• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    Guide joint (1) and provided with the joint hinge joint orthosis (2) for supporting and guiding an anatomical joint (7). The guide joint (1) has a first joint leg (3) and a second joint leg (4) and the joint legs (3, 4) are interconnected via a first linear guide (5) and a second linear guide (6). Each of the linear guides (5, 6) has a guideway (10, 11) in the form of a slot or groove in the second articulated arm (4), in each of which a sliding element (12, 13) arranged on the first articulated arm (3) engages, wherein the guideways (10, 11) intersect. The two sliding elements (12, 13) are spatially separated from each other and spaced and protrude from a side surface of the first hinge leg (3).
    公开号:AT517182A1
    申请号:T50323/2015
    申请日:2015-04-22
    公开日:2016-11-15
    发明作者:Kurt Wayd
    申请人:Kurt Wayd；
    IPC主号:
    专利说明:

    Guide joint for a joint orthosis
    The invention relates to a joint for a joint orthosis for the physiological guidance of an anatomical joint, wherein the guide joint has a first joint leg and a second joint leg and the joint legs are connected to each other via a first linear guide and a second linear guide, wherein each of the linear guides as a slot or groove trained guideway in the second hinge leg, in each of which engages a arranged on the first hinge leg slider, and wherein the guideways intersect.
    The invention further relates to a joint orthosis for a knee joint with a thigh assembly and a lower leg assembly, which are connected to each other via an outer guide joint and an inner guide joint.
    The bending movement of the human knee joint is a complex kinematic interaction of various translational and rotational movements resulting from the rolling and sliding of the femoral condyles (medial and lateral condyles) of the femur (femur) on the opposite tibial plateau of the lower leg bone. Tibia and femur cohesion is provided by ligaments, tendons, and muscles that allow not only flexion but also relative axial twisting and lateral tilting of the tibia relative to the femur (similar to an O-leg and X-leg Position).
    In a complete flexion (ie a pivoting movement from an angle of 0 ° -stretched leg - up to an angle of about 135 ° or more - fully angled leg) pivots the thigh not only about a fixed with respect to the lower leg pivot axis, but the Thigh also moves posteriorly with respect to the tibial plateau. This offset movement to the rear is up to about 12 -14 mm in the case of an average-sized adult knee joint. In a full extension, ie a pivoting movement from an angle of 135 ° and more to the starting position of 0 °, the lower leg (tibia) turns from the top by about 15 ° about its own axis to the outside (lateral). At the same time, the tibia can also move laterally to the femur in a small angular range, comparable to an O-leg or X-leg position. During the bend, the thigh in the joint plane at the beginning, that is to say in the first approx. 30 ° of flexion, undergoes almost a pure rotation about a fixed axis of rotation, and only then does the translational movement begin posteriorly and downwards.
    After knee surgery, it is necessary for a rapid healing process, especially the knee joint targeted physiological guide. The flexion movement should also be possible completely or as required in terms of angle. This function is performed by knee-joint orthoses constructed of a thigh mount, a lower leg mount, and a hinge mechanism located between upper and lower leg mount, with the upper and lower leg months conventionally performed with straps or hard shells.
    Above all, the physiological leadership is solved by many knee braces of the prior art only a little satisfactory.
    For example, in conventional knee braces, the articulating mechanism consists of two monocentric pivots disposed on opposite sides of the knee joint and defining a pivot through the knee joint. However, this rotational movement about a fixed axis of rotation contradicts the physiological kinematics of the anatomical knee. Since rotation can not occur simultaneously about two different axes, a difference in movement occurs between the anatomical knee and the orthosis, which leads to elevations and displacements of the orthosis on the patient's leg and of the patients especially when the greater bending of the knee as extremely unpleasant is felt. This difference movement can also have negative effects on the healing process, since the ligaments and tendons are additionally burdened. Usually, in the application of commercially available knee orthoses, a "compromise axis" is sought which is chosen such that the smallest displacements result during a complete flexion between the monocentric orthotic joint and the anatomical knee joint. The "compromise area" is a limited small area on the inside and outside of the knee which is best aligned with the variable rotation area of the anatomical knee. This "compromise area" is usually found in the posterior third of the femoral condyles. If the axis of rotation is positioned outside of this limited area, quite significant displacements and lifts of the orthosis on the leg of the patient. In practice, a sustainable alignment mounting of the orthosis on the leg of the patient, however, can hardly be achieved.
    Numerous attempts to create physiologically correct joints for knee joint orthoses have failed because the complex movements of the knee joint described above are well known, but have not yet been implemented mechanically.
    US 2013/0018293 A1, filed by the present Applicant, discloses several embodiments of knee joint orthotic joints which have for the first time succeeded in satisfactorily reproducing the kinematic specifications of the knee joint. A disclosed in US 2013/0018293 A1 embodiment of a joint has two flat, abutting joint legs, wherein in one of the joint leg a substantially along the leg axis extending, wide guide groove and introduced at the bottom of the guide groove extending substantially transversely to the leg axis narrow guide slot are. The other leg axis has a circular plateau whose diameter corresponds to the width of the guide groove. On the plateau a bolt is further arranged, whose diameter corresponds to the width of the guide slot. The plateau is inserted into the guide groove so that the bolt is arranged in the guide slot. By the two, substantially transversely arranged guides results between the two joint legs a kinematic movement that corresponds to the knee movement very closely. The translational movement of the upper joint leg, ie the joint leg, which is intended to follow the movement of the thigh, corresponds essentially to the length of the guide slot.
    However, a disadvantage is the complex production of this joint. Due to the two laterally juxtaposed joint leg limiting pins that are used in holes to limit the bending movement, adversely disadvantageous to bending.
    It is the object of the subject invention to provide a ball joint and a knee joint orthosis provided with this joint, which further improves the state of the art. In particular, a guide joint is to be created that is small, lightweight and easy to manufacture. Between the first joint leg and the second joint leg, a corresponding physiological joint movement should result.
    These and other objects are achieved according to the invention by a hinge of the type mentioned, in which the two sliding elements are spatially separated from each other and spaced and protrude from the first joint leg. This allows the production of a cost-effective and stable guide joint, which also durable strong static and dynamic loads, such as those occur in knee braces. The two axes of rotation of the sliding elements are parallel, but laterally offset from each other. As a result, the position of the sliding elements at each diffraction angle is clearly defined in the crossed guideways.
    The distance between the two axes of rotation and the arrangement and length of the two guideways is chosen so that the resulting movement when bending the Führungsge steering the physiological bending movement of an average-sized femoral head corresponds as closely as possible.
    In a preferred embodiment, the sliding elements can be arranged on two opposite sides of the first joint leg. In this case, the sliding elements can protrude in different directions from the joint leg to the outside or they can protrude from two opposite inner surfaces of the joint leg in opposite directions inwards.
    In an advantageous embodiment, the first or second joint leg can have bores for inserting a delimiting pin. This allows the possible range of diffraction angles of the guide joint to be limited in a simple and effective manner. In a joint leg, which is composed of two side parts, the side parts can have congruent holes for inserting a limiting pin.
    In a further advantageous embodiment of the invention, the sliding surfaces on the sliding elements and / or on the guideways may be provided with a friction and wear reducing surface coating. On the one hand, a surface coating reduces the wear of the guide joint and can optionally replace a complex hardening.
    The guide joint according to the invention can also be advantageously used in prostheses.
    The above-mentioned joint orthosis for a knee joint, which is provided on both sides with a guide joint according to the invention, allows a physiologically correct guidance of the joint over the entire diffraction region. Due to the achievable small size of the guide joints, the joint orthosis can have a very low weight and be well adapted to the body shape, so that in addition a good wearing comfort is guaranteed.
    Advantageously, in this case, an outer thigh rail of the thigh assembly can be connected via a first hinge to the outer guide joint, and an inner lower leg rail of the lower leg assembly can be connected via a second hinge, an intermediate rail and a third hinge with the inner hinge. This allows an advantageous adaptation of the joint orthosis to different leg shapes. Optionally, less or more than the above hinges may be provided as needed. The hinges can also allow a simple, space-saving folding of the unused joint orthosis.
    In a preferred embodiment, the inner hinge can be integrally formed with the inner thigh rail and / or the outer hinge can be integrally formed with the outer lower leg rail.
    The subject invention will be explained in more detail below with reference to Figures 1 to 5, which show by way of example, schematically and not by way of limitation advantageous embodiments of the invention. It shows
    Figure 1 is a schematic representation of the movement of a human knee joint in a bending movement of the knee.
    Fig. 2 shows a hinge according to the invention in an exploded perspective view;
    Fig. 3 shows the guide joint of Figure 2 in another exploded perspective view from a different perspective.
    4a to 4h is a schematic representation of the sequence of movement of the guide joint shown in Figures 2 and 3 ..;
    5 and 6 show an alternative embodiment of the guide joint according to the invention in two crack representations; and
    Fig. 7, two guide joints according to the invention with the attached rails of a knee brace.
    To illustrate the sequence of movements that results in the flexion of a human knee joint, Figure 1 shows this sequence of movements based on four different flexion angles of the knee in a sectional view through femur 34 (thigh bone) and tibia 35 (tibia), wherein the sectional plane of the joint plane corresponds, which runs normal to the joint axis. The other elements of the knee joint, such as the kneecap, the meniscus, the fibula or the numerous ligaments are not shown in FIG. 1 for the sake of clarity.
    Starting from an extended leg (position a shows the tibial and femoral head at a diffraction angle of 0 °), the following positions b, c and d each show a bent position of the knee joint at 30 °, 90 ° and 135 °. A healthy knee joint can be angled even further, with the maximum possible flexion generally being at an angle between about 140 ° to 150 °. During the flexion movement of the knee, the condyles 36 of the femur 34 slide on the adjoining pan-like tibial plateau 37 of the tibia 35. Essential for the movement is thus the shape of the condyles 36, the course of which is simplified in the articular plane as two merge circles K and k merging into one another can, with the larger K-circle having a larger radius than the radius of the smaller K-circle k. During the flexion movement, the condyles 36 slide initially, ie from the straight leg (0 °) to a flexion of about 30 °, almost exclusively along the larger kinking circle K, so theoretically for the femur 34 a nearly pure rotational movement about the center of the larger Schmiegekreises K results.
    In fact, the selected pivot point for all monocentric joints is in a "compromise zone" found in the posterior third of the femoral condyles, within the small kink circle k.
    From position b there is a transition from the large kink circle K to the small kink circle k, in which the condyles on the tibial plateau also begin to roll in addition to the sliding movement and the center of rotation shifts progressively posteriorly. (This displacement corresponds to the displacement of a sliding element 12 described below along a guide track 10 of a linear guide 5, in FIGS. 2 to 4).
    The initial positions A of the variable rotation center relative to the tibial plateau changes during the flexion movement and migrates to an end position E, which is shown in Fig. 1 for the flexion angle of 135 °. As can be seen from Fig. 1, also change the points of contact between the femoral condyles and the tibial plateau, and migrate during the bending movement significantly backwards (posterior), which is explained by a diffraction angle of 30 ° by an additional rolling movement. For the positions c (90 ° flexion) and d (135 ° flexion) the position of the femur 34 'is shown in dashed lines, which would result (starting from position a) with a pure rotation of the femur 34 about a fixed pivot point, as the virtual rotation center, the initial position A of the variable rotation center was selected. It can be seen that the actual position of the femur 34 has shifted in the position d with respect to the virtual layer 34 'by a horizontal offset h and a vertical offset v ".
    This horizontal and vertical offset is the cause of a knee joint seat having a pure pivot tending to be in the angled position, i. from a flexion angle of 30 °, "push away" the thigh from the lower leg, so that between the femur 34 and tibia 35 a tensile load is created, which would additionally stress the ligaments, which should actually be spared. In the case of knee joint orthoses with a fixed axis of rotation, therefore, the maximum flexion angle is usually restricted. Although walking is still possible, movements that require a larger flexion angle are prevented by the orthosis. A sports activity, such as running, cycling, gymnastics or swimming, is hardly possible with a limited maximum angle of the diffraction. A targeted training to build muscle and regain full joint mobility after surgery can not be carried out satisfactorily with the orthosis. Exercises that require a larger flexion angle can no longer be performed by the patient alone. Instead, with the orthosis in place, the exercise must be performed with the help of a therapist who manually supports the joint during the exercise. Using an ergonomically correct orthosis, the patient could perform many exercises more frequently and more regularly without the costly professional support of a therapist.
    In order to produce a physiological guide joint, therefore, the movement sequence shown in Fig. 1 must be reproduced as faithfully as possible, in particular the achievement of the relatively large horizontal offset h of joints with a monocentric joint is not technically possible.
    Fig. 2 and Fig. 3 show an inventive hinge 1 from two different perspectives. The hinge 1 consists of a one-piece upper hinge leg 3 and a two-part lower hinge leg 4. The upper hinge leg 3 consists of a substantially flat plate having a guide portion 39, projecting from the one side sliding on a first slider 12 and from the opposite side projecting a second sliding member 13 are arranged. The sliding members 12, 13 are each formed as circular discs fixed to the surface of the guide portion 39. The discs may be fixedly mounted or formed as rollers, wherein the axes of the two sliding elements 12,13 are arranged offset to one another. The two sliding elements are spatially separated from each other and have, with respect to the joint plane, no overlaps. The surface of the sliding elements 12,13 has a high hardness and low friction, this can be achieved either by a hardening of the surface or by a coating.
    The lower joint leg 4 consists of a first side part 8 and a second side part 9, which have substantially the same outer contours. In the first side part 8, a slot-shaped first guide track 10 is provided for the first sliding element 12, and in the second side part 9, a slot-shaped second guide track 11 is provided for the second sliding element 13. The two sliding elements 12,13, each in a
    Fi'ihri inriehohn n Π 11 nloiton hilrlon with Ηιωοωπ on iorlor Qoito rloc nharön ^^ l ^ nlzoorhartlzalc 3 each have a linear guide 5, 6 from. The guideways 10, 11 are formed as simple slots in the side part 8, 9, wherein also simple or profiled grooves or other, more complex guideways for the sliding elements 12, 13 of the upper joint leg can be provided. The sliding surfaces provided in the guideways 10, 11 may, like the corresponding surfaces of the sliding elements 12, 13, be coated or hardened to improve the sliding properties and longevity of the joint.
    The upper joint leg 3 and the two lower side parts 8, 9 each have mounting holes 43, with which the guide joint can be attached to adjacent structures, for example on the thigh mounting or the lower leg assembly of a knee-joint orthosis. Instead of the mounting holes 43, any other types of attachment may be provided. In this case, a spacer element can be provided between the two side parts 8, 9, so that the distance between the side parts 8, 9 corresponds to the thickness of the guide region 39 of the upper joint leg 3 plus a play allowance. Preferably, for the lower joint leg 4, the adjacent structure, that is about a rail of the lower leg assembly, to which the guide joint is attached, at the same time perform the function of the spacer element.
    Advantageously, the upper joint leg 3 of the inner guide joint can be made in one piece with the thigh assembly of a knee brace, so that the mounting holes are unnecessary. The same applies to the outer joint, with a side part of the lower joint leg 4 can be made in one piece with the lower leg assembly. In this case, however, the second side part must be provided with mounting holes to hold the guide joint together.
    Furthermore, a number of bores 14,15 are introduced into the side parts 8, 9 in the edge region, wherein each bore 14 of the first side part 8 is associated with a coaxial bore 15 in the second side part 9, resulting in multiple pairs of bores. Through each pair of holes 14,15 a limiting pin 44 can be pushed (shown in Fig. 2), which limits the movement of the upper joint leg 3 at a certain angle. The limiting pin 44 may, for example, be provided with a thread which is screwed into a thread provided in the bore 15 in order to fix the limiting pin 44.
    The terms "top" and "bottom" refer only to the orientation shown in Figs. 2 and 3, but it will be apparent to those skilled in the art that the hinge may be used in reverse, so that the "lower" hinge leg 4 of Fig. 2 and 3 can be installed in a joint orthosis just as much as the upper joint leg. By doing
    Case, the course of the linear guides 5, 6 would have to be adjusted accordingly. The terms "top" and "bottom" are for convenience of description only and are not intended to be limiting. The same applies to the terms "inside" (ie the side facing the knee joint) and "outside" (ie the side facing away from the knee joint).
    The two guideways 10, 11 are, with respect to the joint plane, arranged crosswise, with a clearly defined relative position between the upper joint leg 3 and lower joint leg 4 results through the crosswise arrangement and the two staggered sliding elements 12, 13 for each diffraction angle. The first linear guide 5 is arranged substantially horizontally, wherein the rear, d. H. the end of the linear guide facing the diffraction inner side (ie, for example, the popliteal fossa) is arranged a little lower than the front end (that is to say, for example, the patella). This is due to the fact that the midpoint of the no oscillation circle k of the femoral condyles in the initial position at 0 ° diffraction from the tibial plateau is farther away than in the end position at 135 °. The second linear guide 6 is normal to the first linear guide 5, i. essentially vertically aligned. The angle between the first and second linear guide 5, 6 is about 90 °, but the linear guides can also be arranged at an acute or obtuse angle to each other.
    The relative movement when bending the guide joint 1 is shown in Fig. 4a to 4h, wherein the essential elements of the guide joint 1 are shown projected into the joint plane. In this case, in particular the positively driven movement of the sliding elements 12, 13 fixedly connected to the upper joint leg 3 in the crosswise arranged guide tracks 10, 11 must be taken into account. In the positions of Figs. 4a to 4c, which correspond to a diffraction of about 20 °, 35 ° and 40 °, the first sliding member 12 remains in the region of the front end of the first guide track 10, while the second sliding member 13 in the second Guideway 11 moves downwards. The movement of the upper joint leg 3 (relative to the fixed lower joint leg 4) corresponds essentially to a pivoting movement about the first sliding element 12, which in this region of the bending movement can be regarded as a substantially fixed joint axis. This flexion movement essentially corresponds to the physiological movement section in the case of the anatomical knee joint, in which the condyles 36 slide along the first osculating circle K (see FIG. 1).
    Starting at a diffraction angle of 30 ° of the position shown in Fig. 4c, and amplified in Figs. 4d to 4e, upon further flexion of the guide joint 1, the first slider 12 begins in the first guideway 10 backwards (posterior, ie away from At the diffraction angle of QO ° hot Hoc 7 A / oito f ^ loitolomont 1 ^ in Hör Fiihri innchohn 1 1 Honotonoton DiinlH- orroioht l into the end of the guideway 11) and moves Then, with further flexion again up until the first sliding member 12 is present at full flexion at the rear end of the first guide track 10. In the subsequent extension, the second sliding member 13 moves back down and it reaches the lowest point again at a diffraction angle of 90 ° and moves again on further extension up to the starting position at 0 °, (the sliding member 13 oscillates at a full flexion and extension between 90 ° and 135 °).
    In order to keep the fulcrum in a fixed position during the first 30 °, the second sliding element 13 was placed at an angle of 15 ° above the sliding element 12 in the second guide track 11. If now the sliding member 13, which is located together with the sliding member 12 on the thigh associated joint leg 3, rotate in a circular arc of 15 ° to the slider 12, then both sliding elements are on the axis of the guideway 10. However, since the Guideway 11 over the first 15 ° no circle but a straight line represents and the distance between the centers of the two sliding elements is greater than the distance from the first sliding member 12 to the interface of the two guideways, the first sliding member 12 is pressed slightly outward. To this difference measure the guideway 10 must be extended to prevent blocking the movement. When rotated by a further 15 °, the first sliding member 12 moves back to this difference measure back to the starting position. Now, the joint leg 3 has made a rotation of 30 ° without the first sliding member 12, which is the movable center of rotation, has changed its position significantly.
    However, the linear guide 6 (guide track 11) could also run in a curved manner, so that at the beginning of the bending movement (at a diffraction between 0 ° and about 30 °) a pure circular movement around the first sliding element 12 could result. The linear guide 6 would have to be performed in a circular arc of 30 ° around the front end of the first linear guide 5 around and then run straight again. However, the illustrated embodiment with straight sliding elements 12, 13 is sufficient to mimic a physiologically correct bending movement sufficiently well (the differential movement of the sliding element 12 during the first 30 ° is negligible and can be neglected).
    In order to illustrate the bending movement that the upper joint leg 3 makes relative to the fixed lower joint leg 4, compared to a pure pivoting movement about a fixed axis, a position of a comparative upper joint leg 3 'is shown in FIG. 4b to 4h, each with a dot-dash line. is plotted, which would rotate about a fixed pivot axis. As a fixed pivot axis of the comparative upper joint leg 3 ', the position shown in Fig. 1a of the first slider 12 was selected. In particular, in Fig. 4h it can be seen that the guide joint 1 according to the invention in the bending movement both a horizontal offset h, as well as a vertical offset v has substantially the horizontal offset h and the vertical offset v of the anatomical knee joint correspond, as he is shown in Fig. 1.
    5 and 6 show schematically a further embodiment of a guide joint 101 according to the invention, in which the linear guides 105, 106 have been "reversed" relative to the embodiment shown in FIGS. 2 to 4, wherein the sliding elements 112, 113 on two opposite side parts 108, 109 of the upper joint leg 103 are arranged projecting inwardly. The two intersecting guideways 110, 111 of the linear guides 105, 106 are introduced as grooves in the lying between the side members 108, 109 lower hinge leg 104. In order to reduce the thickness of the lower joint leg 4, the grooves of the guideways 110, 111 overlap in their crossing region.
    The flexion movement of the guide joints 1, 101 illustrated in FIGS. 2 to 6 makes it possible to produce anatomically correct knee joint orthoses 2, which allow the therapist to specify the specifications for a maximum (and possibly minimum) flexion angle on the basis of the medical indication, not based on the inadequacy of the knee brace 2 used. The use of such a guide joint in a knee brace 2 is illustrated in FIG.
    Fig. 7 shows the elements of the thigh assembly 16 and the lower leg assemblies 17 of the knee brace 2, which communicate with the guide joints 1a and 1b to be arranged on both sides of the knee joint. The outer guide hinge 1a connects an outer thigh rail 24 with an outer lower leg rail 18, wherein advantageously the connection with the thigh assembly by means of a hinge takes place. The inner guide joint 1b connects an inner thigh splint 25 to an inner lower thigh splint 19, wherein the connection to the lower thigh splint takes place via two hinges, which are connected to one another via an intermediate rail. The thigh mount 16 and the lower leg mount 17 may each be provided with fasteners, such as straps, for attachment to the thigh or lower leg, or may be attached to known hard shells (these are not shown in FIG. 7).
    Designation: Guide joint (1)
    Knee joint orthosis (2) upper joint leg (3) lower joint leg (4) first linear guide (5) second linear guide (6) anatomical joint (7)
    Side parts (8, 9) Guideways (10, 11)
    Sliding elements (12, 13)
    Holes (14,15)
    Thigh mounting (16)
    Lower leg assembly (17) outer lower leg splint (18) inner lower leg splint (19) outer thigh splint (24) inner thigh splint (25) first, second, third hinge (26, 27, 28)
    Intermediate rail 29
    Femur (femur) 34
    Tibia (lower leg bone) 35
    Condyle 36
    Tibiaplateau 37
    Marking point 38 Guidance area 39
    Mounting hole 43, 43 ', 43 "
    Limiting pin 44
    权利要求:
    Claims (8)
    [1]
    claims
    A joint (1) for a joint orthosis (2) for supporting and guiding an anatomical joint (7), wherein the guide joint (1) has a first joint leg (3) and a second joint leg (4) and the joint limbs (3, 4 ) via a first linear guide (5) and a second linear guide (6) are interconnected, wherein each of the linear guides (5, 6) designed as a slot or groove guide track (10,11) in the second hinge leg (4), in each of which engages on the first joint leg (3) arranged sliding element (12, 13), and wherein the guide tracks (10,11) intersect, characterized in that the two sliding elements (12,13) are spatially separated and spaced from each other and from the first joint leg (3) protrude.
    [2]
    Second guide joint (1) according to claim 1, characterized in that the first or the second joint leg (4) has two interconnected side parts (8, 9, 108, 109).
    [3]
    Third guide joint (1) according to claim 2, characterized in that the sliding elements (12, 13, 112, 113) on two opposite sides of the first hinge leg (3, 103) are arranged.
    [4]
    4. Guide joint (1) according to claim 2 or 3, characterized in that the first or second joint leg (3, 4) bores (14, 15) for insertion of a limiting pin (44).
    [5]
    5. Guide joint (1) according to any one of claims 1 to 4, characterized in that sliding surfaces on the sliding elements (12, 13) and / oran the guide tracks (10, 11) are provided with a friction and Abnutzungsverringernden surface coating.
    [6]
    6. joint orthosis (2) for a knee joint with a thigh assembly (16) and a lower leg assembly (17), characterized in that the thigh assembly (16) via an outer guide joint (1 a) and an inner guide joint (1 b), respectively one of claims 1 to 7, with the lower leg assembly (17) is connected.
    [7]
    7. joint orthosis (2) according to claim 6, characterized in that an outer thigh rail (24) of the thigh assembly (16) via a first hinge (26) with the outer guide joint (1 a) is connected, and that an inner lower leg rail (19) the lower leg assembly (17) via a second hinge (27), an intermediate rail (29) and a third hinge (28) with the inner guide joint (1b) is connected.
    [8]
    8. joint orthosis (2) according to claim 6 or 7, characterized in that the inner guide joint (1 b) is formed integrally with the inner thigh rail (24) and / or the outer hinge (1 a) formed integrally with the outer lower leg rail (18) is.
    类似技术:
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    同族专利:
    公开号 | 公开日
    US20180296381A1|2018-10-18|
    WO2016169960A1|2016-10-27|
    AT517182B1|2018-04-15|
    EP3285698A1|2018-02-28|
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    法律状态:
    优先权:
    申请号 | 申请日 | 专利标题
    ATA50323/2015A|AT517182B1|2015-04-22|2015-04-22|Guide joint for a joint orthosis|ATA50323/2015A| AT517182B1|2015-04-22|2015-04-22|Guide joint for a joint orthosis|
    PCT/EP2016/058716| WO2016169960A1|2015-04-22|2016-04-20|Guide joint for a joint orthosis|
    US15/568,671| US20180296381A1|2015-04-22|2016-04-20|Guide joint for a joint orthosis|
    EP16726484.5A| EP3285698A1|2015-04-22|2016-04-20|Guide joint for a joint orthosis|
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