and the remote control and the actuating device for the locking device can relate to all lockable knee joints and can be used in combination with these.
• Remote controls are considered to be wireless, in particular IR, radio or acoustic remote controls, but not a so-called “satellite switch”, that is to say switches coupled to the respective device via a cable.
• a delay element is assigned to the locking device according to the invention, which unlocks or locks the locking device after the actuation of the unlocking.
• the delay element can be designed as a relay, as an elastic or rheological element or as an electronic circuit with an actuator.
• Figure 1 - a side view of a prosthetic knee joint according to the invention with mounted thigh receptacle and artificial lower leg;
• Figure 2 is an enlarged view of Figure 1 without the thigh
• Figure 3 - a partial sectional view of Figure 2;
• FIG. 4 shows an individual part of a front joint part
• FIG. 5 shows an individual part of an upper part
• FIG. 6 shows an individual part of a lower part with an assembled artificial lower leg
• Figure 7 is a partial representation of a hydraulic piston with piston rod
• Figure 8 is a sectional view of a prosthetic knee joint according to the invention with a joint device;
• Figure 9 is an enlarged view of a resistance device;
• Figure 1 - a partial representation of a secondary valve
• Figure 15 - a partial sectional view of the valve system
• FIGS 16 and 17 an isolated representation of a control rod with an adjusting device for the auxiliary valve
• Figure 18 an enlarged view of the prosthetic knee joint with the upper part, lower part, the resistance device and the front joint part;
• Figure 19 a detailed representation of the actuating device for the control rod
• Figure 20 - a representation of a first cam in the unswitched state
• Figure 21 - a representation according to Figure 20 with the control rod actuated
• Figures 22 and 23 the arrangement of a second cam and a rotary member
• Figure 24 the mechanical coupling of the actuator with the rotary member and the cam
• FIG. 25 shows a representation according to FIG. 24 in a switched state in which the auxiliary valve is open
• Figures 26 and 27 - an arrangement of an actuating cable on the actuating device
• FIGS. 30 to 32 state representations of the mechanical control as a function of the diffraction angle
• Figure 33 is an exploded view of the front link and actuator
• Figures 35 and 36 representations of the knee joint with a motor-driven actuating device
• Figure 37 two overall views of the prosthetic knee joint in different angular positions; and Figure 38 shows an embodiment of a delay element.
• FIG. 1 shows a prosthesis knee joint 1 according to the invention, which has an upper part 10 and a lower part 20, the upper part 10 being pivotally connected to the lower part 20 via a joint device.
• This hinge device has a front hinge lever 40 which is rotatably fastened to both the upper part 10 and the lower part 20.
• a resistance device 30, which is designed as a hydraulic cylinder device, prevents an uncontrolled flexion movement of the lower part 20 against the normal, that is to say forward, running direction with respect to the upper part 10 and at the same time serves as a rear joint part.
• the design of the joint device has the effect that a large part of the load when walking or standing, which is exerted by the prosthesis user on the prosthetic knee joint 1, is introduced via the resistance device 30 into the lower part 20 and above into an artificial lower leg 200.
• a corresponding receptacle 25 is formed at the lower end of the lower part 20.
• the lower part 20 and the artificial lower leg 200 can be formed in one piece and optionally equipped with an artificial foot.
• a receptacle 100 for the leg stump is attached to the upper end of the upper part 10, the receptacle 100 being able to be fastened to the upper part 10 via a fastening device 11, which is shown in FIG.
• the prosthetic knee joint 1 has an actuating device 50 which is arranged and designed on the front articulated lever 40 in a manner similar to a patella.
• the actuating device 50 is slidably mounted on the front articulated lever 40, the function being described below.
• the front articulated lever 40 is rotatably mounted on a bearing block 21 of the lower part 20.
• the articulated lever 40 is likewise rotatably mounted on a front section 14 of the upper part 10, whereas the resistance device 30 is rotatably arranged on a rear section 13 of the upper part 10 in the forward running direction.
• FIG. 3 shows the prosthetic knee joint 1 in a partial sectional view, in which the design of the resistance device 30 with a hydraulic piston 30 ′ can be seen, which is connected to the upper part 10 via a piston rod 31.
• the piston 30 'moves within a cylinder 26 which is formed by the guide 23.
• the guide 23 is formed as a cylinder wall and forms an integral part of the lower part 20.
• At the lower end of the cylinder 26 there is a closure device, via which the cylinder 26 can be filled with a hydraulic fluid.
• FIGS. 4 to 7 Individual parts of the joint construction are shown in FIGS. 4 to 7, the front joint part 40 being shown in FIG. 4, which is designed as a joint lever with two axes of rotation.
• 5 shows the upper part 10 with the fastening device 11 for receiving a leg stump; the upper part 10 has two receptacles for axes of rotation to be able to rotatably accommodate the resistance device 30 and the front joint part 40.
• FIG. 6 shows a lower part 20 with the receptacle 25 for the artificial lower leg 200, the lower part being essentially tubular, on which a front bearing block 21 is formed or fastened.
• the component shown in FIG. 7 forms the resistance device 30, the component consisting of a piston rod 31 and a piston 30 '.
• a bore is formed at the upper end of the piston rod 31, so that the piston rod 31 can be rotatably supported in the rear section 13 of the upper part 10.
• FIG. 8 shows an alternative structure of the joint device, in which the upper part 10 is arranged in an articulated manner directly on the bearing block 21, and the piston rod 31 is connected to the rear section 13 of the upper part via a rear articulated lever 12.
• FIG. 9 shows a cross section through the lower part 20, so that the function of the resistance device is visible.
• the outer wall 23 of the lower part 20 is cylindrical and forms a cylinder cavity 26 in which the piston 30 'is axially displaceably guided.
• the piston 30 ' is designed as a conventional hydraulic piston which is axially subjected to a force via the piston rod 31.
• a controllable valve system 60 is arranged centrally within the piston 30 'and is switched via a control rod 76 guided centrally in the piston rod 31. The switching takes place in that the valves of the valve system 60 are loaded in the axial direction.
• FIG. 9 shows a cross section through the lower part 20, so that the function of the resistance device is visible.
• the outer wall 23 of the lower part 20 is cylindrical and forms a cylinder cavity 26 in which the piston 30 'is axially displaceably guided.
• the piston 30 ' is designed as a conventional hydraulic piston which is axially subjected to a force via the piston rod 31.
• the valve system 60 has a main valve 61 which is designed as a check valve and is arranged within the piston 30 'in such a way that an upward movement of the piston 30' and thus the piston rod 31 is always possible, but a lowering of the piston 30 'down is prevented.
• the piston 30 ' is shown on an enlarged scale.
• the control rod 31 does not push the main valve 61 down, so the valve 61 prevents the piston 30 'from moving downward, but allows the piston 30' to move upward, because the holes 32 carry hydraulic oil from the upper chamber to the lower one Chamber can flow freely.
• FIG. 11 shows the switched state of the main valve 61, that is to say that hydraulic fluid can flow from the lower chamber into the upper chamber through the bores 32, so that the piston 30 'can move downward.
• the valve 61 enables the piston 30 'to move freely in both directions, which means that the knee joint can move freely.
• FIG. 12 shows a sectional illustration of the valve system 60, in which it becomes clear that a similarly constructed secondary valve 62 is arranged within the main valve 61.
• the principle of operation corresponds to Chen that of the main valve 61; in the position according to FIG. 12, the control rod 76 does not actuate either the main valve 61 or the secondary valve 62, so that both valves 61, 62 block the downward movement of the piston 30 'and thus a deflection.
• the main valve 62 allows passage from the upper chamber into the lower chamber, so that stretching is possible at any time.
• the control rod 76 has two shoulders 761, 762 which are assigned to the respective valves 61, 62.
• the shoulders 761, 762 are axially offset from one another, the second shoulder 762 engaging with the secondary valve 62 earlier than the first shoulder 761 with the main valve.
• FIG. 13 shows a state in which the auxiliary valve 62 is switched, that is, opened, via the control rod 31. Due to the lower maximum flow rate through the auxiliary valve 62, while the auxiliary valve 62 is open, a downward movement of the piston 30 'and thus a flexion of the knee joint is made possible, but only with a high resistance, which leads to a smooth, time-delayed movement and damping, which leads to a controlled lowering of the body from a standing to a sitting position.
• the liquid flow is indicated by the arrows and leads along a valve plate 63, a valve stem 64 and through corresponding bores into the upper cylinder chamber.
• FIG. 14 shows the secondary valve 62 in an individual representation, the left figure representing a complete secondary valve 62 which has a valve disk 63 and a valve stem 64.
• the right-hand illustration of FIG. 14 shows the cross section of the valve stem 64, which is oval in shape.
• a flattened portion is formed, which is designed for a rotationally fixed coupling with the control rod 76.
• valve stem 64 has a non-rotationally symmetrical cross section.
• the valve 62 is guided in a round valve guide inside the main valve 61 and by simply turning the valve stem 64 it is possible to adjust the flow rate which is passed through the secondary valve 62 by limiting the flow rate by reducing the flow cross section.
• This rotation of the auxiliary valve 62 advantageously takes place via the control rod 76, which is shown in FIGS. 16 and 17, namely via an adjusting wheel 77, which adjusts the control rod 76 in the region of the piston rod receptacle.
• FIG. 18 shows the overall structure of the joint device with the upper part 10, the lower part 20, the front joint part 40 and the resistance device 30.
• the front joint part 40 is rotatably mounted on the upper part 10 and the lower part 21 via an upper axis of rotation 17 and a lower axis of rotation 18.
• the piston rod 31 is rotatably mounted on the rear section 13 of the upper part 10 via the axis of rotation 15; the piston rod 31 itself is guided axially displaceably within the lower part 20.
• FIG. 19 shows a pivotally mounted pressure lever 78 which is arranged above the end of the control rod 76.
• the pressure lever 78 is pivotally mounted on the piston rod 31 below the axis of rotation 15 and has a cylindrical support body, the axis of which is parallel to the axis of rotation of the pressure lever 78. It is thereby achieved that the cam valve 71, as shown in FIG. 20, precisely controls the secondary valve 62 and, if appropriate, the main valve 61.
• FIG. 20 shows how the cam disk 71 is connected in a rotationally fixed manner to the upper part 10 and extends above the pressure lever 78.
• the control rod 76 is in the upper position, which represents the normal position, since due to the load when standing, hydraulic pressure always acts against the check valves 61, 62.
• the cam plate 71 Only when a predetermined angle has been reached, as shown in FIG. 21, does the cam plate 71, by means of a projection formed therein, cause the control rod 76 to be pressed down and thereby firstly the auxiliary valve 62 and then the main valve 61 to open.
• the angle is 70 °, which the upper part 10 has to be pivoted to the lower part 20 until the first cam plate 71 presses the control rod 76 downward and thereby opens the valves 61, 62.
• the knee joint can move freely, which is advantageous for a prosthesis user in the sitting position.
• the first cam plate 71 is a first element of a control device 70, which makes it possible in connection with the valve system 60 to always allow a free extension of the lower part 20 and, at the same time, it is always possible to bend freely above a defined angular range in order to achieve a comfortable To allow sitting. Furthermore, by ensuring that there is a lock against the bending direction when the resistance device 30 is not open and the specified angular range is not exceeded. On the other hand, a controllable, relatively high resistance to diffraction in an open state of the secondary valve is possible in order to enable the change from the standing to the sitting position in a safe and controlled manner.
• FIG. 22 A further device of the control device 70 is shown in FIG. 22 in the form of a second cam plate 72, with which it is possible to actuate the control rod 76 in such a way that the auxiliary valve 62 is open and can thus be switched to the increased resistance mode.
• the second cam plate 72 also acts on the pressure lever 78, but is arranged in FIG. 22 such that the auxiliary valve 62 is not switched.
• the second cam plate 72 is connected via a lever 52, which is rotatably mounted on the cam plate 72, to a rotary member 51, which is mounted on the front axis of rotation 17. By rotating the rotary member 51, the second cam disk 72 is rotated via the lever 52 and a projection presses the control rod 76 downward and activates the auxiliary valve 62, which is shown in FIG. 23.
• the actuating device 50 is designed in the form of a patella, which is connected to the rotary member 51 via a further lever 53.
• FIG. 24 shows the combination of the displaceable actuating device 50 with the levers 52, 53 and the rotary member 51; in the position according to FIG. 24, the actuating device 50 is in a lowered position, which means that the rotary member 51 is rotated to the maximum counterclockwise and in the present lever arrangement the second cam 72 is also rotated counterclockwise at most. If the actuating device 50 is shifted upward, as shown in FIG. 25, the rotary member 51 rotates in the clockwise direction and likewise the second cam disk 72. This has the effect that the projection formed on the second cam disk 72 acts on the pressure lever 78 and that Control rod 76 presses down, whereby the auxiliary valve 62 is switched, that is, opened and thus a gentle lowering from the standing to the sitting position is made possible.
• an actuation cable 55 is provided, which can be guided upwards from the knee, so that the mode can be set by pulling the actuation cable 55, which is arranged on a lever 53 in the present exemplary embodiment , in which a gentle bending is made possible.
• the actuating cable 55 can also be arranged on the rotary member or on the actuating device 50 itself. The entire knee joint is shown in plan view in FIG. 27, together with the actuating cable 55.
• FIGS. 28 and 29 show a sectional illustration of the actuating device 50 which is displaceably mounted on the front joint part 40 and which has a locking element 56 which is spring-loaded and can engage in a recess 46 which is formed on the front joint part 40. If the actuating device 55 is raised, as shown in FIG. 29, the locking element 56, which is designed here as a ball, snaps into the recess 46 in a form-fitting manner and holds the actuating device 50 in the upper position. This means that the secondary valve 62 remains open via the second cam 72 thus when the actuating device 50 is actuated once, the resistance remains the same for the entire process of settling.
• the auxiliary valve 62 remains closed in the lowered position of the actuating element 50, a locking device being formed via the levers 52, 53, the rotary member 51 and the control rod 70, which prevents the knee joint from flexing due to the blocking of the hydraulic flow.
• the prosthesis user can always stretch the knee joint, but without the risk of the joint bending away in an uncontrolled manner.
• the embodiment can thus be used as a stand-up aid and as a sitting-down aid for geriatric patients
• the auxiliary valve 62 is provided when the angle, which allows free movement of the knee joint due to the opening of the main valve is closed. This is done in that a driver 19 is arranged on the upper part 10, which rotates the rotary member 51 counterclockwise from a certain angle and thereby moves the actuating device 50 via the lever 53 from the locked, upper position to the unlocked, lower position.
• a driver 19 is arranged on the upper part 10, which rotates the rotary member 51 counterclockwise from a certain angle and thereby moves the actuating device 50 via the lever 53 from the locked, upper position to the unlocked, lower position.
• the rotary member 51 is rotated counterclockwise above the driver 19 above a fixed knee angle, which leads to the lever 53 pushing the actuating device 50 downward and thereby unlocking the actuating device 50.
• the driver 19 is fixedly attached to the upper part 10 and guided in a guide of the rotary member 51.
• two return springs 57 are provided within the actuating device 50, as shown in FIGS. 33 and 34 ,
• the return springs 57 are mounted within recesses on the back of the actuating device 50 and are supported on the front joint part 40 by means of corresponding pins.
• a safe guiding of the actuating device 50 is ensured by a central slot, in which a projection engages, which is formed on the rear side of the actuating device 50.
• FIGS. 35 and 36 An alternative embodiment of the actuating device 50 is shown in FIGS. 35 and 36, in which the actuating device 50 is motor-driven and is preferably activated or deactivated via a remote control.
• a motor 510, an energy storage device 520, a transmission 530 and a control unit 540 are provided within the actuating device, by means of which the actuating device 50 can be moved upwards or downwards.
• the rest of the mechanical see connection of the actuating device via levers 52, 53, rotary member 51 and cams 72, 71 is as described above, so that reference is made to this. Due to a modular design and compatibility of the manual and the motor-driven actuating device 50, a variant can be selected depending on the need or indication.
• the activation of the actuating device 50 via a remote control can also be used for other locking knee joints that do not have a stand-up and sit-down aid.
• the remote control enables the locking or locking to be unlocked with a minimum of effort in a posture that appears most secure to the prosthesis user, without having to reach for the knee or release a hand from a walking aid, for example.
• FIG. 37 shows two overall views of the prosthetic knee joint in different angular positions, which shows the compact structure and the large pivoting range of the lower part 20 relative to the upper part 10.
• the advantages of the prosthesis according to the invention are that by activating the actuating device, be it manually or by motor, the prosthesis user can switch from a locked state of the knee joint to a movable state, the mobility being designed such that an essentially constant, relatively high resistance to diffraction is applied, so that a controlled, smooth and slow movement from standing to sitting is made possible.
• the actuation can take place either in the area of the prosthetic knee joint or by pulling an actuation cable, so that the actuation and thus switching into the mode with a high resistance is inconspicuously possible.
• the lock can be released at any time by the prosthesis user and switched to the mode of increased resistance to diffraction. Conversely, locking against flexion of the prosthetic knee joint can be effected by the prosthesis user at any time.
• the articulated device Due to the integration of the hydraulic cylinder in the lower part as an integral, load-bearing part, the articulated device has the advantage of the compact design, which saves weight as well as installation space. It is not necessary to mount a separate cylinder, and the resistance device in the form of an integrated hydraulic cylinder also acts as a load-bearing component.
• FIG. 38 shows an exemplary embodiment of a delay element 384/385/386 of a locking device, which in the form of a satellite switch represents a time delay in the unlocking.
• FIG. 38 shows an actuating cable 55 connected to the locking mechanism of the knee joint, which is firmly connected to a handle 382 at the end remote from the joint.
• a spring support 384 is also firmly connected to the actuation cable 55.
• the handle 382 is slidably mounted on a base plate 381, the base plate 381 forming a housing 383 for receiving both the actuation cable 55 and the spring support 4.
• a spring device 385, 386 is arranged in the housing 383, the base plate being fixed with a resilient structure, such as. B. a shaft of a prosthetic leg is bound.
• the rheological spring element 385 By pulling the actuating cable 55 over the handle 382, the rheological spring element 385, for. B. a pronounced viscoelastic elastomer, loaded under pressure and holds the operating cable 55 even after releasing the operating handle 382 for a certain time in the pulled position.
• One or more spring elements 386 with possibly different spring properties support the effect of the rheological spring element 385 and / or allow an advantageous adjustment of the function or facilitate assembly by prestressing.
• there is a time-delayed resetting of the actuation cable 55 This time delay can be used for a user-friendly and therefore hazard-free switching of the knee joint.
• the operating hand After pulling the actuating cable 55, the operating hand can be used again for a function that supports the movement sequence and the knee joint can thus be unlocked in a more delayed and controlled manner.

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• Health & Medical Sciences (AREA)
• Transplantation (AREA)
• Biomedical Technology (AREA)
• Cardiology (AREA)
• Oral & Maxillofacial Surgery (AREA)
• Engineering & Computer Science (AREA)
• Heart & Thoracic Surgery (AREA)
• Vascular Medicine (AREA)
• Life Sciences & Earth Sciences (AREA)
• Animal Behavior & Ethology (AREA)
• General Health & Medical Sciences (AREA)
• Public Health (AREA)
• Veterinary Medicine (AREA)
• Orthopedic Medicine & Surgery (AREA)
• Prostheses (AREA)

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• 2003
  • 2003-11-07 DE DE10351916A patent/DE10351916A1/de not_active Ceased
• 2004
  • 2004-11-04 EP EP04802682A patent/EP1699391A2/de not_active Withdrawn
  • 2004-11-04 AU AU2004286759A patent/AU2004286759A1/en not_active Abandoned
  • 2004-11-04 CN CNA200480040062XA patent/CN1901857A/zh active Pending
  • 2004-11-04 JP JP2006538646A patent/JP4625015B2/ja not_active Expired - Fee Related
  • 2004-11-04 CA CA002544901A patent/CA2544901A1/en not_active Abandoned
  • 2004-11-04 US US10/595,720 patent/US20070083272A1/en not_active Abandoned
  • 2004-11-04 RU RU2006119915/14A patent/RU2006119915A/ru not_active Application Discontinuation
  • 2004-11-04 KR KR1020067011026A patent/KR20060130059A/ko not_active Application Discontinuation
  • 2004-11-04 WO PCT/DE2004/002456 patent/WO2005044155A2/de active Application Filing

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