DE102015207832A1 - Joint device for a hinge insert in bodies of living beings, in particular humans, for the endogenous support or replacement of natural joint movements and artificial joint - Google Patents

Abstract

In order, if natural joint movements only limited or no longer work, e.g. By paralyzing the muscular functions to improve and optimize the support or replacement of these natural joint movements over known joint prosthesis, and preferably so far that an additional increase in performance can be achieved, a hinge device (GV) is used for a hinge insert in bodies of living beings, especially humans , proposed for endogenous support or replacement of natural joint movements and an artificial joint in which an active endogenous joint movement is generated to assist or replace the anatomical, body-own joint movements. In particular, through the miniaturization of sensors and electromagnets, it is possible to make Artificial Joints "active", i. A joint device (GV) forming a joint functional unit in the body of the living being with joint bones of the natural joint produces an active endogenous joint movement based on electromagnetic force exerted on joint bones which supports or replaces the natural joint movement.

Description

Joint device for a hinge insert in bodies of living beings, in particular humans, for the endogenous support or replacement of natural joint movements and artificial joint

The invention relates to a joint device for a joint insert in bodies of living beings, in particular humans, for the endogenous support or replacement of natural joint movements according to the preamble of patent claim 1.

Numerous groups of people today need artificial joints. There are multiple reasons for that. In particular, by osteoarthritis, the most common of all joint diseases, arises in many cases, the need to replace joints with an implant. Most affected are hands, knees and hips, but all other joints can be affected. More than three million people already have an artificial joint in Germany alone. About 200,000 artificial hip joints, 150,000 artificial knee joints and 12,000 artificial shoulder joints are used annually [cf. http://www.arthrose.de/arthrose/haeufigkeit.html ].

Other causes may be congenital or acquired deformities, rheumatic diseases or more rare diseases such as hemophilia, gout or necrosis [ see. http://www.asklepios.com/orthopaediehamburgwest_Kniegelenk.Asklepios ]. Weight-bearing joints such as hip or knee joints are the most frequently affected [cf. http://www.arthrose.de/arthrose/haeufigkeit.html ].

However, artificial joints are not only a relief, quality of life and alternative or supplement to the natural joint for certain groups of people, but can generally be used in the bodies of living things.

All artificial joints or joint prostheses currently function "passively", i. they replace the natural joint mechanism, while the artificial joint mechanism of the artificial joint continues to be moved by the body's own muscles.

A typical joint prosthesis in the human knee is on the web page http://www.apotheken-umschau.de/multimedia/15/51/89/6208544785.jpg shown. The web page illustration shows the basic structure of a knee joint prosthesis without support.

In the classical joint prosthesis, both the tibia and the femur are each a joint piece, preferably made of metal (but it can also be used other materials with comparable properties in terms of Abriebfestig- and stiffness, are used), mounted in a suitable form to the joint and anchored. A first joint piece, preferably in the case of the knee joint designed as a joint roller, is thereby attached to the foot of the femur. A second joint, preferably in the case of the knee joint formed as a metal plateau, is thereby anchored on the tibial head of the tibia. Between the two joint pieces or the joint roller and the metal plateau is designed as a sliding surface, to the joint roller and the metal plateau formally adapted and the damping and friction behavior for the knee joint movement material optimally designed slider to facilitate the movement. The movement of the knee joint is achieved (although not explicitly shown in the web pages illustration) exclusively by muscle power.

Against this background of the "passive" functioning of the articulation mechanism of today's artificial joints, the research and practical application of artificial joints focuses on the improvement and further development of these "passive" joint mechanisms, e.g. in such a way as to increase their lifespan and to render unnecessary medical-surgical interventions for the replacement of the artificial joints.

A further focus has been on the development of external support and movement structures, so-called exoskeletons, which have been used in particular in paralyzed people, in the industrial sector and in the armaments-related area.

Examples of medical use include the "ReWalk Exosklett" [cf. http://www.rewalk.com/de/ ], "eLEGS" by Berkeley Bionics [cf. http://www.exoskelette.com/berkeley-bionics.html ], the "HAL Exosklett" [cf. https://www.youtube.com/watch?v=_Jq2zr5tauA ] or "REX Bionics" [cp. http://www.rexbionics.com/ ].

Examples from the military area are the "Lockheed Hulc" [cf. http://www.lockheedmartin.com/us/products/hulc.html ] or the "X-OS 2" from Raytheon [ see. http://www.army-technology.com/projects/raytheon-xos-2-exoskeleton-us/ ].

Examples of industrial applications include the "Panasonic Power Loader" [cf. http://www.cnet.com/news/panasonic-working-on-actual-alien-power-loader/ ].

The big disadvantage of previous exoskeletons is that they have a high weight, are very bulky and thus restrict the freedom of movement. In addition, exoskeleton forces act only indirectly from the outside and not directly within the joint.

The object underlying the invention is to provide a hinge device for a hinge insert in living bodies, in particular humans, for the endogenous support or replacement of natural joint movements and an artificial joint in which, when the natural - i. the anatomical, body-own - joint movements only limited to no longer work, e.g. by paralysis of the muscular functions, the support or replacement of the natural joint movements over known joint prosthesis is improved and optimized, and preferably so far as to allow an additional increase in performance.

This object is achieved on the basis of the device defined in the preamble of claim 1 by the features specified in the characterizing part of claim 1.

In addition, the object is achieved by an artificial joint according to the patent claim 11.

The idea underlying the invention is to provide a hinge device for a hinge insert in bodies of living beings, in particular humans, for the endogenous support or replacement of natural (ie anatomical, body-own) joint movements and an artificial joint, in or for the support or replacing the anatomical, body-own joint movements an active endogenous joint movement is generated. Such an "active" designed device and such an "active" designed artificial joint in which natural movements are supported or completely replaced could be particularly helpful in patients (human and animal) whose muscular functions are severely limited ( eg by paralysis), but also in non-restricted patients or exoskeletons lead to enormous performance increases (eg military, industrial applications).

• a. Eine Gelenkprothese mit Prothesestücken, die mit Gelenkknochen des natürlichen Gelenkes verbunden wird bzw. werden;
• b. Ein erstes Prothesestück mit einer in Bezug auf den zugeordneten Gelenkknochen diametralen, im Wesentlichen in Längsrichtung des Gelenkknochens ausgeprägten Magnetisierung;
• c. Ein zweites als ein Miniatur-Elektromagnet ausgebildetes Prothesestück mit einer in Bezug auf den zugeordneten Gelenkknochen im Wesentlichen in axialer Richtung Elektro-Magnetisierung, der mit dem ersten Prothesestück die elektromagnetische Kraft ausübt und vorzugsweise (vgl. Anspruch 8) zur Elektrizitätsversorgung, z.B. Stromversorgung, mit einer primär- oder sekundärzellenbasierten Batterie verbindbar ist (diese Versorgung kann entweder körperendogen oder körperexogen erfolgen);
• d. eine Steuerungseinheit zur körperendogenen und/oder körperexogenen Ansteuerung des Miniatur-Elektromagneten;
• e. ein Gleitelement als Gleitfläche der Prothesestücke bei der aktiven, endogenen Gelenkbewegung.

To facilitate the movement of joints in living bodies, an artificial joint (alternative to previously known artificial joints) is proposed, preferably for the knee of humans and / or animals. In particular, through the miniaturization of sensors, it is possible to make artificial joints "active", ie it is an active, based on electromagnetic exercise in joint bone endogenous joint movement generated by a natural joint bone joint function unit forming joint device that supports the natural joint movement or replaced. The proposed joint device contains for this purpose according to claim 1 the following components

• a. A joint prosthesis with prosthetic pieces that is connected to joint bones of the natural joint;
• b. A first prosthesis piece with a diametrical in relation to the associated joint bone, substantially pronounced in the longitudinal direction of the joint bone magnetization;
• c. A second designed as a miniature electromagnet prosthesis piece with respect to the associated joint bone substantially in the axial direction of electro-magnetization, which exerts the electromagnetic force with the first prosthesis piece and preferably (see claim 8) for electricity supply, eg power supply, with can be connected to a primary or secondary cell-based battery (this supply can be either body endogenous or exogenous to the body);
• d. a control unit for body-endogenous and / or body-exogenous control of the miniature electromagnet;
• e. a sliding element as a sliding surface of the prosthetic pieces in active, endogenous joint movement.

• 1) Die Bewegung von Lebewesen (z.B. Mensch oder Tier) mit Bewegungseinschränkung wird erleichtert.
• 2) Im industriellen oder militärischen Umfeld kann durch eine solche Vorrichtung eine deutliche Einsparung an Muskelkraft und somit eine längere Ausdauer erreicht werden.
• 3) Im Vergleich zu den eingangs erwähnten exogenen Lösungen (z.B. Exoskeletten) ist die vorgeschlagene Gelenkvorrichtung, gegebenenfalls mit Ausnahme der Stromversorgung, nicht sichtbar.

The main advantages of the proposed artificial joint with the hinge device provided therefor are:

• 1) The movement of living beings (eg human or animal) with movement restriction is facilitated.
• 2) In industrial or military environment can be achieved by such a device a significant saving in muscle strength and thus a longer endurance.
• 3) Compared to the exogenous solutions mentioned at the outset (exoskeletons, for example), the proposed joint device, if appropriate with the exception of the power supply, is not visible.

Advantageous developments are specified in the subclaims.

Further advantages of the invention will become apparent from the following description of a preferred embodiment of the invention from the variety of possible embodiments [eg for different joint shapes in living things, especially humans, (eg ball joint, ellipsoid joint, saddle joint, hinge joint, rolling, wheel or pivot joint, swivel and / or condyle joint) and / or other physical engineering modes of active support / replacement of the natural joint mechanism] human knee joint (condylar joint) according to the 1 to 6 , These show:

1A and 1B (Prior art) based on the presentation and description on the web page http://www.cpk-kempten.de/kniegelenk.html as well as in the form of a side view ( 1A ) and a sectional view of 1A ( 1B ) the structure and function of a knee joint (of man).

2A and 2 B starting from the 1A and 1B the construction of an artificial knee joint with a schematically illustrated joint device for endogenous support or replacement of natural (ie, anatomical, endogenous) knee joint movements.

3 based on the presentation on the web page http://www.heilberufe-ausbildung.de/Knochen_Gelenke/Knochen.htm the principal mode of action and the use of the artificial knee joint with the joint device according to the 2A and 2 B in a human body for endogenous support or replacement of natural knee joint movements.

4 the basic structure and the articular knee joint arrangement-specific principle realization of an electromagnetically based concept of the joint device according to 3 for endogenous support or replacement of the natural knee joint movements.

5A . 5B and 5C starting from the 4 the electromagnetically based endogenous support of the knee during a movement (first direction of movement) from a neutral knee joint position (180 ° position; 5A ), via a weakly angled knee joint position (eg 160 ° position; 5B ) into a slightly angled knee joint position (eg 120 ° position; 5C ).

6A . 6B and 6C starting from the 4 and the scenario in the 5A to 5C the electromagnetically based endogenous support of the knee during a movement (second direction of movement, opposite to the first direction of movement) from the middle-slightly angled knee joint position (eg 120 ° position; 6A ;), via the weakly angled knee joint position (eg 160 ° position; 6B ) in the neutral knee joint position (180 ° position; 6C ).

In other words, the embodiment of the invention described below can be explained in any way to other conceivable embodiments, e.g. the alternatives indicated above apply.

1A and 1B (State of the art) show based on the presentation and description on the web page http://www.cpk-kempten.de/kniegelenk.html as well as in the form of a side view ( 1A ) and a sectional view of 1A ( 1B ) the structure and function of a knee joint KG (by humans). The human knee joint KG is composed of two partial joints, a patellar joint KSG and a popliteal joint KKG. The knee joint GK belonging to the knee joint KG are a kneecap KS, a femur OSK, a tibia SBE and a fibula WBE. The patella KS and the femur OSK form the patellar joint KSG, while the femur OSK and the tibia SBE form the popliteal joint KKG. Characteristic for both partial joints KKG, KSG of the knee joint KG is that between the femur OSK and the patella KS and between the femur OSK and the tibia SBE each have a joint surface GFL consisting of a covered with a cartilaginous layer KPS articular process GFS at the foot of the femur OSK, on the joint-facing side of the patella KS and the tibial head of the tibia SBE is formed.

Another special feature of the knee joint KG is that in the popliteal fossa between the articular surfaces GFL of the thigh bone OSK and the tibia SBE still another cartilage structure is present, which is referred to as meniscus MK. The meniscus MK consists as shown in the 1B from an inner meniscus IMK and an outer meniscus AMK. During the movement of the knee joint KG, the joint surfaces GFL formed in the partial joints KSG, KKG slide and roll relative to one another.

While in the patella joint KSG by fitting the kneecap KS in thigh muscles OSM and a patella band KSB as a lower extension of the thigh muscles OSM the articular surfaces GFL of the patella KS and the femur OSK more or less accurately fit, such a precisely juxtaposed facing the articular surfaces GFL of the femur OSK and the tibia SBE in the popliteal joint KKG not given. Without the meniscus MK or the menisci IMK, AMK between the articular surfaces GLF of the thigh bone OSK and the tibia SBE, an uneven pressure distribution between the joint bones GK would exist quite generally, and in particular during the sliding and rolling movement of the articular surfaces GLF. However, the meniscus MK in the popliteal joint KKG usually eliminates it.

In addition to establishing a uniform pressure distribution between the joint surfaces GFL, the meniscus MK, IMK, AMK additionally serves as a shock absorber when the popliteal joint KKG or the knee joint KG is loaded, in particular by movement of the human body. In addition, the meniscus MK, IMK, AMK contributes to the stabilization of the popliteal joint KKG and thus of the knee joint KG as a whole. For the stabilization of the knee joint KG, in addition to the meniscus MK or the menisci IMK, AMK, the musculature surrounding the knee joint KG as well as several ligaments besides the already mentioned patellar ligament KSB are responsible. These bands include in particular - as in the 1B an inner band IBA, an outer band ABA and cruciate ligaments KRB. In the sectional view of the knee joint KG in the 1B Of the two existing in the knee joint KG cross bands KRB only a front cruciate ligament VKRB is shown, while a posterior cruciate ligament is not visible through the sectional view. The cruciate ligaments KRB are located in the middle of the knee joint KG and are respectively attached to the thigh bone OSK and the tibia SBE.

2A and 2 B show starting from the 1A and 1B the construction of an artificial knee joint KÜKG with a schematically illustrated joint device GV for endogenous support or replacement of natural (anatomical, endogenous) knee joint movements. The Artificial Joint KÜKG differs in the present case of the natural knee joint KG in the 1A and 1B in that due to the provided for the artificial knee joint KÜK in the popliteal joint KKG joint device GV on the femur OSK part (except the part of the femur OSK is the knee joint joint KSG heard) designed as a joint surface GFL, covered with the cartilaginous layer KPS articular process GFS and Shin SBE the fully formed as a joint surface GFL, covered with the cartilage layer KPS articular process GFS including the meniscus MK or menisci IMK, AMK removed and replaced by the joint device GV. This means that all other parts of the in the 1A and 1B described knee joint KG, which are used for the stabilization of the knee joint KG and for the natural knee joint movements, remain intact. So remains eg according to the 2A the patellar joint KSG from the implantation of the joint device GV completely untouched and still fully functional. The same applies according to the 2 B also on the ligaments of the Artificial Knee Joint KÜKG, the inner band IBA, the outer band ABA and the Kreuzbändern KRB and especially in the 2 B shown anterior cruciate ligament KB too.

In such a way as in the 2A and 2 B Artificial knee joint KÜKG it is therefore ensured that when the joint device GV is used in the artificial knee joint KÜKG for endogenous support or replacement of natural joint movements and regardless of how this is configured, at least the stability of the knee joint despite the absence of the meniscus MK, IMK, AMK is given. The other due to the absence of the meniscus MK or the menisci IMK, AMK resulting functional impairment of the artificial knee joint KÜKG against the natural knee joint KG in the 1A and 1B , Such as the Stoßdämpffunktion and the property for producing a uniform pressure distribution in the articular surfaces, should therefore be the best possible mitigated by the joint device GV.

The generation of natural joint movements, eg in the knee joint KG in the 1A and 1B , is the interaction of the anatomical joint mechanism, the joint mechanism of surrounding muscles and the central nervous system as a motor impulse generator for the musculature. If this system of joint mechanism, musculature and central nervous system fully or only partially functional, it can be supported by the implanted joint device GV provided by this system natural knee joint movement. If, on the other hand, the system of joint mechanism, musculature and central nervous system is so severely disturbed, eg by paralysis, that no natural knee joint movement is possible, the implanted joint device GV replaces the natural knee joint movement.

3 shows based on the presentation on the web page http://www.heilberufe-ausbildung.de/Knochen_Gelenke/Knochen.htm the principal mode of action and the use of the artificial knee joint KÜKG with the implanted joint device GV according to 2A and 2 B in a human body for endogenous support or replacement of natural knee joint movements. To explain the principal mode of action of the joint device GV are in the 3 most components of the joint device GV (but not all components of the joint device GV) are shown. The still missing for the preferred embodiment of the invention but also relevant components of the hinge device GV are in 4 shown.

As shown in the 3 For example, the hinge device GV (schematic representation) comprises a joint prosthesis GPT implanted in the knee joint of the human body. In the knee joint, an arrangement for the electromagnetic force generation AEMK is also introduced, which is part of the GPT joint prosthesis. This is in the 3 in such a way that the arrangement for the electromagnetic force generation AEMK as a smaller "box" is located in a larger "box", which represents the joint prosthesis GPT. As the relationship between the arrangement of the electromagnetic force generation AEMK and the GPT joint prosthesis looks in detail, it will be described later in the description of the arrangement for electromagnetic force generation AEMK is later in the description of 4 clarified.

In addition to the joint prosthesis GPT and the arrangement for electromagnetic force generation AEMK the joint device GV also contains a control unit STE, which is connected to the control of the miniature electromagnet MEM with this. The control unit STE is preferably located in the vicinity of the miniature electromagnet MEM introduced in the knee joint (cf. 4 ). This preferred accommodation (implantation) of the control unit STE is in the 3 not shown for reasons of space. Instead, the control unit STE is in accordance with 3 not far from the knee joint with the implanted miniature electromagnet MEM on the femur OSK (alternative for the introduction of the control unit).

Before discussing the detailed principle of operation of the joint device GV, the construction of the control unit STE and the arrangement for the electromagnetic force generation AEMK will first of all be described below.

Central component of the control unit STE is a microprocessor MIP, each having a bidirectional connection to a radio frequency interface (RF interface) RFI, at least one input / output interface (I / O interface) IOI, but preferably two I / O Interfaces - a first I / O interface IOI1 and a second I / O interface IOI2 - and to a programming interface PSS has. The microprocessor MIP of the control unit STE is bidirectionally connected to the arrangement for electromagnetic force generation AEMK via the I / O interface IOI or the first I / O interface IOI1.

In the principle of electromagnetic force generation, the force is generated by magnetic repulsion or attraction. The arrangement for electromagnetic force generation AEMK has for this purpose, on the one hand, a magnetic part MGT, which has a substantially longitudinal direction (as in 3 represented) by the poles "N" and "S" pronounced magnetization MGT and may be formed, for example as a permanent magnet PMG, and on the other a miniature electromagnet MEM, which forms a common functional unit for the electromagnetic force generation with the magnetic part MGT. For this purpose, in the miniature electromagnet MEM a substantially in the axial direction (as in 3 represented by the poles "N" and "S" pronounced electro-magnetization, which runs substantially perpendicular or perpendicular to the magnetization MGT. For this purpose, the miniature electromagnet MEM has an iron core ESK with a coil SPL spanning it. The coil SPL is in turn connected to a drive logic ASL, which supplies power to the coil SPL and which, triggered by control commands, changes the current direction in the coil SPL and thus brings about a reversal of the polarization of the magnet. By this polarity reversal forces and attraction forces is alternately generated between the magnetic member MGT and the permanent magnet PMG and the miniature electromagnet MEM. This is in the 3 by a coil winding shown by a solid line (current direction is left of the iron core from the drawing plane and right of the iron core in the drawing plane) and corresponding magnetization (field line outside the iron core from "N" to "S" and iron core from "S" to "N ") and by a coil winding shown with dashed lines (current direction is left of the iron core in the drawing plane and right of the iron core from the drawing plane) and corresponding magnetization (field line outside the iron core from" S "to" N "and in the iron core of" N " after "S").

Both the control unit STE and the miniature solenoid MEM are supplied for the respective operation of a battery BAT with electrical energy, ie with electricity. The battery BAT is preferably primary or secondary cell based and is located or mounted either inside or outside the human body. In the arrangement of the battery BAT within the body, this is for example at the joint bone GK, eg the tibia SBE, as in the 3 shown attached. Optionally, here, in the endogenous placement of the battery BAT, in the case that the battery is secondary cell-based, even wireless charging options, for example by induction, come into question.

For example, when attached externally to the body, the battery BAT may be attached to a belt around the waist of the human.

• 1. Steuerung durch eine körperendogene Impulsgebung, bei der die Steuerungseinheit STE bzw. der Mikroprozessor MIP über das I/O-Interface IOI bzw. das zweite I/O-Interface IOI2 mit mindestens einem Elektromyographie-Sensor EMGS und/oder mindestens einem Gehirnstrom-Sensor GSS, die jeweils für die Steuerung der endogenen Kniegelenkbewegungen bestimmte körpereigene Impulse erfassen, verbunden ist.
• 2. Steuerung durch eine manuelle, körpereigene und -exogene Impulsgebung, bei der die Steuerungseinheit STE bzw. der Mikroprozessor MIP über das I/O-Interface IOI bzw. das zweite I/O-Interface IOI2 elektromechanisch mit einer manuell von einem Menschen, dem die Gelenkvorrichtung GV implantiert worden ist, bedienbaren, Impulse auslösenden Bedieneinrichtung BDE verbunden ist. Die Bedieneinrichtung BDE ist dabei vorzugsweise derart am Körper des Menschen angebracht, dass dieser durch einfache Handbedienung das Aussenden von Impulsen durch die Bedieneinrichtung BDE auslösen kann. Vorstellbar ist aber auch (wie in der 3 dargestellt), dass die Bedieneinrichtung BDE z.B. um die Hüfte des Menschen befestigt ist.
• 3. Steuerung durch eine externe, körperfremde und -exogene Impulsgebung, bei der die Steuerungseinheit STE bzw. der Mikroprozessor MIP über das RF-Interface RFI mit einem Fernsteuergerät FSG zur Aussendung ferngesteuerter Impulse an die Steuerungseinheit STE drahtlos verbunden ist.
• 4. Steuerung durch eine automatisierte, auf die körpereigenen Gelenkbewegungen angepasste Impulsgebung, bei der die Steuerungseinheit STE bzw. der Mikroprozessor MIP über die Programmier-Schnittstelle PSS derart programmierbar ist, dass, wenn ein Mensch, dem die Gelenkvorrichtung GV implantiert worden ist, der das natürliche Kniegelenk KG noch ganz leicht bewegen kann und somit noch eine initiale Bewegung des Körpers schafft, durch entsprechendes Programm-basiertes Ansteuern des Miniatur-Elektromagneten MEM die aktive unterstützende endogene Kniegelenkbewegung gestartet wird.

In order for the natural knee joint movements to be endogenously supported or replaced by the joint device GV in the artificial knee joint KÜKG introduced into the human body, the microprocessor MIP of the control unit STE for controlling the miniature electromagnet MEM must be pulse-based Control commands (pulses) are controlled. In this case, the control commands mentioned above for controlling the miniature electromagnet MEM are generated and output. This pulse-based control is preferably performed by at least one of the following types of pulsing:

• 1. Control by a body-endogenous pulse, in which the control unit STE or the microprocessor MIP via the I / O interface IOI or the second I / O interface IOI2 with at least one electromyography sensor EMGS and / or at least one brain power Sensor GSS, each of which detects the body's own impulses for the control of the endogenous knee joint movements, is connected.
• 2. Control by a manual, endogenous and exogenous pulse, in which the control unit STE or the microprocessor MIP via the I / O interface IOI and the second I / O interface IOI2 electromechanically with a manually by a human, the the joint device GV has been implanted, operable, pulse-triggering control device BDE is connected. The operating device BDE is preferably attached to the human body in such a way that it can trigger the emission of pulses by the operating device BDE by simple manual operation. But it is also conceivable (as in the 3 shown) that the control device BDE is attached, for example, around the waist of the person.
• 3. Control by an external, exogenous and exogenous pulse, in which the control unit STE or the microprocessor MIP is wirelessly connected via the RF interface RFI with a remote control unit FSG for transmitting remote-controlled pulses to the control unit STE wirelessly.
• 4. Control by an automated, adapted to the body's joint movements pulse, in which the control unit STE or the microprocessor MIP via the programming interface PSS is programmable such that, if a person, the joint device GV has been implanted, the natural knee joint KG still can move quite easily and thus still creates an initial movement of the body, by appropriate program-based driving the miniature electromagnet MEM, the active supporting endogenous knee joint movement is started.

4 shows the basic structure and the artificial knee joint KÜKG arrangement - specific principle realization of the electromagnetically based concept of the joint device GV after the 3 for endogenous support or replacement of the natural knee joint movements. Starting from the representations in the 2A and 2 B show the 4 based on a simplified schematic diagram of the popliteal joint KKG with the involved femur OSK and the tibia SBE which additional components of the joint device GV, to which already in the description of the 3 mentioned device components, in the popliteal joint KKG is implanted. First, the joint prosthesis GPT should be mentioned, which is attached to the ends of the joint bone GK (foot of the thigh bone OSK and tibial bone of the tibia SBE) of the popliteal joint KKG. Thus, the joint prosthesis GPT has a first prosthesis piece PTS1, which is preferably designed as a magnetic joint roller, which is formed as a joint surface, covered with the cartilaginous layer of the thigh bone OSK in the popliteal joint KKG completely replaced (see 1A and 2A ) and firmly connected to the thighbone OSK and / or anchored in the thighbone OSK. The first prosthesis piece PTS1 or the magnetic joint roller is magnetized in such a way and, for example as already mentioned above, formed as a permanent magnet PMG, that with respect to the associated joint bone GK or the thigh bone OSK a diametrical, substantially in the longitudinal direction of the joint bone GK or Thigh bone OSK pronounced magnetization MGT exists (cf. 3 ). As material for the first prosthesis piece PTS1 of the joint prosthesis GPT are basically all magnetic materials in question, such as ferromagnetic materials such as the purely metallic elements iron, cobalt, nickel, etc. or ferromagnetic alloys such as AlNiCo alloys, SmCo alloys, Nd _2nd Fe ₁₄ B alloys, Ni ₈₀ Fe ₂₀ alloys (also referred to as "permalloy") or NiFeCo alloys (also referred to as "mumetal").

Furthermore, the joint prosthesis GPT has a second prosthesis piece PTS2, which is preferably designed as a metal joint plateau, the joint surface formed as covered with the cartilage layer articular process of the tibia SBE in the popliteal joint KKG completely replaced (see 1A and 2A ) and firmly anchored on the tibial head of the tibia SBE and / or anchored in the tibia SBE. The second prosthesis piece PTS2 has the miniature electromagnet MEM, wherein the electro-magnetization generated in the miniature electromagnet MEM acts with respect to the associated joint bone GK or the tibia SBE essentially in the axial direction (cf. 3 ). In the case of the metal Gelenkplateaus the miniature electromagnet MEM is integrated in the metal joint plateau, as material for the metal joint plateau in addition to metal other materials in question, such as carbon, plastic, etc. in the form of ceramics or fiber composites.

The magnetizations of the prosthesis pieces PTS1, PTS2 - in the first prosthesis piece PTS1, the magnetization MGT and the second prosthesis piece PTS2, the miniature electromagnet MEM generated by the electro-magnetization - done with inverted polarity, so that in the active endogenous joint movement, the associated joint bone GK, OSK, SBE at the same time, independent of direction of movement (cf. 5A to 5C and 6A to 6C ) in each case in a first portion TB1 by magnetic repulsion forces from each other and in a second portion of TB2 by magnetic attraction forces approach each other.

In this way, on the joint bone GK, the femur OSK and the tibia SBE, new modified articular articular surfaces KGFL. Between these two artificial joint surfaces KGFL at the foot of the thigh bone OSK and the tibial head of the tibia SBE now another additional component of the joint device GV is introduced a sliding element GLE, which, when the two prosthetic pieces PTS1, PTS2 connected to the joint bone GK, OSK, SBE and / are anchored in this, between the prosthetic pieces PTS1, PTS2 arranged and designed such that it serves as a sliding surface of the prosthesis pieces PTS1, PTS2.

As already in the description of the 3 is indicated, the control unit STE should preferably be placed in the vicinity of the arranged in the knee joint miniature electromagnet MEM. In contrast to the placement of the control unit STE on the thighbone OSK (cf. 3 ) this is according to the 4 housed in or on the tibia. In this case, the control unit STE is preferably implanted in the tibia SBE together with the second prosthesis piece PTS2 of the joint prosthesis GPT. The 4 Incidentally, the mounting of the battery BAT on the tibia SBE also in the vicinity of the miniature electromagnet MEM and the control unit STE and the connection to the electromyography sensor EMGS and / or the brain current sensors GSS, which are responsible for the control of the endogenous Joint movements detect certain body-own pulses and forward them to the control unit STE.

5A . 5B and 5C show starting from the 4 and on the basis of the associated description of the figure, the electromagnetically based endogenous support of the knee during a movement for a first direction of movement BWR1 (bending of the knee) out of a neutral knee joint position (180 ° position; 5A ), via a weakly angled knee joint position (eg 160 ° position; 5B ) into a slightly angled knee joint position (eg 120 ° position; 5C ). The 5A 5B and 5C illustrate exemplarily for the first direction of movement BWR1, as a result of the electromyography sensor EMGS and / or the brain current sensors GSS forwarded to the control unit pulses with appropriate control of the miniature electromagnet MEM by the control unit STE an active, electromagnetic force on the joint bones GK, the femur OSK and the tibia SBE, based endogenous joint movement is generated, which supports or replaces a natural joint movement. The sliding element GLE has the task of serving as a sliding surface of the prosthesis pieces PTS1, PTS2 during active, endogenous joint movement.

6A . 6B and 6C show starting from the 4 and on the basis of the associated figure description as well as the scenario in the 5A to 5C the electromagnetically based endogenous support of the knee in a movement for a second direction of movement BWR2 (stretching of the knee), which is opposite to the first direction of movement BWR1 in the 5A to 5C runs, from the slightly angled knee joint position (eg 120 ° position; 6A ;), via the weakly angled knee joint position (eg 160 ° position; 6B ) in the neutral knee joint position (180 ° position; 6C ). The 6A . 6B and 6C illustrate exemplarily for the second direction of movement BWR2, as a result of the electromyography sensor EMGS and / or the brain current sensors GSS forwarded to the control unit pulses with appropriate control of the miniature electromagnet MEM by the control unit STE an active, electromagnetic force on the joint bones GK, the femur OSK and the tibia SBE, based endogenous joint movement is generated, which supports or replaces a natural joint movement. The sliding element GLE has the task of serving as a sliding surface of the prosthesis pieces PTS1, PTS2 during active, endogenous joint movement.

QUOTES INCLUDE IN THE DESCRIPTION

This list of the documents listed by the applicant has been generated automatically and is included solely for the better information of the reader. The list is not part of the German patent or utility model application. The DPMA assumes no liability for any errors or omissions.

Cited non-patent literature

• http://www.arthrose.de/arthrose/haeufigkeit.html [0003]
• see. http://www.asklepios.com/orthopaediehamburgwest_Kniegelenk.Asklepios [0004]
• http://www.arthrose.de/arthrose/haeufigkeit.html [0004]
• http://www.apotheken-umschau.de/multimedia/15/51/89/6208544785.jpg [0007]
• http://www.rewalk.com/en/ [0011]
• http://www.exoskelette.com/berkeley-bionics.html [0011]
• https://www.youtube.com/watch?v=_Jq2zr5tauA [0011]
• http://www.rexbionics.com/ [0011]
• http://www.lockheedmartin.com/us/products/hulc.html [0012]
• see. http://www.army-technology.com/projects/raytheon-xos-2-exoskeleton-us/ [0012]
• http://www.cnet.com/news/panasonic-working-on-actual-alien-power-loader/ [0013]
• http://www.cpk-kempten.de/kniegelenk.html [0023]
• http://www.heilberufe-ausbildung.de/Knochen_Gelenke/Knochen.htm [0025]
• http://www.cpk-kempten.de/kniegelenk.html [0030]
• http://www.heilberufe-ausbildung.de/Knochen_Gelenke/Knochen.htm [0037]

Claims (11)

An articulating device (GV) for a hinge insert in living bodies, in particular humans, for endogenously supporting or replacing natural joint movements with (a) a joint prosthesis (GPT), comprising a first prosthesis piece (PTS1) and a second prosthetic piece (PTS2), each this prosthesis piece (PTS1, PTS2) with one of several, in particular two, joint bone (GK, OSK SBE) of a natural joint (KG) in the body in such a binding and / or in the joint bone (GK, OSK, SBE) anchored, the joint prosthesis (GPT) either at least partially replaces a joint extension (GFS) of the joint bones (GK, OSK, SBE) formed as articular surface (GFL) and covered with a cartilaginous layer (KFS), or is placed at least partially on the articular process (GFS), characterized in that (b) the first prosthesis piece (PTS1) is magnetized in such a way, in particular as a permanent magnet (PMG) is formed that with respect to the associated gel (GK, OSK, SBE) a diametrical, substantially in the longitudinal direction of the joint bone (GK, OSK, SBE) pronounced magnetization (MGT), (c) the second prosthesis piece (PTS2) a miniature electromagnet (MEM), in particular with a control logic (ASL) and an iron core (ESK) spanning coil (SPL), wherein in the miniature electromagnet (MEM) generated electro-magnetization with respect to the associated joint bone (GK, OSK, SBE) substantially in axial direction acts, (d) a control unit (STE) for controlling the miniature electromagnet (MEM) in such a way, in particular with a microprocessor (MIP) and with at least one associated I / O interface (IOI, IOI1, IOI2) is formed by at least one of a body-endogenous pulse, a manual, the body's own and body-exogenous pulse, an external, extraneous and body-exogenous pulse and an automated, on the body's own (E) a common functional unit comprising and implementing device features (a) to (d) is designed such that to assist or replace the natural articulation movements, a functional unit adapted to articulate movements is generated and outputted to control the miniature electromagnet (MEM); active, based on electromagnetic force exerted on the joint bones (GK, OSK, SBE), endogenous joint movement is generated, (f) a sliding element (GLE), which, when the two prosthetic pieces (PTS1, PTS2) with the joint bones (GK, OSK, SBE) are connected and / or anchored therein between the prosthesis pieces (PTS1, PTS2) arranged and designed such that it serves as a sliding surface of the prosthetic pieces (PTS1, PTS2) in the active, endogenous joint movement. Joint device (GV) according to claim 1, characterized in that the magnetization of the prosthetic pieces (PTS1, PTS2) takes place with inverted polarity, so that in the active endogenous joint movement, the associated joint bone (GK, OSK, SBE) at the same time, regardless of movement direction in each case remove the first portion (TB1) from each other by magnetic repulsive forces and in a second portion (TB2) by magnetic attraction forces approach each other. Joint device (GV) according to claim 1 or 2, characterized in that in a knee joint insert of the human, the first prosthesis piece (PTS1) of the joint prosthesis (GPT) with a femoral bone (OSK) of the joint bones (GK, OSK, SBE) connects and / or is anchored in this as well as a magnetic joint roller and the second prosthesis piece (PTS2) of the joint prosthesis (GPT) with a tibia (SBE) of the joint bones (GK, OSK, SBE) binds and / or anchored in this and as a metal joint plateau is formed, in which the miniature electromagnet (MEM) is integrated. Joint device (GV) according to one of claims 1 to 3, characterized in that the control unit (STE) for the body endogenous pulse, in particular via a second I / O interface (IOI2), with at least one electromyography sensor (EMGS) and / or cerebral flow sensors (GSS), which detect endogenous joint motions of certain body-own impulses. Articular device (GV) according to one of claims 1 to 4, characterized in that the control unit (STE) for the manual, endogenous and exogenous pulse, in particular via a second I / O interface (IOI2), electromechanical with a manual by a People, the device has been implanted, operable, pulse triggering control device (BDE) is connected. Joint device (GV) according to one of claims 1 to 5, characterized in that the control unit (STE) for the external, exogenous and exogenous pulse, in particular via an RF interface (RFI), with a remote control device (FSG) for transmitting remotely controlled Pulses to the control unit (STE) is wirelessly connected. Joint device (GV) according to one of claims 1 to 6, characterized in that the control unit (STE) for the automated, adapted to the body's joint movements Pulse has a programming interface (PSS), via which the control unit (STE) is programmable such that, if a person, the device has been implanted, the natural joint can still easily move and thus still an initial movement of the Body creates, by appropriate program-based driving of the miniature electromagnet (MEM), the active supporting endogenous joint movement is started. Joint device (GV) according to claim 1, characterized in that the miniature electromagnet (MEM) for power to a primary or secondary cell-based battery (BAT) inside or outside the body is connectable and the battery (BAT) within the body, in particular at the joint bone (GK, OSK, SBE) is attached. Joint device (GV) according to one of claims 1 or 4 to 7, characterized in that the control unit (STE) on the joint bone (GK, OSK, SBE) can be fastened. Joint device (GV) according to claim 3 and 4, characterized in that the electromyography sensor (EMGS) on the femur (OSK) can be fastened. Artificial joint (KÜKG) for use in bodies of living beings, in particular humans, for the endogenous support or replacement of natural joint movements, characterized in that the joint device (GV) according to one of claims 1 to 10 in the body of the living being, in particular in the knee joint of the People, is implanted.

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