WO2016004855A1 - 膝关节矫形器 - Google Patents

膝关节矫形器 Download PDF

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Publication number
WO2016004855A1
WO2016004855A1 PCT/CN2015/083465 CN2015083465W WO2016004855A1 WO 2016004855 A1 WO2016004855 A1 WO 2016004855A1 CN 2015083465 W CN2015083465 W CN 2015083465W WO 2016004855 A1 WO2016004855 A1 WO 2016004855A1
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WO
WIPO (PCT)
Prior art keywords
thigh
hinge portion
rotation
plane
skeleton
Prior art date
Application number
PCT/CN2015/083465
Other languages
English (en)
French (fr)
Inventor
罗云
甘云
Original Assignee
罗云
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by 罗云 filed Critical 罗云
Priority to CN201580036935.8A priority Critical patent/CN106535833B/zh
Priority to US15/324,727 priority patent/US10765548B2/en
Publication of WO2016004855A1 publication Critical patent/WO2016004855A1/zh

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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
    • A61F5/00—Orthopaedic methods or devices for non-surgical treatment of bones or joints; Nursing devices; Anti-rape devices
    • A61F5/01—Orthopaedic devices, e.g. splints, casts or braces
    • A61F5/0102—Orthopaedic devices, e.g. splints, casts or braces specially adapted for correcting deformities of the limbs or for supporting them; Ortheses, e.g. with articulations
    • A61F5/0123—Orthopaedic devices, e.g. splints, casts or braces specially adapted for correcting deformities of the limbs or for supporting them; Ortheses, e.g. with articulations for the knees
    • 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
    • A61F5/00—Orthopaedic methods or devices for non-surgical treatment of bones or joints; Nursing devices; Anti-rape devices
    • A61F5/01—Orthopaedic devices, e.g. splints, casts or braces
    • A61F5/0102—Orthopaedic devices, e.g. splints, casts or braces specially adapted for correcting deformities of the limbs or for supporting them; Ortheses, e.g. with articulations
    • A61F2005/0132—Additional features of the articulation
    • A61F2005/0134—Additional features of the articulation with two orthogonal pivots
    • 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
    • A61F5/00—Orthopaedic methods or devices for non-surgical treatment of bones or joints; Nursing devices; Anti-rape devices
    • A61F5/01—Orthopaedic devices, e.g. splints, casts or braces
    • A61F5/0102—Orthopaedic devices, e.g. splints, casts or braces specially adapted for correcting deformities of the limbs or for supporting them; Ortheses, e.g. with articulations
    • A61F2005/0132—Additional features of the articulation
    • A61F2005/0165—Additional features of the articulation with limits of movement
    • A61F2005/0167—Additional features of the articulation with limits of movement adjustable

Definitions

  • the present invention relates to an orthosis, and more particularly to a knee orthosis.
  • the lower limbs of the human body refer to the lower part of the abdomen of the human body, including the buttocks, the thighs, the knees, the calves and the feet. They have the important functions of supporting the body to stand and walk, and can also make the body sit, sit, and lie.
  • the main role is to support the weight of the lower limbs of the bone, that is, the lower limb bone, divided into lower limb bone and free lower limb bone.
  • the lower extremity is the hip bone
  • the free lower extremity bone includes the femur, tibia, tibia, and tibia. 7 humerus, 5 tibia and 14 phalanx.
  • the joint between the bone and the bone is called the joint, and the lower limb of the human body includes three joints: the hip joint, the knee joint and the ankle joint, all of which are load-bearing joints.
  • the bone or joint of the human body may be damaged or degraded, and the lesion or degradation of the lower limb bone or lower limb bone joint may seriously affect its weight bearing function, thereby affecting the standing, walking and running jump of the human body.
  • drug therapy traditional physiotherapy and rehabilitation are usually used, and in severe cases, surgical treatment is used to restore the function of the lower limb bone or joint.
  • orthoses are often used.
  • brace is an extracorporeal device used in the limbs or other parts of the human body to prevent and correct deformities, treat bone, joint, nerve, and muscle disorders and compensate for its function. It restricts or assists body movement, or changes the body force line. Reduces dysfunction of the limbs, spine, and skeletal muscle system. Depending on the site of application, it can be divided into an upper limb orthosis, a spinal orthosis, and a lower limb orthosis.
  • the upper limb orthosis is mainly used to compensate for lost muscle strength, support paralyzed limbs, maintain or fix limbs and functional positions, provide traction to prevent contracture and / or prevent or correct deformities;
  • spinal orthoses are mainly used to relieve local pain, protect the lesion from further damage, support paralyzed muscles and / Or prevent or correct deformities;
  • lower limb orthoses are mainly used to fix diseased joints, prevent or correct deformities, compensate for lost muscle function, improve gait, avoid limb weight bearing, promote fracture healing and early functional recovery.
  • the knee joint is one of the important weight-bearing joints of the lower limbs of the human body, as shown in Figure 1, which is connected to the thigh femur 1 and the calf tibia 2 Between, it includes articular cartilage 4 , medial meniscus 5 and lateral meniscus 6 . From the perspective of human kinematics, there are many kinds of motion inside the knee joint when the lower limbs are flexed to straight. For example, when the calf swings back and forth, the range of flexion angle in the passive bending state is 0-140.
  • the thigh can be rotated around the long axis of the calf by a certain angle, called the internal rotation and external rotation of the knee joint (internal rotation and external rotation) ), usually in the active rotation state, the angle is about 30 degrees.
  • knee joint aids for different lesions or injuries are generated.
  • cruciate ligament injury PCL ACL Auxiliary equipment
  • free-loading aids orthoses
  • knee assist devices have two lateral hinges parallel to the rotation plane connecting the thigh skeleton and the calf skeleton, and do not take into account the adduction and abduction of the thigh and the calf when flexing to straightening.
  • the calf support of the flexible strap or the curved rigid structure is often used to press the calf.
  • the calf tibia will be subjected to a large pressure and the soft tissue layer at the forward position is thin, it is more sensitive to the feeling of pressure, and thus the comfort of the existing accessory is very poor.
  • those skilled in the art are directed to developing a knee orthosis that conforms to the movement of the knee joint portion and improves the wearing comfort of the calf portion.
  • the technical problem to be solved by the present invention is to provide a knee orthosis which realizes the movement of the compliant knee joint portion by arranging a connecting structure having two rotational degrees of freedom, and through design combination
  • the type of calf support structure enhances the wearing comfort of the calf portion.
  • the present invention provides a knee orthosis comprising a thigh skeleton for wearing on a thigh of a lower limb and a calf skeleton for wearing on a lower leg of the lower limb, the thigh skeleton being connected to the a calf skeleton, and a rotation between the first position and the second position relative to the calf skeleton about a first axis passing through the joint position of the two; when the thigh skeleton is in the first position,
  • the knee orthosis is adapted to the lower limb in a standing position; wherein the thigh skeleton can also undergo a second relative rotation relative to the calf skeleton, the first axis being opposite the second axis
  • the angle of the rotating plane of rotation is at In the range of 0 to 15°.
  • the knee orthosis further includes a connection structure disposed between the thigh skeleton and the calf skeleton, the connection structure including an adjustment mechanism and a connection hinge through which the thigh skeleton passes The rotation occurs, the second leg rotation of the thigh skeleton through the connecting hinge; the connection position is at the adjustment mechanism.
  • the adjustment mechanism includes a grooved disk and a slider that are rotatable relative to each other, one of the grooved disk and the slider is connected to the thigh skeleton through the connection hinge, and the other is fixedly coupled to the calf skeleton.
  • the thigh skeleton includes two thigh struts that are juxtaposed to each other for fitting the thigh
  • the knee orthosis includes two of the connecting structures, and the connecting hinges of the two connecting structures Separatingly connected to the two thigh struts
  • the connecting hinge includes a first hinge portion and a second hinge portion rotatable relative to each other, the first hinge portion being fixedly coupled to the thigh skeleton, the first a second hinge portion connected to the adjustment mechanism; when the thigh skeleton is in the first position, a rotation axis of the first hinge portion of the two connection hinges relative to the second hinge portion
  • the angle between the first axis is 90° ⁇ 30°, more preferably, the angle of rotation of the first hinge portion of the two connecting hinges relative to the second hinge portion is 90° ⁇ 20° with respect to the first axis .
  • the two thigh support strips are a first thigh support strip for fitting the inner side of the thigh and a second thigh support strip for fitting the outer side of the thigh; Fit the sides of the knee joint separately.
  • the second hinge portion is fixedly coupled to the adjustment mechanism; for one of the thigh struts and a connection hinge and adjustment mechanism connected thereto, the groove plate of the adjustment mechanism and the slider
  • the rotational plane of the relative rotation is a first plane of rotation
  • the plane of rotation of the first hinge portion and the second hinge portion is a second plane of rotation; when the thigh skeleton is in the first position,
  • the angle between the first plane of rotation and the second plane of rotation is 90 ° ⁇ 25 °, more preferably, the angle between the first plane of rotation and the second plane of rotation is 90 ° ⁇ 10 °.
  • the second hinge portion is fixedly coupled to the adjustment mechanism by a rivet or a screw.
  • the second hinge portion is rotatably coupled to the adjustment mechanism; for one of the thigh struts and a connection hinge and adjustment mechanism coupled thereto, the slot plate and the slide of the adjustment mechanism
  • the relatively rotating plane of rotation of the block is a first plane of rotation
  • the plane of rotation of the second hinge portion and the relative rotation of the adjustment mechanism is a third plane of rotation; when the thigh skeleton is in the first position
  • the angle between the second plane of rotation and the third plane of rotation is 90 ° ⁇ 40 °, more preferably, the angle between the second plane of rotation and the third plane of rotation is 90 ° ⁇ 30 °.
  • the second hinge portion is coupled to the adjustment mechanism by a pin, and the relative rotation of the second hinge portion and the adjustment mechanism is performed around the pin.
  • the thigh skeleton when the thigh skeleton is turned from the first position to the second position, the thigh skeleton expands outward; when the thigh skeleton is turned from the second position to the first position, The thigh skeleton is inwardly contracted; the thigh skeleton undergoes the contraction and the expansion through the connecting hinge.
  • the relative rotation plane of the groove plate and the slider of the adjustment mechanism is a first rotation plane
  • the connection hinge includes a first hinge portion and a second hinge that are rotatable relative to each other a portion
  • the rotational plane of the relative rotation of the first hinge portion and the second hinge portion is a second plane of rotation
  • the second hinge portion is rotatably coupled to the adjustment mechanism
  • the second hinge portion is a rotational plane of the relative rotation of the adjustment mechanism is a third rotation plane
  • an angle between the second rotation plane and the third rotation plane is 90 ° ⁇ 40 °, more preferably, the angle between the second plane of rotation and the third plane of rotation is 90 ° ⁇ 30 °.
  • an angle between the first plane of rotation and the first axis is 55°-75°.
  • the thigh skeleton includes two thigh struts that are juxtaposed to each other for fitting the thigh
  • the knee orthosis includes two of the connecting structures, and the connecting hinges of the two connecting structures
  • the first hinge portions are respectively fixedly coupled to one of the thigh skeletons; and when the thigh skeleton is in the first position, the first hinge portions of the two connection hinges are opposite to the second hinge
  • the angle between the partially rotating rotating shaft and the first axis is 90° ⁇ 30°, more preferably, the angle of rotation of the first hinge portion of the two connecting hinges relative to the second hinge portion is 90° ⁇ 20° with respect to the first axis .
  • the two thigh support strips are a first thigh support strip for fitting the inner side of the thigh and a second thigh support strip for fitting the outer side of the thigh;
  • the angle between the groove plate of the two adjustment mechanisms and the relative rotational plane of the slider is 30°-70°.
  • the angle between the first rotating plane and the second rotating plane is 90 ° ⁇ 25 °, more preferably, the angle between the first plane of rotation and the second plane of rotation is 90 ° ⁇ 10 °.
  • the second hinge portion is coupled to the adjustment mechanism by a pin, and the relative rotation of the second hinge portion and the adjustment mechanism is performed around the pin.
  • the second hinge portion is coupled to the first hinge portion by a second pin shaft, and the relative rotation of the first hinge portion and the second hinge portion is performed around the second pin shaft,
  • the second pin axis is perpendicular to a contact surface of the first hinge portion and the second hinge portion.
  • first hinge portion and the second hinge portion have a contact surface, and the pin passes through at least a portion of the first hinge portion and at least a portion of the second hinge portion.
  • first hinge portion and the second hinge portion have a plurality of contact faces, and the pin shaft sequentially passes through at least a portion of the first hinge portion and at least a portion of the second hinge portion .
  • one of the first hinge portion and the second hinge portion has a protrusion extending outward in a direction perpendicular to the second plane of rotation, and the other has a guide groove matching the protrusion Receiving the projection by the guide groove and allowing the projection to rotate therein to effect the relative rotation of the second hinge portion and the adjustment mechanism.
  • the thigh skeleton further includes a thigh support for laterally fitting the front side of the thigh, and the ends of the thigh support strips away from the calf support are connected to the thigh support; the thigh
  • the curved flexible structure has a radius of curvature that becomes smaller as the thigh skeleton contracts inward, and becomes larger as the thigh skeleton expands outward.
  • the thigh support is rotatable about its attachment point to the thigh support.
  • the inner surface of the thigh support has a pad, and the surface of the pad is a mesh-like silica gel layer.
  • a second adjustment mechanism is disposed between the first hinge portion and the thigh support for adjusting and setting a relative position of the first hinge portion and the thigh support.
  • the second adjustment mechanism includes a first set of holes formed in the first hinge portion, and a plurality of sets at the end of the thigh support for cooperating with the first set of holes Two sets of holes and connectors; adjusting and setting by aligning a set of the second set of holes with the first set of holes and fixing the first hinge portion with the thigh struts using a connector a relative position of the first hinge portion to the thigh struts.
  • the second adjustment mechanism includes a first set of teeth disposed at the first hinge portion, and a second set disposed at an end of the thigh support for mating with the first set of teeth a tooth and a connecting member; adjusting and setting the first by adjusting the occlusal position of the first set of teeth and the second set of teeth and fixing the first hinge portion and the thigh struts using a connecting member The relative position of a hinge portion to the thigh struts.
  • the second adjustment mechanism includes a groove disposed at the first hinge portion, a protruding portion disposed at an end of the thigh struts for engaging with the groove, and from both sides Passing through the first hinge portion up to the two set screws of the groove; adjusting the position by adjusting the two set screws against the position of the protruding portion in the groove A relative position of the first hinge portion to the thigh struts is set.
  • the calf skeleton comprises a calf support for laterally fitting the middle portion of the lower leg, the calf support comprising a first portion and a second portion having different curvatures connected at two ends, the second portion being a flexible structure
  • the first portion has a compliance that is less than the second portion and that is disposed outside of the second portion.
  • both ends of the first portion and the second portion are connected by a female pin.
  • the calf skeleton further comprises a butterfly-shaped calf support for fitting the upper part of the lower leg, the calf support comprising an intermediate portion and four wings extending from the intermediate portion, the upper two wings of the calf support Extending upwardly, the two ends are respectively connected to the two adjusting mechanisms, the lower wings are laterally extended, and the two ends are respectively connected to the two ends of the first calf strap, and the first calf strap is used for A rim of the lower leg is spanned at a rhombic depression of the posterior aspect of the lower extremity; an intermediate portion of the shank struts is coupled to the first portion.
  • the two ends of the second portion are connected to both ends of the second lower leg strap, and the second lower leg strap is used to span the calf.
  • the inner surface of the second portion has a gasket, and the surface of the gasket is a mesh-like silica gel layer.
  • the knee orthosis of the present invention comprises a thigh skeleton and a calf skeleton, wherein the thigh skeleton is worn on the thigh and the calf skeleton is worn on the calf.
  • the thigh skeleton is connected to the calf skeleton by connecting a hinge and an adjustment mechanism, and the connection position of the thigh skeleton and the calf skeleton is at the adjustment mechanism.
  • the adjustment mechanism includes portions that are capable of rotating relative to each other, the two portions being coupled to the thigh skeleton and the calf skeleton, respectively, thereby achieving relative rotation between the thigh skeleton and the calf skeleton, following the straight flexion motion of the thigh relative to the lower leg.
  • the thigh skeleton can rotate between the first position and the second position relative to the calf skeleton, wherein when the thigh skeleton is in the first position, the knee orthosis is adapted to the lower limb standing in the upright position, that is, the thigh skeleton and the calf skeleton are at Straightening state, the angle between the two ⁇ 180 °; When the thigh skeleton is in the second position, the knee orthosis is adapted to the lower limb of maximum flexion, that is, the angle between the thigh skeleton and the calf skeleton is ⁇ 30 ° - 40 °.
  • the plane of rotation of the two adjustment mechanisms distributed on the inner and outer sides of the knee joint (the first plane of rotation: the plane in which the part of the adjustment mechanism is rotated relative to the other part, or the plane perpendicular to its axis of rotation) is not parallel, the plane is forward Form an angle.
  • the relative positional relationship between the two adjustment mechanisms and the knee joint is: - In the downward direction, the adjustment mechanism is near the tibial plateau; in the left-right direction, the adjustment mechanism is located near the proximal end of the humerus on both sides of the humerus; In the posterior direction, the adjustment mechanism is about 1/3 of the thickness in the anteroposterior direction of the knee joint.
  • the rotation plane of the two adjustment mechanisms is 30-70° Angle
  • the angle ⁇ of the plane of rotation of the two adjustment mechanisms is 50°
  • the cross section of the human knee joint is narrowed in the front and back of the knee joint, and the middle is wide and approximately elliptical. Therefore, the two adjustment mechanisms at the angle of the range are more compatible with the lower limbs of the human body, making it more light and invisible. .
  • the two connecting hinges are respectively connected to the two thigh struts upwardly, and the two adjusting mechanisms are respectively connected downward.
  • the connecting hinge is composed of a first hinge portion and a second hinge portion which are relatively rotatable, wherein a rotational plane of the relative rotation of the first hinge portion and the second hinge portion is a second plane of rotation; the connecting hinge can be fixed to the adjusting mechanism, It can be rotatably connected to the adjustment mechanism.
  • the thigh skeleton can undergo a second relative rotation with respect to the calf skeleton, the rotational plane of rotation being substantially parallel to the first axis passing through the joint position of the thigh skeleton and the calf skeleton (eg Figure The axis EF ) shown in 15 is generally in the range of 0 to 15° between the first axis and the plane of rotation.
  • the angle of rotation of the first hinge portion of the two connecting hinges relative to the second hinge portion is at an angle with the first axis 90° ⁇ 30° , more preferably, the angle of rotation of the first hinge portion of the two connecting hinges relative to the second hinge portion is 90° ⁇ 20° with the first axis;
  • the angle between the first plane of rotation and the second plane of rotation is 90° ⁇ 25°, and more preferably, the angle between the first plane of rotation and the second plane of rotation is 90° ⁇ 10° .
  • the rotational plane of the relative rotation of the second hinge portion and the adjusting mechanism is a third plane of rotation.
  • the angle of rotation of the first hinge portion of the two connecting hinges relative to the second hinge portion is at an angle to the first axis 90° ⁇ 30°, more preferably, the angle of rotation of the first hinge portion of the two connecting hinges relative to the second hinge portion is 90° ⁇ 20° with respect to the first axis
  • the angle between the second plane of rotation and the third plane of rotation is 90° ⁇ 40°, and more preferably, the angle between the second plane of rotation and the third plane of rotation is 90° ⁇ 30°; the first plane of rotation
  • the angle between the second plane of rotation is 90 ° ⁇ 25 °, more preferably, the angle between the first plane of rotation and the second plane of rotation is 90 ° ⁇ 10 °.
  • the angle range here is to adapt to the shape of different human lower limbs, such as O
  • the design ensures that the thigh skeleton has sufficient degrees of freedom and flexibility, so that the thigh skeleton can not only flex and straighten with the calf skeleton, but also can rotate at a certain angle around the axis of the thigh skeleton, that is, in the background art The internal and external rotations mentioned.
  • the cross-sectional profile of the thigh changes with the buckling state, it is embodied as follows: when the thigh is flexed relatively straight, the cross-sectional profile width is larger, especially in the case of the lower jaw, the soft tissue of the thigh is squeezed, and the width is significantly enlarged. In order to further improve the fit of the accessory and the limb, it is required that the width of both sides of the thigh skeleton changes with the flexion angle.
  • the width of the connection point between the two sides of the thigh skeleton and the adjustment mechanism is also increased, thereby driving the two thigh skeletons.
  • the side width becomes larger, and the width of the thigh contour becomes larger when the chin is lowered.
  • the thigh skeleton is turned toward the calf skeleton (ie, when the thigh skeleton is increased relative to the calf skeleton), the thigh skeleton expands outward (ie, the width of both sides becomes larger); the thigh skeleton is turned away from the calf skeleton.
  • the thigh skeleton contracts inward (ie, the width of both sides becomes smaller).
  • the design is adapted to the actual biomechanical motion of the lower extremity knee joint, ie, including flexion motion and adduction abduction motion along the axial direction of the thigh. If the opposite is true, the adductor of the lower extremity will be suppressed after the accessory is only considered for flexion.
  • the adaptability of the orthosis to different wearers is improved, and the thigh support and the connection hinge are provided with a first
  • the second adjustment mechanism adjusts the relative angles of the two and fixes them after the adjustment is completed.
  • the calf skeleton comprises a calf support, a calf support and a calf strap, and the two ends of the calf support are respectively connected to two adjustment mechanisms, and the middle portion is connected to the calf support.
  • the calf support consists of a rigid first portion and a flexible second portion, similar to a bowstring structure, in which the ends of the second portion (calf chord) are fixed and tensioned on the first portion (calf bracket), the calf chord and There is a certain gap in the middle of the calf support bow.
  • the calf chord is in contact with the calf, so although the calf support spans the lower leg, the main load position on the lower leg effectively avoids the tibia.
  • the entire calf support spans the calf, the calf chord is in contact with the calf, the middle portion is pressed against the humerus, and the rigid portion of the calf support arch is pressed against the soft tissue on both sides of the tibia.
  • the force distribution between the orthosis and the lower leg can be reasonably distributed: mainly by the calf support arch and the soft tissue on both sides of the calf, and indirectly applied to the soft tissue uniformly through the calf chord; Secondly, the middle of the flank of the flank of the calf is pressed against the calf of the calf, which is subjected to less pressure.
  • the flexible calf chord can exert force on the tibia of the calf without excessive pressure, thus greatly improving The comfort of the calf.
  • the inner surface of the thigh support and the calf chord is provided with a layer of breathable and non-slip padding to enhance the load carrying capacity of the orthosis and prevent the orthosis from slipping during wear, preferably with a reticulated silicone gelatin coating.
  • Composite liner it is also possible to arrange a cushion in a position close to the tibia in the upper portion of the lower leg struts to ensure that the lower leg stalk does not damage the lower leg even in an impact state.
  • Figure 1 is a schematic view of the anatomy of the human knee joint.
  • Figure 2 shows Odra's knee assists.
  • Figure 3 is a front elevational view of the knee orthosis of the present invention in a preferred embodiment.
  • Figure 4 is a rear elevational view of the knee orthosis shown in Figure 3.
  • Figure 5 is a side view of the knee orthosis shown in Figure 3.
  • Fig. 6 shows a structure of the joint hinge of the knee orthosis shown in Fig. 3.
  • Figure 7 shows another structure for connecting the hinges.
  • Figure 8 shows yet another structure for connecting the hinges.
  • Figure 9 shows a connection between the connecting hinge and the thigh struts, which allows for discrete adjustment of the angle between the connecting hinge and the thigh struts.
  • Figure 10 shows another connection between the connecting hinge and the thigh struts, which allows for stepless adjustment of the angle between the connecting hinge and the thigh struts.
  • Figure 11 shows the connection of the thigh struts to the thigh rest of the knee orthosis shown in Figure 3.
  • Figure 12 shows the calf skeleton of the knee orthosis shown in Figure 3.
  • Figure 13 is an exploded view of the calf support of the calf skeleton shown in Figure 12.
  • Figure 14 shows a cross section of the calf support of the calf skeleton shown in Figure 12.
  • Figure 15 shows the structure of the adjustment mechanism of the knee orthosis shown in Figure 3 and its connection to the lower leg support.
  • the knee orthosis of the present invention includes a thigh skeleton 20 and a calf skeleton 10, and a thigh skeleton 20 Wear on the thigh, the calf skeleton 10 is worn on the calf.
  • the thigh skeleton 20 includes a thigh support 21, two thigh support strips 22 and 23, and two thigh straps 24 and 25;
  • the calf skeleton 10 Includes calf support 11 , calf support 16 (see Figure 12) and two calf straps 14 and 15;
  • thigh support 22 by connecting hinge 41 and adjustment mechanism 31 Connected to the lower leg support 16 , the thigh support 23 is connected to the lower leg support 16 by a connection hinge 42 and an adjustment mechanism 32.
  • the connecting hinge 41 and the adjusting mechanism 31 constitute a thigh skeleton
  • the working state of the knee orthosis of the present invention includes a first state and a second state, and the adjustment mechanism enables the knee orthosis with the lower limb of the user wearing the knee orthosis of the present invention from the flexed state to the straightened state From the second state to the first state, the thigh skeleton of the knee orthosis in the first state tightly binds the thigh, the calf skeleton tightly binds the calf, and the thigh skeleton applies a force to the thigh along the mechanical axis of the femur and away from the calf, the calf skeleton Applying a force to the lower leg along the mechanical axis of the tibia and away from the thigh; and with the lower limb of the user wearing the knee orthosis of the present invention from the straightened state to the flexed state, the adjustment mechanism causes the knee orthosis from the first The state enters the second state, and the thigh skeleton of the knee orthos
  • the adjustment mechanism in the knee orthosis of the present invention and the Chinese patent application 'Knee joint orthosis with no-load function' is the same, and is composed of a slotted disk and a slider which can be rotated and translated with each other.
  • the present invention is incorporated by reference to the Chinese patent application 'Knee joint orthosis with the function of no load.' (Application No.: 201310347765.8) The description of the adjustment mechanism.
  • the adjustment mechanisms 31 and 32 The plane of rotation (ie, the plane in which the plane slider rotates relative to the grooved disk, or the plane perpendicular to the axis of rotation of the slider and the grooved disk, in this embodiment, the contact plane of the slider and the grooved disk) is not parallel, and the plane direction The front forms an angle.
  • the angle ⁇ of the plane of rotation of the adjustment mechanisms 31 and 32 is preferably at an angle of 30-70, and more preferably, the angle ⁇ is 50°.
  • Figure 6 shows a structure of the connecting hinge and its connection to the slider of the adjustment mechanism.
  • the connection hinge 41 The first hinge portion 411 and the second hinge portion 412 are included, and the first hinge portion 411 is connected to the end of the thigh support 22, and the two can be fixedly connected by screws or the like; the slider 310
  • the end portion has a through hole which is bored on the pin shaft 414 of the second hinge portion 412; the first hinge portion 411 and the second hinge portion 414 are provided with holes for engaging the pin shaft 413, the first hinge portion
  • the hole 411 is further provided with a hole for engaging with the pin 415; one end of the pin shaft 413 has a convex outer edge, a spring is sleeved thereon, and the other end of the pin shaft 413 has a hole for engaging with the pin 415, the pin axis 413 sequentially passes through the second hinge portion 412 and the first hinge portion 411, and the pin 415 sequentially passes through the first hinge portion 411 and the pin 413
  • the connecting hinge 41 has two degrees of freedom: it can rotate about the axis AB relative to the slider 310, i.e. its plane of rotation relative to the slider 310 is the point of contact between the two and perpendicular to the axis
  • the plane of AB; its first hinge portion 411 and second hinge portion 412 may rotate about the axis CD relative to each other, i.e., the first hinge portion 411 is opposite to the second hinge portion 412.
  • the plane of rotation is the plane passing through the contact points of the two and perpendicular to the axis CD.
  • Figure 7 shows another structure of the joint hinge, the first hinge portion 4411 and the second hinge portion of the structure compared to the former structure.
  • the 4412 is also connected by a pin (not shown) along the axis CD, and the second hinge portion 4412 is also passed along the axis AB.
  • the pin shaft is connected to the adjusting mechanism and will not be described here.
  • the first hinge portion 4411 and the second hinge portion 4412 in the structure There are more than one contact faces parallel to the rotational plane of relative rotation between the two, as shown in Figure 7 for three such contact faces. That is, the first hinge portion 4411 and the second hinge portion 4412 There are portions that are embedded in each other and have portions that are joined to each other.
  • the first hinge portion 4411 has a projection 44111
  • the second hinge portion 4412 has a projection 44121
  • the first hinge portion 4411 has a recess for engaging the projection 44121
  • the second hinge portion 4412 has a recess for engaging the projection 44111.
  • the fit of the 412, in this example, the portion of the pin that is subjected to the force perpendicular to its axial direction is longer and has a multi-point force thereon, which has the advantage of better bending resistance, so that the assembled hinge clasp after assembly Precision is not easy to loose.
  • Figure 8 shows another structure of the connecting hinge and its connection to the slider of the adjustment mechanism.
  • the connecting hinge 141 A first hinge portion 1411 and a second hinge portion 1412 are included, and the first hinge portion 1411 is used for the same thigh support 22 The ends are connected, and the two can be fixedly connected by screws or the like (the screws for connecting the two are shown); the second hinge portion 1412 is used for the same slider 1310 The ends are connected, and the two can be fixedly connected by screws or the like (the screws for connecting the two are shown); the end of the first hinge portion 1411 and the second hinge portion 1412 Connected by ball hinges.
  • the first hinge portion 1411 has a protrusion 1415 of the ball stud, the protrusion 1415 includes a ball head and a rod portion, and the second hinge portion 1412 has a guide groove 1414.
  • Below the 1414 is a ball cavity that cooperates with the ball head of the protrusion 1415.
  • the ball cavity is open on the bottom surface of the guide groove 1414; the ball head of the protrusion 1415 is embedded in the ball cavity, and the rod portion is restrained in the guide groove 1414.
  • the first hinge portion 1411 and the second hinge portion 1412 are rotatable in two directions with respect to each other: rotation about the axial direction of the stem portion of the projection 1415, that is, the first hinge portion 1411
  • the plane of rotation relative to the second hinge portion 1412 is a plane passing through the contact points of the two and perpendicular to the axis of the stem; at the center of the ball head passing the projection 1415 and parallel to the guide groove 1414
  • the rotation in the plane of rotation of the extending direction that is, the plane of rotation of the first hinge portion 1411 relative to the second hinge portion 1412 is a point of contact between the two and parallel to the guide groove 1414
  • a second adjustment mechanism may be provided between the first hinge portion and the thigh struts for adjusting and setting the first hinge portion and the thigh
  • the relative position of the struts that is, the first hinge portion and the thigh struts are relatively rotatable connections, and the relative position (angle) of the first hinge portion and the thigh struts can be adjusted to adapt to different users.
  • Figure 9 shows a structure in which the angle between the connecting hinge and the thigh struts can be discretely adjusted
  • FIG. 10 shows a structure in which the angle between the connecting hinge and the thigh struts can be steplessly adjusted.
  • the first hinge portion 2411 and the end of the thigh support 222 are connected by a female screw 2413, and the thigh support The end of the 222 and the first hinge portion 2411 have ratchet teeth that match each other.
  • first loosen the female screw 2413 To adjust the misalignment between the two sets of ratchet teeth to the required angle, and finally tighten the female screw 2413 to fix the first hinge portion 2411 and the thigh support 222.
  • the first hinge portion 3411 The end of the thigh rib 322 is connected by a female screw 3413, and rotation between the two can occur with respect to each other.
  • the end of the thigh rib 322 has a convex portion, and the first hinge portion 3411
  • the upper portion has a groove slightly wider than the convex portion, and the convex portion is inserted into the groove, and each of the two sides of the groove has a set screw 3414 and 3415, and the set screws 3414 and 3415
  • the bulging portion of the thigh rib 322 is held and clamped from both sides.
  • the second adjustment mechanism can also be implemented by means of a connector that cooperates with a selected connection hole.
  • a first set of holes is opened in the first hinge portion, and a plurality of sets of holes are formed at the ends of the thigh struts for engaging the first set of holes, by selecting a set of the second set of holes and the first set
  • the holes are aligned and secured by the connectors through the aligned holes to secure the first hinge portion to the thigh struts, thereby adjusting and setting the relative position of the first hinge portion to the thigh struts.
  • the thigh skeleton 20 includes thigh support 22 and 23, thigh support 21 and cushion 26 .
  • the two thigh struts 22 and 23 have a curved L shape, and the upper end is connected to the thigh support 21
  • the preferred connection method is a hinge connection, and the relative rotation between the thigh support and the thigh support can be performed, and the angle of rotation is within 30°, preferably 10°.
  • the connection between the thigh support and the thigh support is achieved by the female screw, such as the female screw 27 passing through the through hole of the thigh support 22 and the thigh support 21 to realize the thigh support 22 and the thigh support 21 the connection between.
  • the thigh support 21 is made of a flexible material, as in a preferred embodiment, a 65 degree silicone material. Therefore thigh support 21
  • the contour of the surface conforms to the change in the shape of the contour of the thigh during flexion and straightening.
  • connection point between the thigh support 22, 23 and the thigh support 21 is close to the thigh support 21 In the middle portion, a certain distance is maintained between the two connection points, preferably a distance of 0-50 mm. In this embodiment, the spacing is 25 mm.
  • Pad 26 is a non-slip pad that enhances the thigh support 21
  • the load bearing capacity and the knee orthosis of the present invention that is worn are prevented from slipping, in this example a composite liner having a reticulated silicone gelatin coating.
  • the calf skeleton 10 includes a calf support 16 , a calf support 11 and a cushion 17 .
  • the calf support 16 is butterfly-shaped, the upper two wings are respectively connected to the groove plate of the adjusting mechanism 31, 32, the lower two wings are connected with the calf strap 14;
  • the lower leg support 16 is a rigid structure, the calf support 11 It is fixedly attached to the lower leg support 16 and the lower leg support 11 is below the lower leg support 16 and the middle of the two is fixedly connected.
  • the calf support 11 includes a first portion 110 and a second portion 113, the first portion 110 is relatively rigid and has a strip shape, the middle portion of which is fixedly coupled to the lower leg support 16; the second portion 113 is a strip-shaped flexible sheet having a projection 111 and 112 respectively adjacent to the two end portions thereof. Two blind holes are formed between the projections 111 and 112 and the second portion 113 for respectively receiving the two ends of the first portion 110, such as the blind holes 1121.
  • Liner 17 It is a non-slip pad which enhances the load carrying capacity of the calf support 11 and prevents the worn knee orthosis of the present invention from slipping, in this example a composite pad having a reticulated silicone gelatin coating.
  • Calf support 11 For the lateral fit of the middle of the front of the calf, the calf strap 14 is used to straddle the back of the calf in a diamond-shaped depression in the back of the knee, and the calf strap 15 is used to span the calf.
  • Thigh straps 24, 25 and calf straps 14 , 15 structure and material with Chinese patent application '
  • the structure and material of the thigh strap and the calf strap in the knee orthosis with no-load function are the same, and the present invention contains Chinese patent application.
  • the description of the thigh strap and the calf strap in the knee orthosis with no-load function is (Application No.: 201310347765.8).
  • Thigh straps 24, 25 and thigh straps 22 , 23 connection method and the connection of the calf straps 14 and 15 with the calf support 16 and the calf support 11 and the Chinese patent application 'Knee joint orthosis with no load function' (application number: 201310347765.8)
  • the connection of the thigh strap to the thigh splint and the connection of the calf strap to the thigh splint are the same as the Chinese patent application. This part of the description of the knee orthosis with no-load function (Application No.: 201310347765.8).
  • connection method and the connection of the calf straps 14 and 15 with the calf support 16 and the calf support 11 can also be combined with the Chinese patent application 'Quick straps for joint aids' (application number: The connection between the strap and the holder in 201420149171.6) is the same, and the present invention refers to the quick strap of the Chinese patent application 'articulating aid' (application number: This section describes the content in 201420149171.6).

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Abstract

一种膝关节矫形器，包括用于佩戴在下肢的大腿上的大腿骨架（20）和用于佩戴在小腿上的小腿骨架（10），大腿骨架（20）连接到小腿骨架（10），且能绕通过两者的连接位置的第一轴线相对于小腿骨架（10）发生在第一位置和第二位置之间的转动；大腿骨架（20）在第一位置时，膝关节矫形器适应于处于站立正位的下肢；大腿骨架（20）还能发生相对于小腿骨架（10）的第二相对转动，第一轴线与第二相对转动的转动平面的夹角在0到15°的范围内。大腿骨架（20）和小腿骨架（10）之间的连接结构包括调节机构（31）和连接铰链（41），大腿骨架（20）通过调节机构（31）发生上述转动，通过连接铰链（41）发生上述的第二相对转动。上述膝关节矫形器通过连接铰链（41）和调节机构（31），适应了人体下肢在运动中的大腿相对小腿的内、外旋，更符合人体工学及运动学。

Description

膝关节矫形器
技术领域
本发明涉及一种矫形器，尤其涉及一种膝关节矫形器。
背景技术
人体下肢是指人体腹部以下部分，包括臀部、股部、膝部、小腿部和足部，其具有支撑身体站立、步行的重要功能，还可以使身体呈坐位、跪坐、卧位等多种姿势。其中，主要作用为支撑体重的下肢的骨骼，即下肢骨，分为下肢带骨和自由下肢骨两部分。下肢带骨即髋骨，自由下肢骨包括股骨、髌骨、胫骨、腓骨及 7 块跗骨、 5 块跖骨和 14 块趾骨。骨与骨之间连接的地方称为关节，人体下肢包括三大关节：髋关节、膝关节和踝关节，皆为承重关节。
由于老化、生病或意外，人体的骨或关节会发生病变或退化，而人体下肢骨或下肢骨关节的病变或退化可能严重影响其承重功能，进而影响人体的站立、行走以及奔跑跳跃。对此，通常采用药物治疗、传统理疗及康复治疗，严重时采用手术治疗以恢复下肢骨或关节的功能。在康复治疗中，常常使用矫形器。
矫形器（ orthosis ）又称支具（ brace ），是用于人体四肢或其它部位以预防、矫正畸形，治疗骨、关节、神经、肌肉疾患并补偿其功能的体外装置，它通过限制或辅助身体运动，或改变身体力线等作用，以减轻四肢、脊柱、骨骼肌系统的功能障碍。根据适用部位不同，其可以分为上肢矫形器、脊柱矫形器以及下肢矫形器。其中，上肢矫形器主要用于补偿失去的肌力、扶持麻痹的肢体、保持或固定肢体与功能位、提供牵引力以防止挛缩和 / 或预防或矫正畸形；脊柱矫形器主要用于减轻局部疼痛、保护病变部位免受进一步损伤、支持麻痹的肌肉和 / 或预防、矫正畸形；下肢矫形器主要用于固定病变关节、预防或矫正畸形、代偿失去的肌肉功能、改善步态、避免肢体承重、促进骨折愈合和早期功能恢复。
膝关节是人体下肢的重要承重关节之一，如图 1 所示，其连接于大腿股骨 1 和小腿胫骨 2 之间，其包括关节软骨 4 、内侧半月板 5 和外侧半月板 6 。从人体运动学角度分析，人体下肢在屈曲到伸直时，膝关节内部存在多种运动。例如：小腿前后摆动时，其被动弯曲状态下屈曲角范围是 0-140 度；同时大腿能绕小腿长轴轴线旋转一定角度，称为膝关节内、外旋运动（ internal rotation and external rotation ），通常主动旋转状态下，该角度约为 30 度。
由于膝关节在外力冲击或退化病变等原因引起内部结构受损，例如韧带损伤，软骨退化及半月板磨损，最终导致病患膝关节疼痛及运动障碍。为解决上述问题，针对不同病变或损伤的膝关节辅具由此产生。例如针对交叉韧带损伤的 PCL 、 ACL 辅具，及针对膝骨性关节炎的免载辅具（矫形器）等。目前绝大多数的膝关节辅具（矫形器）均具有旋转平面平行的两个侧向铰链连接大腿骨架和小腿骨架，并未考虑到适应大腿与小腿在屈曲到伸直时的内收外展运动，由此此类辅具只能沿侧向铰链的旋转平面发生旋转运动。当患者佩戴此类辅具时，其大腿与小腿的内收外展运动将受到辅具的限制，从而改变了膝关节内部的力学平衡。法国奥德拉（ Odra ）膝关节辅具设计了能够主动内旋的辅具（参见其网站 http://odra.ca/en/ ），如图 2 所示。但是其内旋角度固定，并不一定同所有人的内旋角度相同，并且其侧向铰链同膝关节间的空隙太大，贴合程度低，外观差，极大地影响了用户在使用辅具时的接受度。
另外，目前在大部分需要对小腿正向施加压力以被固定在小腿上的辅具中，多采用柔性绑带或弧形刚性结构的小腿托压迫小腿。但由于小腿胫骨处将承受较大的压力，且正前向位置处的软组织层较薄，其对压力的感受更是敏感，因而现有的这类辅具的舒适性是很差的。
因此，本领域的技术人员致力于开发一种膝关节矫形器，其能顺应的膝关节部分的运动，且提高小腿部分的佩戴舒适性。
发明内容
有鉴于现有技术的上述缺陷，本发明所要解决的技术问题是提供一种膝关节矫形器，通过布置具有两个转动自由度的连接结构实现其顺应的膝关节部分的运动，并通过设计组合型的小腿托结构，提高小腿部分的佩戴舒适性。
为实现上述目的，本发明提供了一种膝关节矫形器，包括用于佩戴在下肢的大腿上的大腿骨架和用于佩戴在所述下肢的小腿上的小腿骨架，所述大腿骨架连接到所述小腿骨架，且能绕通过两者的连接位置的第一轴线相对于所述小腿骨架发生在第一位置和第二位置之间的转动；所述大腿骨架在所述第一位置时，所述膝关节矫形器适应于处于站立正位的所述下肢；其特征在于，所述大腿骨架还能发生相对于所述小腿骨架的第二相对转动，所述第一轴线与所述第二相对转动的转动平面的夹角在 0 到 15° 的范围内。
进一步地，所述膝关节矫形器还包括设置在所述大腿骨架和所述小腿骨架之间的连接结构，所述连接结构包括相连的调节机构和连接铰链，所述大腿骨架通过所述调节机构发生所述转动，所述大腿骨架通过所述连接铰链发生所述第二相对转动；所述连接位置在所述调节机构处。
进一步地，所述调节机构包括可以相对于彼此转动的槽盘和滑块，所述槽盘和所述滑块中的一个通过所述连接铰链与大腿骨架相连，另一个固定连接到所述小腿骨架。
进一步地，所述大腿骨架包括两个用于贴合所述大腿的彼此并立的大腿支条，所述膝关节矫形器包括两个所述连接结构，两个所述连接结构的所述连接铰链与两个所述大腿支条分别地相连；所述连接铰链包括可以相对于彼此转动的第一铰链部分和第二铰链部分，所述第一铰链部分与所述大腿骨架固定连接，所述第二铰链部分与所述调节机构相连；当所述大腿骨架在所述第一位置时，两个所述连接铰链的所述第一铰链部分相对于所述第二铰链部分转动的转动轴与所述第一轴线的夹角为 90°±30° ， 更优选地，两个所述连接铰链的所述第一铰链部分相对于所述第二铰链部分转动的转动轴与所述第一轴线的夹角为 90°±20° 。
进一步地，所述两个大腿支条为用于贴合所述大腿的内侧的第一大腿支条和用于贴合所述大腿的外侧的第二大腿支条；两个所述连接结构用于分别贴合膝关节的两侧。
进一步地，所述第二铰链部分固定连接到所述调节机构；对于一个所述大腿支条和与其相连的连接铰链和调节机构，所述调节机构的所述槽盘和所述滑块的所述相对转动的转动平面为第一转动平面，所述第一铰链部分与所述第二铰链部分的相对转动的转动平面为第二转动平面；当所述大腿骨架在所述第一位置时，所述第一转动平面与所述第二转动平面的夹角为 90°±25° ，更优选地，所述第一转动平面与所述第二转动平面的夹角为 90°±10° 。
进一步地，所述第二铰链部分通过铆钉或螺钉固定连接到所述调节机构。
可选地，所述第二铰链部分可转动地连接到所述调节机构；对于一个所述大腿支条和与其相连的连接铰链和调节机构，所述调节机构的所述槽盘和所述滑块的所述相对转动的转动平面为第一转动平面，所述第二铰链部分与所述调节机构的相对转动的转动平面为第三转动平面；当所述大腿骨架在所述第一位置时，所述第二转动平面与所述第三转动平面的夹角为 90°±40° ，更优选地，所述第二转动平面与所述第三转动平面的夹角为 90°±30° 。
进一步地，所述第二铰链部分通过销轴连接到所述调节机构，所述第二铰链部分与所述调节机构的所述相对转动绕所述销轴进行。
进一步地，在所述大腿骨架从所述第一位置转向所述第二位置时，所述大腿骨架向外扩展；在所述大腿骨架从所述第二位置转向所述第一位置时，所述大腿骨架向内收缩；所述大腿骨架通过所述连接铰链发生所述收缩和所述扩展。
进一步地，所述调节机构的所述槽盘和所述滑块的所述相对转动的转动平面为第一转动平面，所述连接铰链包括可以相对于彼此转动的第一铰链部分和第二铰链部分，所述第一铰链部分与所述第二铰链部分的相对转动的转动平面为第二转动平面，所述第二铰链部分可转动地连接到所述调节机构，所述第二铰链部分与所述调节机构的相对转动的转动平面为第三转动平面；当所述大腿骨架在所述第一位置时，所述第二转动平面与所述第三转动平面的夹角为 90°±40° ，更优选地，所述第二转动平面与所述第三转动平面的夹角为 90°±30° 。
进一步地，所述第一转动平面与所述第一轴线之间的夹角为 55°-75° 。
进一步地，所述大腿骨架包括两个用于贴合所述大腿的彼此并立的大腿支条，所述膝关节矫形器包括两个所述连接结构，两个所述连接结构的所述连接铰链的所述第一铰链部分分别与一个所述大腿骨架固定连接；当所述大腿骨架在所述第一位置时，两个所述连接铰链的所述第一铰链部分相对于所述第二铰链部分转动的转动轴与所述第一轴线的夹角为 90°±30° ， 更优选地，两个所述连接铰链的所述第一铰链部分相对于所述第二铰链部分转动的转动轴与所述第一轴线的夹角为 90°±20° 。
进一步地，所述两个大腿支条为用于贴合所述大腿的内侧的第一大腿支条和用于贴合所述大腿的外侧的第二大腿支条；两个所述连接结构用于分别贴合膝关节的两侧，两个所述调节机构的所述槽盘和所述滑块的所述相对转动的转动平面之间的夹角为 30°-70° 。
进一步地，对于一个所述大腿支条和与其相连的连接铰链和调节机构，当所述大腿骨架在所述第一位置时，所述第一转动平面与所述第二转动平面的夹角为 90°±25° ，更优选地，所述第一转动平面与所述第二转动平面的夹角为 90°±10° 。
进一步地，所述第二铰链部分通过销轴连接到所述调节机构，所述第二铰链部分与所述调节机构的所述相对转动绕所述销轴进行。
进一步地，所述第二铰链部分通过第二销轴连接到所述第一铰链部分，所述第一铰链部分与所述第二铰链部分的所述相对转动绕所述第二销轴进行，所述第二销轴垂直于所述第一铰链部分与所述第二铰链部分的接触面。
可选地，所述第一铰链部分与所述第二铰链部分具有一个接触面，所述销轴依次经过至少部分的所述第一铰链部分与至少部分的所述第二铰链部分。
可选地，所述第一铰链部分与所述第二铰链部分具有多个接触面，所述销轴依次经过交替的至少部分的所述第一铰链部分与至少部分的所述第二铰链部分。
进一步地，所述第一铰链部分与所述第二铰链部分中的一个具有沿垂直于所述第二转动平面的方向向外延伸的凸起，另一个具有与所述凸起匹配的导槽，通过所述导槽接纳所述凸起并允许所述凸起在其中转动实现所述第二铰链部分与所述调节机构的所述相对转动。
进一步地，所述大腿骨架还包括用于横向地贴合在所述大腿正面的大腿托，两个所述大腿支条远离所述小腿支条的端部与所述大腿托相连；所述大腿托为弯曲的柔性结构，其曲率半径在所述大腿骨架向内收缩时变小，在所述大腿骨架向外扩展时变大。
进一步地，所述大腿支条可绕其与所述大腿托的连接点转动。
进一步地，所述大腿托的内表面具有衬垫，所述衬垫的表面为网状的硅胶层。
进一步地，所述第一铰链部分与所述大腿支条之间设置有第二调节机构，用于调节并设定所述第一铰链部分与所述大腿支条的相对位置。
可选地，所述第二调节机构包括开设在所述第一铰链部分的第一组孔、开设在所述大腿支条端部处的多组用于与所述第一组孔配合的第二组孔和连接件；通过选择一组所述第二组孔与所述第一组孔对准并使用连接件将所述第一铰链部分与所述大腿支条固定，实现调节并设定所述第一铰链部分与所述大腿支条的相对位置。
可选地，所述第二调节机构包括设置在所述第一铰链部分的第一组齿、设置在所述大腿支条端部处的用于与所述第一组齿配合的第二组齿和连接件；通过调节所述第一组齿和所述第二组齿的咬合位置并使用连接件将所述第一铰链部分与所述大腿支条固定，实现调节并设定所述第一铰链部分与所述大腿支条的相对位置。
可选地，所述第二调节机构包括设置在所述第一铰链部分的凹槽、设置在所述大腿支条端部处的用于与所述凹槽配合的凸出部分和从两侧穿过所述第一铰链部分直到所述凹槽的两个紧定螺丝；通过调节所述两个紧定螺丝使其抵触在所述凹槽中的所述凸出部分的位置，实现调节并设定所述第一铰链部分与所述大腿支条的相对位置。
进一步地，所述小腿骨架包括用于横向贴合所述小腿的中部的小腿托，所述小腿托包括两端分别相连的曲率不同的第一部分和第二部分，所述第二部分为柔性结构，所述第一部分的柔度小于所述第二部分，其被布置在所述第二部分之外。
进一步地，所述第一部分和所述第二部分的两端通过子母钉连接。
进一步地，所述小腿骨架还包括用于贴合小腿上部的蝶形的小腿支条，所述小腿支条包括中间部分和从所述中间部分延伸的四个翼，所述小腿支条上部两翼向上弯曲地延伸，其两个端部分别连接所述两个调节机构，下部两翼横向延伸，其两个端部分别与第一小腿绑带的两端相连，所述第一小腿绑带用于在所述下肢的膝后区的菱形凹陷处横跨所述小腿的背面；所述小腿支条的中间部分与所述第一部分相连。
进一步地，所述第二部分的所述两端与第二小腿绑带的两端相连，所述第二小腿绑带用于横跨所述小腿肚。
进一步地，所述第二部分的内表面具有衬垫，所述衬垫的表面为网状的硅胶层。
在一个较佳的实施例中，本发明的膝关节矫形器包括大腿骨架和小腿骨架，其中，大腿骨架佩戴于大腿，小腿骨架佩戴于小腿。大腿骨架通过连接铰链和调节机构与小腿骨架相连，大腿骨架和小腿骨架的连接位置在调节机构处。调节机构包括能够发生相对彼此转动的部分，这两部分分别与大腿骨架和小腿骨架相连，由此实现大腿骨架与小腿骨架之间的相对转动，跟随大腿相对小腿的伸直屈曲运动。大腿骨架能相对于小腿骨架发生在第一位置和第二位置之间的转动，其中大腿骨架在第一位置时，膝关节矫形器适应于处于站立正位的下肢，即大腿骨架和小腿骨架处于伸直状态，两者间夹角～ 180 ° ；大腿骨架在第二位置时，膝关节矫形器适应于处于最大屈曲的下肢，即大腿骨架和小腿骨架之间夹角～ 30 °-40° 。
分布在膝关节内外两侧的两个调节机构的转动平面（第一转动平面：调节机构的一部分相对于另一部分发生相对转动的平面，或垂直于其旋转轴的平面）不平行，平面向前形成夹角。佩戴本发明的膝关节矫形器时，两个调节机构与膝关节的相对位置关系为：在上 - 下的方向上，调节机构处在胫骨平台附近；在左 - 右的方向上，调节机构处在髌骨两侧的胫骨近端位置附近；在前 - 后的方向上，调节机构处在膝关节前后方向厚度上约前 1/3 处。通常两个调节机构的旋转平面呈 30-70° 夹角，在本发明的一个较佳的设计中，两个调节机构的旋转平面的夹角 α （如图 15 所示）为 50° 。人体膝关节的横截面呈由于膝关节的横断面前后窄，中间宽，近似椭圆形状，因此呈该范围的夹角的两个调节机构更能与人体下肢的贴合程度，使其更加轻便隐形。
在一个较佳的实施例中，两个连接铰链向上分别连接两个大腿支条，向下分别连接两个调节机构。连接铰链由可发生相对转动的第一铰链部分和第二铰链部分构成，其中第一铰链部分与第二铰链部分的相对转动的转动平面为第二转动平面；连接铰链可以固定于调节机构，也可以可转动地连接于调节机构。通过第一铰链部分和第二铰链的相对转动，大腿骨架能发生相对于小腿骨架的第二相对转动，该转动的转动平面基本平行于通过大腿骨架和小腿骨架的连接位置的第一轴线（如图 15 中所示的轴线 EF ），通常第一轴线与该转动平面的夹角在 0 到 15° 的范围内。
当连接铰链固定于调节机构，较佳地，当大腿骨架在所述第一位置时，两个连接铰链的第一铰链部分相对于第二铰链部分转动的转动轴与第一轴线的夹角为 90°±30° ， 更优选地，两个连接铰链的第一铰链部分相对于第二铰链部分转动的转动轴与第一轴线的夹角为 90°±20° ； 第一转动平面与第二转动平面的夹角为 90°±25° ，更优选地，第一转动平面与第二转动平面的夹角为 90°±10° 。当连接铰链可转动地连接于调节机构，第二铰链部分与调节机构的相对转动的转动平面为第三转动平面。较佳地，大腿骨架在第一位置时，两个连接铰链的第一铰链部分相对于第二铰链部分转动的转动轴与第一轴线的夹角为 90°±30° ， 更优选地，两个连接铰链的第一铰链部分相对于第二铰链部分转动的转动轴与第一轴线的夹角为 90°±20° ；第二转动平面与所述第三转动平面的夹角为 90°±40° ，更优选地，第二转动平面与第三转动平面的夹角为 90°±30° ；第一转动平面与第二转动平面的夹角为 90°±25° ，更优选地，第一转动平面与第二转动 平面的夹角为 90°±10° 。这里的角度范围是为了适应不同人体下肢的形状，例如 O 型腿、 X 型腿等。
该设计保证了大腿骨架具有足够的自由度和柔性特点，使得大腿骨架不仅能够与小腿骨架发生屈曲和伸直运动，同时其能够绕大腿骨架的轴的方向发生一定角度的旋转，即背景技术中提到的内、外旋运动。
此外，由于大腿的截面轮廓会随屈曲状态发生变化，具体体现为：大腿屈曲相对伸直时其截面轮廓宽度更大，尤其是在下蹲时，大腿软组织收到挤压，宽度明显变大，由此为进一步提高辅具与肢体的贴合程度就需要大腿骨架两侧宽度随屈曲角度变化而变化。由于两个调节机构的旋转平面向后张开，因此，当大腿骨架相对小腿骨架屈曲角增大时，大腿骨架两侧与调节机构的连接点的宽度也随之增大，因而带动大腿骨架两侧宽度变大，适应了下蹲时大腿轮廓宽度变大的现象。具体地为，在大腿骨架转向小腿骨架的同时（即当大腿骨架相对小腿骨架屈曲角增大时），大腿骨架向外扩展（即其两侧宽度变大）；在大腿骨架转离小腿骨架的同时（即当大腿骨架相对小腿骨架屈曲角减小时），大腿骨架向内收缩（即其两侧宽度变小）。由此，该设计适应于人体下肢膝关节的实际生物力学运动，即包含屈曲运动和沿大腿轴向的内收外展运动。若反之，在佩戴上只考虑屈曲运动的辅具后，下肢的内收外展运动将会被抑制。
在一个较佳的实施例中，为适应不同的佩戴者腿的粗细程度及站立态髋膝踝角不同，提高矫形器对不同佩戴者的适应性，大腿支条与连接铰链之间设置有第二调节机构，对两者的相对角度进行调整并在完成调节后固定。
在一个较佳的实施例中，小腿骨架包括小腿支条、小腿托和小腿绑带，小腿支条的两个端部分别连接两个调节机构，中部连接小腿托。
小腿托由刚性的第一部分和柔性的第二部分构成，类似弓弦的结构，其中第二部分（小腿托弦）的两端固定并张紧在第一部分（小腿托弓）上，小腿托弦与小腿托弓中部保有一定间隙。小腿托弦与小腿接触，因此虽然小腿托横跨于小腿，但在小腿上的主要承载位置有效地避开了胫骨。整个小腿托横跨于小腿上，小腿托弦与小腿接触，其中部压于胫骨位置，小腿托弓的刚性部分压于胫骨两侧的软组织位置。因此，对在佩戴矫形器时，矫形器与小腿之间的力分布能合理的分配：主要通过小腿托弓与小腿两侧的软组织承担，并且间接地通过小腿托弦均匀地施加在软组织上；其次，片状小腿托弦的中部压于小腿胫骨上，其承受较小的压力，柔性的小腿托弦能够将力均有地施加在小腿胫骨上，不会出现压力过大情况，从而大大提高了小腿的舒适性。此外，大腿托及小腿托弦的内表面均附有一层透气且防滑衬垫，以增强矫形器的承载能力和防止矫形器在佩戴时下滑，较佳地为具有网状硅胶滴胶涂层的复合衬垫。此外，还可以在小腿支条的上部中与胫骨接近的位置布置缓冲垫，以保证小腿支条即使在冲击状态下也不会对损伤小腿。
以下将结合附图对本发明的构思、具体结构及产生的技术效果作进一步说明，以充分地了解本发明的目的、特征和效果。
附图说明
图 1 是人体膝关节的解剖结构示意图。
图 2 显示了奥德拉的膝关节辅具。
图 3 是一个较佳的实施例中，本发明的膝关节矫形器正视图。
图 4 是图 3 示出的膝关节矫形器的后视图。
图 5 是图 3 所示的膝关节矫形器的侧视图。
图 6 示出了图 3 所示的膝关节矫形器的连接铰链的一种结构。
图 7 示出了连接铰链的另一种结构。
图 8 示出了连接铰链的又一种结构。
图 9 示出了连接铰链与大腿支条的一种连接方式，可以对连接铰链与大腿支条间的夹角进行离散调节。
图 10 示出了连接铰链与大腿支条的另一种连接方式，可以对连接铰链与大腿支条间的夹角进行无级调节。
图 11 示出了图 3 所示的膝关节矫形器的大腿支条与大腿托的连接。
图 12 示出了图 3 所示的膝关节矫形器的小腿骨架。
图 13 是图 12 所示的小腿骨架的小腿托的爆炸图。
图 14 示出了图 12 所示的小腿骨架的小腿托的横截面。
图 15 示出了图 3 所示的膝关节矫形器的调节机构的结构及其与小腿支条的连接。
具体实施方式
如图 3-5 所示，本发明的膝关节矫形器包括大腿骨架 20 和小腿骨架 10 ，大腿骨架 20 佩戴于大腿，小腿骨架 10 佩戴于小腿。其中，大腿骨架 20 包括大腿托 21 、两个大腿支条 22 和 23 以及两个大腿绑带 24 和 25 ；小腿骨架 10 包括小腿托 11 、小腿支条 16 （参见图 12 ）以及两个小腿绑带 14 和 15 ；大腿支条 22 通过连接铰链 41 和调节机构 31 连接到小腿支条 16 ，大腿支条 23 通过连接铰链 42 和调节机构 32 连接到小腿支条 16 。其中，连接铰链 41 和调节机构 31 构成大腿骨架 20 和小腿骨架 10 之间的连接结构。
本发明的膝关节矫形器的工作状态包括第一状态和第二状态，随着佩戴了本发明的膝关节矫形器的使用者的下肢从屈曲状态到伸直状态，调节机构使膝关节矫形器从第二状态进入第一状态，处于第一状态的膝关节矫形器的大腿骨架紧束缚大腿，小腿骨架紧束缚小腿，大腿骨架对大腿施加沿股骨机械轴且背离小腿的方向的力，小腿骨架对小腿施加沿胫骨机械轴且背离大腿的方向的力；而随着佩戴了本发明的膝关节矫形器的使用者的下肢从伸直状态到屈曲状态，调节机构使膝关节矫形器从第一状态进入第二状态，处于第二状态的膝关节矫形器的大腿骨架松束缚大腿，小腿骨架松束缚小腿，大腿骨架不对大腿施加沿股骨机械轴且背离小腿的方向的力，小腿骨架不对小腿施加沿胫骨机械轴且背离大腿的方向的力。这是与中国专利申请 ' 具有免荷功能的膝关节矫形器 ' （申请号： 201310347765.8 ）的膝关节矫形器的工作状态相同的，本发明引用包含中国专利申请 ' 具有免荷功能的膝关节矫形器 ' （申请号： 201310347765.8 ）中的这些描述内容。
本发明的膝关节矫形器中的调节机构与中国专利申请 ' 具有免荷功能的膝关节矫形器 ' （申请号： 201310347765.8 ）中的调节机构相同，皆由可相互转动及平动的槽盘和滑块构成，本发明引用包含中国专利申请 ' 具有免荷功能的膝关节矫形器 ' （申请号： 201310347765.8 ）中关于调节机构的描述内容。以调节机构 31 为例，其中的槽盘与小腿支条固定连接（与中国专利申请 ' 具有免荷功能的膝关节矫形器 ' （申请号： 201310347765.8 ）中的调节机构的槽盘和小腿夹板的固定连接相同，在此不赘述），滑块 310 通过连接铰链 41 连接到大腿支条 22 。
在本发明中，调节机构 31 和 32 的旋转平面（即平面滑块与槽盘发生相对转动的平面，或者垂直于滑块与槽盘的旋转轴的平面，本实施例中为滑块与槽盘的接触平面）不平行，平面向前形成夹角。具体地如图 15 所示，调节机构 31 和 32 的旋转平面的夹角 α 较佳地呈 30-70° 夹角，更优选地，夹角 α 为 50° 。
图 6 示出了连接铰链的一种结构及其与调节机构的滑块的连接方式。如图 6 所示，连接铰链 41 包括第一铰链部分 411 和第二铰链部分 412 ，第一铰链部分 411 用于同大腿支条 22 的端部相连，两者可以通过螺钉等方式实现固定连接；滑块 310 的端部具有通孔，其穿设在第二铰链部分 412 的销轴 414 上；第一铰链部分 411 和第二铰链部分 414 上设有配合销轴 413 的孔，第一铰链部分 411 上还设有与销 415 配合的孔；销轴 413 的一个端部具有凸出的外缘，其上套设弹簧，销轴 413 的另一个端部上具有与销 415 配合的孔，销轴 413 依次穿过第二铰链部分 412 和第一铰链部分 411 ，销 415 依次穿过第一铰链部分 411 和销轴 413 ，由此完成连接铰链 41 的组装。连接铰链 41 具有两个自由度：其相对于滑块 310 可发生绕轴线 AB 的转动，即其相对于滑块 310 的转动平面为经过两者的接触点并垂直于轴线 AB 的平面；其第一铰链部分 411 和第二铰链部分 412 可发生相对于彼此的绕轴线 CD 的转动，即第一铰链部分 411 相对于第二铰链部分 412 的转动平面为经过两者的接触点并垂直于轴线 CD 的平面。
图 7 示出了连接铰链的另一种结构，与前一种结构相比，本结构中的第一铰链部分 4411 和第二铰链部分 4412 也是通过沿轴线 CD 的销轴（未图示）连接，第二铰链部分 4412 也是通过沿轴线 AB 的销轴与调节机构相连，在此不赘述。与前一种结构不同的是，本结构中的第一铰链部分 4411 和第二铰链部分 4412 具有多于一个的平行于两者间相对转动的转动平面的接触面，如图 7 中示出了 3 个这样的接触面。即第一铰链部分 4411 和第二铰链部分 4412 具有彼此嵌入对方的部分，又具有彼此接合对方的部分。如，第一铰链部分 4411 具有凸出部 44111 ，第二铰链部分 4412 具有凸出部 44121 ；第一铰链部分 4411 具有用于接合凸出部 44121 的凹槽，第二铰链部分 4412 具有用于接合凸出部 44111 的凹槽。当将第一铰链部分 4411 和第二铰链部分 4412 的凸出部与对应的凹槽配合后完成两者的组装，由于通过轴线 CD 的销轴依次经过部分的第一铰链部分 4411 、部分的第二铰链部分 4412 、部分的第一铰链部分 4411 和部分的第二铰链部分 4412 。可以看到相对于前一个示例中的只有一个接触面的第一铰链部分 411 和第二铰链部分 412 的配合，在本示例中，承受垂直于其轴向的力的销轴的部分更长，其上为多点受力，这具有抗弯曲效果更好的优点，从而装配后的连接铰链扣合精密不易松脱。
图 8 示出了连接铰链的另一种结构及其与调节机构的滑块的连接方式。如图 8 所示，连接铰链 141 包括第一铰链部分 1411 和第二铰链部分 1412 ，第一铰链部分 1411 用于同大腿支条 22 的端部相连，两者可以通过螺钉等方式实现固定连接（图中示出了用于连接两者的螺钉）；第二铰链部分 1412 用于同滑块 1310 的端部相连，两者可以通过螺钉等方式实现固定连接（图中示出了用于连接两者的螺钉）；第一铰链部分 1411 的端部与第二铰链部分 1412 通过球铰连接。第一铰链部分 1411 具有一个的球头杆的凸起 1415 ，凸起 1415 包括球头部及杆部；第二铰链部分 1412 具有导槽 1414 ，导槽 1414 的下方是与凸起 1415 的球头部配合的球腔，球腔在导槽 1414 的底面上开口；凸起 1415 的球头部嵌入到球腔内，杆部被限制在导槽 1414 内。第一铰链部分 1411 与第二铰链部分 1412 相对于彼此能发生两个方向的转动：绕凸起 1415 的杆部的轴线方向的旋转，即第一铰链部分 1411 相对于第二铰链部分 1412 的转动平面为经过两者的接触点并垂直于杆部的轴线的平面；在经过凸起 1415 的球头部的中心且平行于导槽 1414 的延伸方向的旋转平面内的旋转，即第一铰链部分 1411 相对于第二铰链部分 1412 的转动平面为经过两者的接触点并平行于导槽 1414 的延伸方向的平面。
除了上述的第一铰链部分同大腿支条的端部间的固定的连接方式，第一铰链部分同大腿支条间还可以设置第二调节机构，用于调节并设定第一铰链部分与大腿支条的相对位置，即第一铰链部分同大腿支条间为是能发生相对转动的连接，可以调节第一铰链部分同大腿支条的相对位置（夹角），从而适应于不同的使用者的需求。图 9 示出了可对连接铰链与大腿支条间的夹角进行离散调节的结构，图 10 示出了可对连接铰链与大腿支条间的夹角进行无级调节的结构。
如图 9 所示，第一铰链部分 2411 与大腿支条 222 的端部通过子母螺丝 2413 连接，大腿支条 222 的端部与第一铰链部分 2411 具有相互匹配的棘齿。在调节两者间的相对位置时，先松开子母螺丝 2413 ，调节两组棘齿的齿间错位至需要的角度，最后旋紧子母螺丝 2413 以固定第一铰链部分 2411 与大腿支条 222 。如图 10 所示，第一铰链部分 3411 与大腿支条 322 的端部通过子母螺丝 3413 连接，两者间可以发生相对于彼此的转动，大腿支条 322 的端部有一个凸出部分，第一铰链部分 3411 上具有比该凸处部分略宽的凹槽，该凸处部分插入到该凹槽中，凹槽两侧各有一个紧定螺丝 3414 和 3415 ，紧定螺丝 3414 和 3415 从两侧顶住并夹紧大腿支条 322 的凸出部分。在调节第一铰链部分 3411 与大腿支条 322 间的相对位置时，通过旋转紧定螺丝 3414 和 3415 ，控制大腿支条 322 的凸出部分的移动以控制大腿支条 322 相对于第一铰链部分 3411 转动至需要的角度。
另外，第二调节机构还可以采用连接件与选择的连接孔配合的方式实现。例如，在第一铰链部分开设第一组孔、在大腿支条端部处开设的多组用于与第一组孔配合的第二组孔，通过选择一组第二组孔与第一组孔对准并使用连接件穿过彼此对准的孔来将第一铰链部分与所述大腿支条固定，就能实现调节并设定第一铰链部分与大腿支条的相对位置。
如图 11 所示，大腿骨架 20 包含大腿支条 22 和 23 、大腿托 21 及衬垫 26 。其中，两个大腿支条 22 和 23 呈弯曲的 L 形状，其上端连接大腿托 21 ，较佳的连接方式为铰链连接，大腿支条和大腿托之间可以发生相对转动，转动的角度范围在 30° 以内，较佳地为 10° 以内。本实施例中，大腿支条和大腿托之间通过子母螺丝实现连接，如子母螺丝 27 穿过大腿支条 22 和大腿托 21 上的通孔，实现大腿支条 22 和大腿托 21 之间的连接。大腿托 21 为柔性材料制作而成，如较佳的一个实施例中为 65 度的硅胶材质。因此大腿托 21 的曲面轮廓可顺应屈曲与伸直过程中大腿的轮廓形状的变化。
大腿支条 22 、 23 与大腿托 21 的连接点靠近大腿托 21 的中部，同时两个连接点之间保持一定距离，较好的为 0-50mm 的距离，本实施例中，该间距为 25mm 。衬垫 26 是防滑衬垫，其可以增强大腿托 21 的承载能力并能防止佩戴的本发明的膝关节矫形器下滑，本实例中为具有网状硅胶滴胶涂层的复合衬垫。
如图 12-13 所示，小腿骨架 10 包括小腿支条 16 、小腿托 11 和衬垫 17 。其中，小腿支条 16 呈蝶形，其上部的两翼分别连接调节机构 31 、 32 的槽盘，其下部的两翼连接小腿绑带 14 ；小腿支条 16 为刚性结构，小腿托 11 固定连接在小腿支条 16 上，小腿托 11 在小腿支条 16 的下方，两者的中部固定连接。小腿托 11 包括第一部分 110 和第二部分 113 ，第一部分 110 刚性较大，其呈条状，其中部固定连接到小腿支条 16 ；第二部分 113 为条状柔性片，在接近其两个端部的位置上分别设有一个凸起 111 和 112 ，凸起 111 和 112 与第二部分 113 之间构成两个盲孔，用于分别容纳第一部分 110 的两个端部，如盲孔 1121 。如图 14 所示的小腿托 11 的横截面，小腿托 11 呈弓弦结构，其第一部分 110 和第二部分 113 在两端相连，中间部分分离，本实施例中，两者的中部的间隙为 8mm 。衬垫 17 是防滑衬垫，其可以增强小腿托 11 的承载能力并能防止佩戴的本发明的膝关节矫形器下滑，本实例中为具有网状硅胶滴胶涂层的复合衬垫。小腿托 11 用于横向贴合小腿正面的中部，小腿绑带 14 用于在膝后区的菱形凹陷处横跨小腿的背面，小腿绑带 15 用于横跨小腿肚。
大腿绑带 24 、 25 以及小腿绑带 14 、 15 的结构和材质与中国专利申请 ' 具有免荷功能的膝关节矫形器 ' （申请号： 201310347765.8 ）中的大腿绑带以及小腿绑带的结构和材质相同，本发明引用包含中国专利申请 ' 具有免荷功能的膝关节矫形器 ' （申请号： 201310347765.8 ）中关于大腿绑带以及小腿绑带的描述内容。大腿绑带 24 、 25 与大腿支条 22 、 23 的连接方式以及小腿绑带 14 、 15 与小腿支条 16 和小腿托 11 的连接方式与中国专利申请 ' 具有免荷功能的膝关节矫形器 ' （申请号： 201310347765.8 ）中的大腿绑带与大腿夹板的连接方式以及小腿绑带与大腿夹板的连接方式相同，本发明引用包含中国专利申请 ' 具有免荷功能的膝关节矫形器 ' （申请号： 201310347765.8 ）中的这部分描述内容。另外，大腿绑带 24 、 25 与大腿支条 22 、 23 的连接方式以及小腿绑带 14 、 15 与小腿支条 16 和小腿托 11 的连接方式还可以与中国专利申请 ' 关节辅具的快速绑带 ' （申请号： 201420149171.6 ）中的绑带和固定架之间的连接方式相同，本发明引用包含中国专利申请 ' 关节辅具的快速绑带 ' （申请号： 201420149171.6 ）中这部分描述内容。
以上详细描述了本发明的较佳具体实施例。应当理解，本领域的普通技术人员无需创造性劳动就可以根据本发明的构思做出诸多修改和变化。因此，凡本技术领域的技术人员依本发明的构思在现有技术的基础上通过逻辑分析、推理或者有限的实验可以得到的技术方案，皆应在由权利要求书所确定的保护范围内。

Claims (32)

  1. 一种膝关节矫形器，包括用于佩戴在下肢的大腿上的大腿骨架和用于佩戴在所述下肢的小腿上的小腿骨架，所述大腿骨架连接到所述小腿骨架，且能绕通过两者的连接位置的第一轴线相对于所述小腿骨架发生在第一位置和第二位置之间的转动；所述大腿骨架在所述第一位置时，所述膝关节矫形器适应于处于站立正位的所述下肢；其特征在于，所述大腿骨架还能发生相对于所述小腿骨架的第二相对转动，所述第一轴线与所述第二相对转动的转动平面的夹角在0到15°的范围内。
  2. 如权利要求1所述的膝关节矫形器，其中还包括设置在所述大腿骨架和所述小腿骨架之间的连接结构，所述连接结构包括相连的调节机构和连接铰链，所述大腿骨架通过所述调节机构发生所述转动，所述大腿骨架通过所述连接铰链发生所述第二相对转动；所述连接位置在所述调节机构处。
  3. 如权利要求2所述的膝关节矫形器，其中所述调节机构包括可以相对于彼此转动的槽盘和滑块，所述槽盘和所述滑块中的一个通过所述连接铰链与大腿骨架相连，另一个固定连接到所述小腿骨架。
  4. 如权利要求3所述的膝关节矫形器，其中所述大腿骨架包括两个用于贴合所述大腿的彼此并立的大腿支条，所述膝关节矫形器包括两个所述连接结构，两个所述连接结构的所述连接铰链与两个所述大腿支条分别地相连；所述连接铰链包括可以相对于彼此转动的第一铰链部分和第二铰链部分，所述第一铰链部分与所述大腿骨架固定连接，所述第二铰链部分与所述调节机构相连；当所述大腿骨架在所述第一位置时，两个所述连接铰链的所述第一铰链部分相对于所述第二铰链部分转动的转动轴与所述第一轴线的夹角为90°±30°，更优选地，两个所述连接铰链的所述第一铰链部分相对于所述第二铰链部分转动的转动轴与所述第一轴线的夹角为90°±20°。
  5. 如权利要求4所述的膝关节矫形器，其中所述两个大腿支条为用于贴合所述大腿的内侧的第一大腿支条和用于贴合所述大腿的外侧的第二大腿支条；两个所述连接结构用于分别贴合膝关节的两侧。
  6. 如权利要求4或5所述的膝关节矫形器，其中所述第二铰链部分固定连接到所述调节机构；对于一个所述大腿支条和与其相连的连接铰链和调节机构，所述调节机构的所述槽盘和所述滑块的所述相对转动的转动平面为第一转动平面，所述第一铰链部分与所述第二铰链部分的相对转动的转动平面为第二转动平面；当所述大腿骨架在所述第一位置时，所述第一转动平面与所述第二转动平面的夹角为90°±25°，更优选地，所述第一转动平面与所述第二转动平面的夹角为90°±10°。
  7. 如权利要求6所述的膝关节矫形器，其中所述第二铰链部分通过铆钉或螺钉固定连接到所述调节机构。
  8. 如权利要求4或5所述的膝关节矫形器，其中所述第二铰链部分可转动地连接到所述调节机构；对于一个所述大腿支条和与其相连的连接铰链和调节机构，所述调节机构的所述槽盘和所述滑块的所述相对转动的转动平面为第一转动平面，所述第二铰链部分与所述调节机构的相对转动的转动平面为第三转动平面；当所述大腿骨架在所述第一位置时，所述第二转动平面与所述第三转动平面的夹角为90°±40°，更优选地，所述第二转动平面与所述第三转动平面的夹角为90°±30°。
  9. 如权利要求9所述的膝关节矫形器，其中所述第二铰链部分通过销轴连接到所述调节机构，所述第二铰链部分与所述调节机构的所述相对转动绕所述销轴进行。
  10. 如权利要求3所述的膝关节矫形器，其中在所述大腿骨架从所述第一位置转向所述第二位置时，所述大腿骨架向外扩展；在所述大腿骨架从所述第二位置转向所述第一位置时，所述大腿骨架向内收缩；所述大腿骨架通过所述连接铰链发生所述收缩和所述扩展。
  11. 如权利要求10所述的膝关节矫形器，其中所述调节机构的所述槽盘和所述滑块的所述相对转动的转动平面为第一转动平面，所述连接铰链包括可以相对于彼此转动的第一铰链部分和第二铰链部分，所述第一铰链部分与所述第二铰链部分的相对转动的转动平面为第二转动平面，所述第二铰链部分可转动地连接到所述调节机构，所述第二铰链部分与所述调节机构的相对转动的转动平面为第三转动平面；当所述大腿骨架在所述第一位置时，所述第二转动平面与所述第三转动平面的夹角为90°±40°，更优选地，所述第二转动平面与所述第三转动平面的夹角为90°±30°。
  12. 如权利要求11所述的膝关节矫形器，其中所述第一转动平面与所述第一轴线之间的夹角为55°-75°。
  13. 如权利要求12所述的膝关节矫形器，其中所述大腿骨架包括两个用于贴合所述大腿的彼此并立的大腿支条，所述膝关节矫形器包括两个所述连接结构，两个所述连接结构的所述连接铰链的所述第一铰链部分分别与一个所述大腿骨架固定连接；当所述大腿骨架在所述第一位置时，两个所述连接铰链的所述第一铰链部分相对于所述第二铰链部分转动的转动轴与所述第一轴线的夹角为90°±30°，更优选地，两个所述连接铰链的所述第一铰链部分相对于所述第二铰链部分转动的转动轴与所述第一轴线的夹角为90°±20°。
  14. 如权利要求13所述的膝关节矫形器，其中所述两个大腿支条为用于贴合所述大腿的内侧的第一大腿支条和用于贴合所述大腿的外侧的第二大腿支条；两个所述连接结构用于分别贴合膝关节的两侧，两个所述调节机构的所述槽盘和所述滑块的所述相对转动的转动平面之间的夹角为30°-70°。
  15. 如权利要求14所述的膝关节矫形器，其中对于一个所述大腿支条和与其相连的连接铰链和调节机构，当所述大腿骨架在所述第一位置时，所述第一转动平面与所述第二转动平面的夹角为90°±25°，更优选地，所述第一转动平面与所述第二转动平面的夹角为90°±10°。
  16. 如权利要求15所述的膝关节矫形器，其中所述第二铰链部分通过销轴连接到所述调节机构，所述第二铰链部分与所述调节机构的所述相对转动绕所述销轴进行。
  17. 如权利要求4、5、7、9、11-16中任何一个所述的膝关节矫形器，其中所述第二铰链部分通过第二销轴连接到所述第一铰链部分，所述第一铰链部分与所述第二铰链部分的所述相对转动绕所述第二销轴进行，所述第二销轴垂直于所述第一铰链部分与所述第二铰链部分的接触面。
  18. 如权利要求17所述的膝关节矫形器，其中所述第一铰链部分与所述第二铰链部分具有一个接触面，所述销轴依次经过至少部分的所述第一铰链部分与至少部分的所述第二铰链部分。
  19. 如权利要求17所述的膝关节矫形器，其中所述第一铰链部分与所述第二铰链部分具有多个接触面，所述销轴依次经过交替的至少部分的所述第一铰链部分与至少部分的所述第二铰链部分。
  20. 如权利要求4、5、7、9、11-16中任何一个所述的膝关节矫形器，其中所述第一铰链部分与所述第二铰链部分中的一个具有沿垂直于所述第二转动平面的方向向外延伸的凸起，另一个具有与所述凸起匹配的导槽，通过所述导槽接纳所述凸起并允许所述凸起在其中转动实现所述第二铰链部分与所述调节机构的所述相对转动。
  21. 如权利要求4、5、7、11-16中任何一个所述的膝关节矫形器，其中所述大腿骨架还包括用于横向地贴合在所述大腿正面的大腿托，两个所述大腿支条远离所述小腿支条的端部与所述大腿托相连；所述大腿托为弯曲的柔性结构，其曲率半径在所述大腿骨架向内收缩时变小，在所述大腿骨架向外扩展时变大。
  22. 如权利要求21所述的膝关节矫形器，其中所述大腿支条可绕其与所述大腿托的连接点转动。
  23. 如权利要求21所述的膝关节矫形器，其中所述大腿托的内表面具有衬垫，所述衬垫的表面为网状的硅胶层。
  24. 如权利要求4、5、7、11-16中任何一个所述的膝关节矫形器，其中所述第一铰链部分与所述大腿支条之间设置有第二调节机构，用于调节并设定所述第一铰链部分与所述大腿支条的相对位置。
  25. 如权利要求24所述的膝关节矫形器，其中所述第二调节机构包括开设在所述第一铰链部分的第一组孔、开设在所述大腿支条端部处的多组用于与所述第一组孔配合的第二组孔和连接件；通过选择一组所述第二组孔与所述第一组孔对准并使用连接件将所述第一铰链部分与所述大腿支条固定，实现调节并设定所述第一铰链部分与所述大腿支条的相对位置。
  26. 如权利要求24所述的膝关节矫形器，其中所述第二调节机构包括设置在所述第一铰链部分的第一组齿、设置在所述大腿支条端部处的用于与所述第一组齿配合的第二组齿和连接件；通过调节所述第一组齿和所述第二组齿的咬合位置并使用连接件将所述第一铰链部分与所述大腿支条固定，实现调节并设定所述第一铰链部分与所述大腿支条的相对位置。
  27. 如权利要求24所述的膝关节矫形器，其中所述第二调节机构包括设置在所述第一铰链部分的凹槽、设置在所述大腿支条端部处的用于与所述凹槽配合的凸出部分和从两侧穿过所述第一铰链部分直到所述凹槽的两个紧定螺丝；通过调节所述两个紧定螺丝使其抵触在所述凹槽中的所述凸出部分的位置，实现调节并设定所述第一铰链部分与所述大腿支条的相对位置。
  28. 如权利要求4、5、7、11-16中任何一个所述的膝关节矫形器，其中所述小腿骨架包括用于横向贴合所述小腿的中部的小腿托，所述小腿托包括两端分别相连的曲率不同的第一部分和第二部分，所述第二部分为柔性结构，所述第一部分的柔度小于所述第二部分，其被布置在所述第二部分之外。
  29. 如权利要求28所述的膝关节矫形器，其中所述第一部分和所述第二部分的两端通过子母钉连接。
  30. 如权利要求28所述的膝关节矫形器，其中所述小腿骨架还包括用于贴合小腿上部的蝶形的小腿支条，所述小腿支条包括中间部分和从所述中间部分延伸的四个翼，所述小腿支条上部两翼向上弯曲地延伸，其两个端部分别连接所述两个调节机构，下部两翼横向延伸，其两个端部分别与第一小腿绑带的两端相连，所述第一小腿绑带用于在所述下肢的膝后区的菱形凹陷处横跨所述小腿的背面；所述小腿支条的中间部分与所述第一部分相连。
  31. 如权利要求30所述的膝关节矫形器，其中所述第二部分的所述两端与第二小腿绑带的两端相连，所述第二小腿绑带用于横跨所述小腿肚。
  32. 如权利要求30所述的膝关节矫形器，其中所述第二部分的内表面具有衬垫，所述衬垫的表面为网状的硅胶层。
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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN109646222A (zh) * 2019-01-30 2019-04-19 南京市儿童医院 一种肛门术后灯烤折叠截石位支架

Families Citing this family (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US11980562B2 (en) * 2017-12-14 2024-05-14 Green Sun Medical, LLC Reconfigurable orthosis for deformity correction
DE102017223757B4 (de) * 2017-12-22 2023-05-25 Bauerfeind Ag Hartrahmen mit verschwenkbarer Brücke
CN109009612A (zh) * 2018-06-04 2018-12-18 王荣涛 下肢牵引治疗仪
CN109549769B (zh) * 2018-12-21 2023-11-28 山东省科学院自动化研究所 一种模块化可穿戴肢体连接固定接口装置
CN109481116A (zh) * 2018-12-24 2019-03-19 上海高博医疗器械有限公司 膝关节矫形器
CN111805512B (zh) * 2019-07-02 2023-04-25 重庆市牛迪科技发展有限公司 一种膝关节外骨骼
CN110934681B (zh) * 2019-12-23 2021-11-02 盐城市艾润电器有限公司 一种具有可调装置的医用护膝带
CN111035496B (zh) * 2019-12-30 2022-04-26 顾翔宇 一种人体下肢矫形支具和制造方法
TWI747370B (zh) * 2020-07-10 2021-11-21 至笙企業股份有限公司 下肢護具
DE102021118057A1 (de) 2021-07-13 2023-01-19 Ferd. Hauber Gmbh Gelenk für eine Orthese und eine Knieorthese
DE102021119666A1 (de) * 2021-07-28 2023-02-02 Otto Bock Healthcare Products Gmbh Orthese

Citations (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2350091A1 (fr) * 1976-05-04 1977-12-02 Agnello Sauveur Derotateur de controle de rotation des membres inferieurs
US5766140A (en) * 1996-05-01 1998-06-16 Smith & Nephew Donjoy, Inc. Angular compensation device for a joint brace
US6656144B1 (en) * 1999-11-22 2003-12-02 Hipbolt Orthopedic Systems Articulating joint for an orthopedic brace
WO2008129096A1 (es) * 2007-04-23 2008-10-30 Golden Crab, S.L. Exoesqueleto de seguridad y control para la práctica del esquí de nieve
CN101917942A (zh) * 2007-12-21 2010-12-15 奥托·博克保健有限公司 校正关节
CN101938960A (zh) * 2008-02-05 2011-01-05 贾恩卡洛·佩利斯 用于分解竖向负荷的膝盖人机工程学装置
CN202060926U (zh) * 2011-04-14 2011-12-07 万得医疗器材用品(深圳)有限公司 骨性关节炎膝部矫形护托
CN202161443U (zh) * 2011-06-29 2012-03-14 汤福刚 体外人工膝关节——无创伤膝关节骨关节病矫治装置
WO2013040354A1 (en) * 2011-09-16 2013-03-21 Townsend Design Knee brace with tool less length adjuster
WO2013040375A1 (en) * 2011-09-16 2013-03-21 Townsend Design Knee brace with adjustable bolster
CN103582468A (zh) * 2011-04-21 2014-02-12 医疗技术有限公司 具有动态变化的内外侧铰链的矫形膝盖支架

Family Cites Families (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4723539A (en) * 1984-08-13 1988-02-09 Townsend Industries, Inc. Multiaxis controlled motion knee orthosis
US4773404A (en) * 1984-08-13 1988-09-27 Townsend Jeffrey H Multiaxis controlled motion knee orthosis
US5092320A (en) * 1991-03-19 1992-03-03 Empi, Inc. Knee brace with magnetic securing means
WO2002060359A1 (en) * 2001-01-29 2002-08-08 Asterisk.Asterisk, Llc Joint brace with multi-planar pivoting assembly and infinitely adjustable limb extension regulator
ITVR20020006A1 (it) * 2002-02-06 2003-08-06 Fgp Srl Ortesi per ginocchio ostoartritico
US7485103B2 (en) * 2006-04-13 2009-02-03 Breg, Inc. Rotational hinge assembly for a knee brace having an osteoarthritis treatment function
CN101626741B (zh) * 2007-02-12 2011-10-05 奥索集团公司 带有保护装置的矫形支架
US8945035B2 (en) * 2008-08-28 2015-02-03 Richard A. Nace Knee brace with improved gait swing assist
US8858479B2 (en) * 2010-10-07 2014-10-14 Jone-Shou Industrial Co., Ltd. Adjustable joint positioning device
FR2971702B1 (fr) * 2011-02-21 2013-03-15 Gibaud Orthese pour le traitement des troubles musculaires du coude
US11311402B2 (en) * 2013-05-06 2022-04-26 Aspen Medical Partners, Llc Scoliosis brace
CN204072404U (zh) 2014-03-28 2015-01-07 罗云 关节辅具的快速绑带
WO2015018340A1 (zh) 2013-08-09 2015-02-12 Luo Yun 具有免荷功能的膝关节矫形器

Patent Citations (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2350091A1 (fr) * 1976-05-04 1977-12-02 Agnello Sauveur Derotateur de controle de rotation des membres inferieurs
US5766140A (en) * 1996-05-01 1998-06-16 Smith & Nephew Donjoy, Inc. Angular compensation device for a joint brace
US6656144B1 (en) * 1999-11-22 2003-12-02 Hipbolt Orthopedic Systems Articulating joint for an orthopedic brace
WO2008129096A1 (es) * 2007-04-23 2008-10-30 Golden Crab, S.L. Exoesqueleto de seguridad y control para la práctica del esquí de nieve
CN101917942A (zh) * 2007-12-21 2010-12-15 奥托·博克保健有限公司 校正关节
CN101938960A (zh) * 2008-02-05 2011-01-05 贾恩卡洛·佩利斯 用于分解竖向负荷的膝盖人机工程学装置
CN202060926U (zh) * 2011-04-14 2011-12-07 万得医疗器材用品(深圳)有限公司 骨性关节炎膝部矫形护托
CN103582468A (zh) * 2011-04-21 2014-02-12 医疗技术有限公司 具有动态变化的内外侧铰链的矫形膝盖支架
CN202161443U (zh) * 2011-06-29 2012-03-14 汤福刚 体外人工膝关节——无创伤膝关节骨关节病矫治装置
WO2013040354A1 (en) * 2011-09-16 2013-03-21 Townsend Design Knee brace with tool less length adjuster
WO2013040375A1 (en) * 2011-09-16 2013-03-21 Townsend Design Knee brace with adjustable bolster

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN109646222A (zh) * 2019-01-30 2019-04-19 南京市儿童医院 一种肛门术后灯烤折叠截石位支架

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