CN116549186A

CN116549186A - Ankle joint prosthesis

Info

Publication number: CN116549186A
Application number: CN202310775066.7A
Authority: CN
Inventors: 罗丁豪; 郝永强; 姜闻博; 邓亮; 王磊; 谢凯; 吴钧翔
Original assignee: Ninth Peoples Hospital Shanghai Jiaotong University School of Medicine
Current assignee: Ninth Peoples Hospital Shanghai Jiaotong University School of Medicine
Priority date: 2023-06-28
Filing date: 2023-06-28
Publication date: 2023-08-08

Abstract

The invention discloses an ankle joint prosthesis, which comprises a tibia component, a liner, a talus component and a plurality of bionic ligaments, wherein the tibia component, the liner and the talus component are sequentially connected; the tibial component includes a first intramedullary canal stem and a platform coupled to a lower end of the first intramedullary canal stem; the liner comprises a liner body, wherein a cylindrical boss is arranged on the upper surface of the liner body; the talar component includes a second medullary canal shaft and a connector connected to an upper end of the second medullary canal shaft; the biomimetic ligament connects the pad and the talus component, respectively. The ankle joint prosthesis provided by the invention can completely replace bones and cartilages of the ankle joint surface, thereby overcoming the problem that the cartilaginous surface cannot be repaired in ankle arthroscopy operation. The ankle joint prosthesis with full freedom degrees, which completely reserves six moving modes of flexion and extension, internal and external turning and internal and external rotation, is prepared by replacing the original damaged ankle joint with metal and polymer components, so that uncomfortable symptoms are relieved, and joint movement capability is reserved.

Description

Ankle joint prosthesis

Technical Field

The invention relates to the field of artificial prostheses, in particular to an ankle joint prosthesis.

Background

Ankle joints are one of the most frequent joints that are subjected to the greatest weight forces during daily exercise. A significant portion of the population suffers from varying degrees of ankle injury. Ankle prosthesis replacement is a new treatment that has been developed and popularized in recent years to remove portions of the bone distal to the tibia and proximal to the talus, and to replace it with metal prosthetic components, thereby thoroughly eradicating the pain condition.

Because the talar articular surface is a complex curved surface, the flexion-extension sliding process on the tibial articular surface is necessarily accompanied by both varus and valgus rotation. In addition, due to the difference of the anterior-posterior and medial-lateral muscle group strength of the tibia, the ankle joint itself cannot maintain a completely neutral position when a human body stands, walks and runs under load, but is accompanied by complex varus-valgus and valgus movements. Therefore, the ankle joint is a complex joint with six movement modes of bending, stretching, varus, valgus, internal rotation and external rotation. Generally, ankle dorsi extension may be up to about 30 degrees, plantarflexion may be up to about 40 degrees, varus and valgus may be up to about 30 degrees, and may have slight pronation.

The prior ankle joint prosthesis can ensure that the ankle joint can still move, but most of the prior ankle joint prosthesis can only realize limited flexion and extension movements, and the functions of rotation, selection, inversion and eversion of the foot are basically completely lost, so that patients feel different from natural ankle joints in various actions such as standing, walking and running, have obvious restriction feeling and uncomfortable feeling, and simultaneously the ankle joint prosthesis also bears a great deal of stress due to the natural movement habit of a human body, so that the prosthesis-bone is worn, the prosthesis becomes even broken. Some prostheses are barely able to achieve slight eversion, but their structure is inherently poorly adapted to this movement, the articular surfaces wear very much, and it is likely that the prosthetic articular surfaces will be further dislocated. Some prostheses adopt a purely spherical joint design, the joint is movable in all directions, and because the joint is too flexible and lacks of fixity and supportability, a patient can not obtain support in a fixed direction when supporting and exerting force on the ankle joint, so that the exercise capacity of the prosthesis is affected, and serious load and chronic tearing damage are caused to ligaments and tendons around the ankle joint for a long time. Most of the prior ankle prostheses have small fixation volume in the tibia and the talus, often have only a plurality of tiny spike-shaped bodies, even have no protrusions and only rely on surface friction force and bone cement to fix the bones. Because the metal, the bone cement and the bone still have certain difference in elastic modulus and other mechanical properties, the abrasion of the bone-metal interface is larger, and the long-term failure risks such as prosthesis loosening and displacement are higher.

Disclosure of Invention

The invention aims to provide an ankle joint prosthesis which has complete freedom and completely reserves six moving modes of flexion and extension, internal and external turning and internal and external rotation.

In order to achieve the above object, the present invention provides an ankle joint prosthesis comprising a tibial component, a liner, a talus component, and a plurality of bionic ligaments, which are sequentially connected;

the tibial component includes a first intramedullary canal stem and a platform coupled to a lower end of the first intramedullary canal stem; the lower surface of the platform comprises a cylindrical groove;

the liner comprises a liner body, wherein a cylindrical boss is arranged on the upper surface of the liner body, the shape of the cylindrical groove is matched with that of the cylindrical boss, the cylindrical boss is inserted into the cylindrical groove, so that the liner is connected with the tibia component, and the tibia component can rotate relative to the liner;

a bump is arranged in the cylindrical groove, the cylindrical boss comprises a notch, the bump is arranged in the notch, and the size of the bump is smaller than that of the notch;

the lower surface of the liner body comprises an arc groove; the talar component includes a second medullary canal shaft and a connector connected to an upper end of the second medullary canal shaft; the upper surface of the connecting piece comprises an arc surface, the arc groove is matched with the shape of the upper surface, the upper surface is arranged in the arc groove, so that the talus part is connected with the pad, and the talus part can rotate relative to the pad;

the biomimetic ligament connects the pad and the talus component, respectively.

Optionally, the upper surface of the connecting piece comprises an arc surface, a first side surface and a second side surface which are positioned on two sides of the arc surface, and the arc surface is respectively and smoothly connected with the first side surface and the second side surface.

Optionally, the cambered surface forms a first intersection with the first side surface, and the cambered surface forms a second intersection with the second side surface; the lower ends of the arc grooves corresponding to the first side face and the second side face are respectively bent outwards to form a first protrusion and a second protrusion;

the talar component is rotatable in the direction of the first projection until the first intersection abuts the first projection; the talar component is rotatable in the direction of the second projection until the second intersection abuts the second projection.

Optionally, the talus component can rotate relative to the pad along the length direction of the cambered surface, and the upper surface of the connecting piece of the talus component is not separated from the cambered groove of the pad by pulling the bionic ligament.

Optionally, the central angle of the cambered surface is 100-130 degrees, the radius is 20-25 mm, and the width of the cambered surface is 5-10 mm.

Optionally, the cross section of the lug is a first fan shape, the cross section of the notch is a second fan shape, and the central angle of the first fan shape is smaller than that of the second fan shape.

Optionally, the central angle of the first sector is 20 ° -40 ° different from the central angle of the second sector.

Optionally, through holes for filling bone cement are respectively arranged through the first medullary cavity handle and the second medullary cavity handle; the two sides of the first medullary cavity handle and the second medullary cavity handle are sunken to form a medullary cavity handle groove.

Optionally, the bionic ligament is provided with two pieces, one end of the bionic ligament is connected with the pad, the other end of the bionic ligament is connected with the talus component, and the bionic ligament is symmetrically distributed on two sides of the pad and the talus component.

Optionally, the tibial component and the talus component are made of titanium alloy materials, the liner is made of high polymer polyethylene materials, and the bionic ligament is made of flexible materials.

The beneficial effects of the invention are as follows:

(1) The ankle joint prosthesis provided by the invention can completely replace bones and cartilages of the ankle joint surface, thereby overcoming the problem that the cartilaginous surface cannot be repaired in ankle arthroscopy operation. The metal and polymer components are used for replacing the original damaged ankle joint, so that uncomfortable symptoms are relieved, and joint movement capability is reserved.

(2) The ankle joint prosthesis provided by the invention not only can keep full flexion and extension functions, but also can fully realize the functions of eversion and supination of the ankle joint, and the ankle joint prosthesis can perform limited movement. The tibia component rotates relative to the pad to realize the inward and outward rotation of the ankle joint, and the talus component rotates relative to the pad to realize the flexion and extension and the inward and outward turning of the ankle joint. The contact surfaces among the structures can smoothly and alternately move, so that the structure can fully move and prevent scratch and bump among the structures.

(3) Two bionic ligaments made of flexible materials are additionally arranged between the talus part and the pad of the ankle joint prosthesis, so that not only can the angle of the ankle joint bending and stretching and varus and valgus be limited, but also the dislocation of the ankle joint during the ankle joint bending and stretching and valgus action can be effectively prevented.

(4) The tibia component and the talus component each comprise a medullary cavity handle, and innovatively adopt a quadrangular prism-like structure instead of a common cylindrical and conical structure, so that the self anti-rotation loose capability is enhanced. The center of the medullary cavity handle is provided with a plurality of bone cement penetrating holes, so that the bone cement can be locked and fixed, and the pulling-out resistance is enhanced. The two sides of the medullary cavity handle are respectively provided with a pair of inward concave grooves, so that the up-down loose displacement of the prosthesis in the long axis direction of the tibia is further resisted.

Drawings

Fig. 1 is a rear view of the ankle prosthesis of the invention.

Fig. 2 is a perspective view of the ankle prosthesis of the present invention.

Fig. 3 is a perspective view of a tibial component of the present invention.

Fig. 4 is a perspective view of a gasket of the present invention.

Fig. 5 is a plan view of the ankle prosthesis according to the present invention, wherein a of fig. 5 is a plan view of the ankle prosthesis in an erect state, and b of fig. 5 is a plan view of the ankle prosthesis in an pronated state.

Fig. 6 is a perspective view of a talar component of the invention.

Fig. 7 is a three view of the talar component of the invention, wherein fig. 7 a is a top view of the talar component, fig. 7 b is a left view of the talar component, and fig. 7 c is a front view of the talar component.

Fig. 8 is a perspective view of a bionic ligament according to the invention.

Fig. 9 is a perspective view of a bionic ligament attachment talus component of the invention.

Fig. 10 is a perspective view of the bionic ligament connection pad of the present invention.

Fig. 11 is another perspective view of the gasket of the present invention.

Fig. 12 is a cross-sectional view of a gasket of the present invention.

Fig. 13 is a rear view of the ankle joint prosthesis of the invention in an inverted state.

Fig. 14 is a right side view of the ankle prosthesis according to the present invention, wherein a of fig. 14 is a right side view of the ankle prosthesis in an erect state, and b of fig. 14 is a right side view of the ankle prosthesis in a dorsi-extended state.

In the figures, 1-tibial component, 11-first medullary canal, 12-plateau, 121-cylindrical recess, 1210-bump, 1211-bump side, 2-pad, 21-pad body, 211-arc slot, 2111-first protrusion, 2112-second protrusion, 22-cylindrical boss, 220-notch, 3-talus component, 31-connector, 310-upper surface, 3100-arc, 3101-first side, 3102-second side, 3103-first intersection, 3104-second intersection, 311-bottom, 32-second medullary canal, 4-biomimetic ligament, 5-penetration hole, 6-medullary canal recess.

Detailed Description

The following description of the embodiments of the present invention will be made apparent and fully in view of the accompanying drawings, in which some, but not all embodiments of the invention are shown. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.

Fig. 1 is a rear view of the ankle prosthesis of the invention. In the description of the present invention, the terms "upper", "lower", "left", "right", "front" and "rear" are all based on fig. 1 unless otherwise specified. In describing the medial-lateral directions, the left foot is taken as an example, i.e., the right side of the medial ankle joint prosthesis of fig. 1 is taken as the medial side. Defining the horizontal direction of FIG. 1 as the x-axis, the vertical direction as the y-axis, and the direction perpendicular to the paper surface as the z-axis; the ankle joint prosthesis rotates around the x axis to bend and stretch, moves around the y axis to rotate inwards and outwards, and moves around the z axis to turn inwards and outwards. Furthermore, the terms "first," "second," "third," and the like are used for descriptive purposes only and are not to be construed as indicating or implying relative importance.

In the description of the present invention, it should be noted that, unless explicitly specified and limited otherwise, the terms "mounted," "connected," and "connected" are to be construed broadly, and may be, for example, fixedly connected, detachably connected, or integrally connected; may be a mechanical connection; can be directly connected or indirectly connected through an intermediate medium, and can be communication between two elements. The specific meaning of the above terms in the present invention will be understood in specific cases by those of ordinary skill in the art.

The ankle joint plays a vital role in the actions of standing, walking, running and the like of a human body. The ankle joint can move in six modes of flexion, extension, inversion, eversion, internal rotation and external rotation. Generally, ankle joint dorsi extension can be up to about 30 degrees, plantarflexion can be up to about 40 degrees, varus and valgus can be up to about 30 degrees, and has slight internal and external rotation. The range of motion of the ankle joint must be limited to enhance stability of the motion, otherwise it is prone to injury to the human body, such as spraining of the foot, fracture, etc. At the same time, there should be a high degree of fit between the various structures in the ankle to reduce wear on the articular surfaces and prevent dislocation of the structures.

As shown in fig. 1, the present invention provides an ankle joint prosthesis comprising a tibial component 1, a liner 2 and a talus component 3 connected in sequence, and further comprising a plurality of bionic ligaments 4. One end of the bionic ligament 4 is connected with the pad 2, and the other end is connected with the talus component 3. In this embodiment, the bionic ligament 4 is provided with two pieces, which are respectively connected to the left and right sides of the pad 2 and the talus component 3. The tibia component 1 and the talus component 3 are made of titanium alloy materials, the gasket 2 is made of high polymer polyethylene materials, and the bionic ligament 4 is made of flexible materials.

The tibial component 1 rotates relative to the liner 2 to achieve pronation and supination of the ankle prosthesis.

As shown in fig. 1-5, the tibial component 1 includes a first intramedullary canal stem 11 and a platform 12 coupled to a lower end of the first intramedullary canal stem 11, the lower surface of the platform 12 including a cylindrical recess 121. The liner 2 comprises a liner body 21, a cylindrical boss 22 is arranged on the upper surface of the liner body 21, the cylindrical groove 121 is matched with the cylindrical boss 22 in shape, the cylindrical boss 22 is inserted into the cylindrical groove 121, connection between the liner 2 and the tibial component 1 is achieved, and the tibial component 1 can rotate relative to the liner 2, namely, the tibial component 1 rotates relative to the liner 2 around a y axis. The tibia component 1 rotates leftwards relative to the pad 2, and corresponds to the external rotation of the ankle joint prosthesis; the tibial component 1 is turned to the right relative to the pad 2, corresponding to the pronation of the ankle prosthesis (as shown in b of fig. 5). In order to limit the rotation angle of the inner and outer rotations, a protrusion 1210 is disposed in the cylindrical recess 121, the cylindrical boss 22 includes a notch 220, when the cylindrical boss 22 is inserted into the cylindrical recess 121, the protrusion 1210 is disposed in the notch 220, and the size of the protrusion 1210 is smaller than that of the notch 220. In this example, the cross section of the protruding block 1210 is a first sector, the cross section of the notch 220 is a second sector, the central angle of the first sector is smaller than that of the second sector, the central angle of the first sector is different from that of the second sector by 20 ° -40 °, preferably, the central angle of the first sector is 60 °, the central angle of the second sector is 90 °, the central angle of the first sector is different from that of the second sector by 30 °, and the protruding block 1210 is inserted into the central position of the notch 220 in an upright state (as shown in a of fig. 5) corresponding to the ankle joint prosthesis, and at this time, the ankle joint prosthesis has maximum internal rotation range and external rotation range of 15 ° and 15 ° respectively.

In some embodiments, in order to provide a tighter locking of tibial component 1 and liner 2 at the maximum internal and external rotation range, projection sides 1211 form an acute angle with the bottom surface of platform 12, and two projection sides 1211 of projection 1210 are beveled, each sloping toward the center of projection 1210, i.e., the top edge of projection side 1211 is closer to the center of projection 1210 than the bottom edge, and the shape of notch 220 also matches the shape of projection 1210. Therefore, when the projection side 1211 of the projection 1210 contacts the cylindrical boss 22, the interface between the projection 1210 and the cylindrical boss 22 is a bevel, and the inwardly inclined bevel more locks the tibial component 1 and the liner 2 to each other than a straight surface, increasing the difficulty of the projection 1210 sliding off the notch 220, and reducing the possibility of dislocation between the tibial component 1 and the liner 2 due to excessive internal and external rotation angles.

The talar component 3 rotates relative to the pad 2 to effect flexion, extension, varus and valgus of the ankle prosthesis.

As shown in fig. 6-14, the talar component 3 includes a second medullary canal stem 32 and a connector 31 attached to the upper end of the second medullary canal stem 32. The lower surface of the spacer body 21 comprises an arc groove 211, the shape of the upper surface 310 of the connecting piece 31 is adapted to the shape of the arc groove 211, the upper surface 310 of the connecting piece 31 is placed in the arc groove 211 of the spacer 2, the connection of the talar component 3 to the spacer 2 is achieved, and the talar component 3 can rotate relative to the spacer 2.

The talus component 3 is generally mushroom-shaped, the connector 31 being a mushroom head and the second medullary canal shaft 32 being a mushroom shaft. The upper surface 310 of the connecting member 31 includes a cambered surface 3100 and a first side 3101 and a second side 3102 located at two sides of the cambered surface 3100, and the cambered surface 3100 is smoothly connected with the first side 3101 and the second side 3102 respectively. The arcuate surface 3100 forms a first intersection 3103 with the first side 3101, and the arcuate surface 3100 forms a second intersection 3104 with the second side 3102. The connecting member 31 has a rectangular shape with rounded four corners in plan view and has an arcuate shape in left/right view. The arc groove 211 is bent outwards corresponding to the lower end of the first side surface and the lower end of the second side surface, so as to form a smooth first protrusion 2111 and a smooth second protrusion 2112.

The bionic ligaments 4 are in a flat belt shape with round ends, the length is 24mm, the width is 20mm, and the thickness is 2mm. The medical silica gel material (MED-4735 silicon rubber) is flexible, has certain elasticity, and can provide stronger pulling force when being tensioned. One end of the bionic ligament 4 is connected to the talus component 3 by the bottom surface 311 of the connector 31 of the talus component 3, and the other end is connected to the pad 2 by the side surface of the pad body 21. Two ends of the bionic ligament 4 are respectively provided with a pair of screws, and the bottom surface 311 of the connecting piece 31 and the side surface of the liner body 21 are respectively provided with holes for the screws to pass through. Preferably, the screw diameter for connecting the spacer 2 is 2mm and the screw diameter for connecting the talar component 3 is 3mm.

The link 31 disposed in the arc slot 211 is capable of dislocating movement within the arc slot 211 relative to the liner 2, i.e., the link 31 rotates about the z-axis. Specifically, the connecting piece 31 of the talar component 3 is turned in the direction of the first protrusion 2111 until the first intersection 3103 abuts the first protrusion 2111, and the connecting piece 31 cannot continue to turn to the left, limited by the first protrusion 2111, corresponding to eversion of the ankle prosthesis; the connecting piece 31 of the talar component 3 is turned in the direction of the second protrusion 2112 until said second intersection 3104 abuts said second protrusion 2112, and the connecting piece 31 cannot continue to turn to the right, limited by the second protrusion 2112, corresponding to the varus of the ankle prosthesis (as shown in fig. 13). The first intersection 3103 abuts the first protrusion 2111 or the second intersection 3104 abuts the second protrusion 2112, and there is a strong tendency for the talar component 3 to return to a neutral position, thus effectively providing resistance against excessive valgus dislocation. Preferably, the second intersection 3104 abuts the interior wall apex of the arc groove 211 when the first intersection 3103 abuts the first protrusion 2111, or has a tendency to evert further than the first protrusion 2111; when the second intersection 3104 abuts the second protrusion 2112, or has a tendency to go further inward than the second protrusion 2112, there is a first intersection 3103 abutting the apex of the inner wall of the arcuate slot 211, again limiting eversion of the talar component 3. The offset motion of the articular surface (upper surface 310) of talar component 3 and the padded articular surface (surface of arcuate slot 211) provides resistance to the varus-valgus action, but the contact surfaces or points of contact are relatively smooth, consistent with the actual state of the ankle valgus action between non-resistant and resistant. In addition, the bionic ligament 4 can also limit eversion of the ankle prosthesis. When the connecting piece 31 moves around the z axis, the connecting piece 31 can pull the bionic ligament 4 to stretch or compress. When the varus angle is too large, the bionic ligament 4 on one side of the connecting piece 31 is embedded into the arc groove 211, so that the varus action with a larger angle is blocked, and excessive valgus and dislocation of the joint are further prevented.

The connection member 31 disposed in the arc groove 211 can rotate in the length direction of the arc surface 3100 in the arc groove 211, that is, the connection member 31 rotates about the x-axis. The connecting piece 31 of the talus component 3 rotates forward along the length direction of the cambered surface 3100, corresponding to plantarflexion of the ankle prosthesis; the connecting piece 31 of the talar component 3 is turned backwards along the length of the arc 3100, corresponding to the dorsi extension of the ankle prosthesis (as shown in b of fig. 14). The range of motion of plantarflexion and dorsiflexion is limited by the bionic ligament 4. By pulling on the biomimetic ligament 4, the plantarflexion and dorsiflexion angles are controlled such that the upper surface 310 of the connector 31 of the talar component 3 does not disengage from the arcuate slot 211 of the spacer 2.

The upper surface 310 of the connecting piece 31 has a central angle of a cambered surface 3100 of 100-130 degrees, a radius of 20-25 mm and a cambered surface width of 5-10 mm. Preferably, the central angle of the arc surface 3100 is 121.68 °, the radius is 22.73mm, and the width is 7mm. With this design dimension, the maximum varus angle is 26.31 ° with the articular surface (upper surface 310) of the talar component 3 in contact with the pad articular surface (surface of the arcuate slot 211), and if the two articular surfaces are slightly separated, the maximum valgus angle is up to 30 ° with the bionic ligament 4. Theoretically, the limit angle of plantarflexion and dorsiflexion of the hip joint prosthesis is 60.84 ° (half of 121.68 °), but is limited by the length of the bionic ligament 4 and the bone and soft tissue around the ankle joint prosthesis, the maximum dorsiflexion of the ankle joint prosthesis being about 30 ° and the maximum plantarflexion being about 40 °. The flexion and extension and the varus and valgus angles can meet the requirements of normal ankle joint movement of human body.

The first and second medullary canal handles 11, 32 are generally quadrangular, with trapezoidal left/right views. In order to enhance the connection of the hip prosthesis to the medullary cavity, through said first medullary cavity stem 11 and said second medullary cavity stem 32, respectively, there are provided through holes 5 for filling with bone cement; the two sides of the first and second medullary cavity handles are recessed to form a medullary cavity handle groove 6. The first medullary cavity stem 11 can be inserted into the tibial medullary cavity and the second medullary cavity stem 32 can be inserted into the tibial medullary cavity and then firmly fixed to the bone with bone cement. The bone cement passes through the through holes 5 to form interlocking, so that the prosthesis is effectively placed for loosening, and the marrow cavity handle groove 6 can further enhance the bonding effect of the bone cement. Optionally, the first medullary canal grip 11 has a length (along the y-axis) of 30mm and a thickness (along the x-axis) of 12mm, and has a front surface at an angle of 6.69 ° to the y-axis and a rear surface at an angle of 16.33 ° to the y-axis, with the front surface being more vertical than the rear surface, and conforming to the intramedullary surface topography of the distal tibia. The second medullary canal shaft 32 has a length (in the y-axis direction) of 10mm, a thickness (in the x-axis direction) of 10mm, and a width (in the z-axis direction) of 18mm. The diameter of the penetration hole 5 is 8mm.

In summary, the present invention provides an ankle prosthesis comprising a tibial component, a liner, a talus component, and a plurality of bionic ligaments, which are sequentially connected. The tibia component rotates relative to the pad to realize the inward and outward rotation of the ankle joint, and the talus component rotates relative to the pad to realize the flexion and extension and the inward and outward turning of the ankle joint. The bionic ligament is made of flexible materials, so that not only can the angle of ankle joint bending and stretching and internal and external turning be limited, but also joint dislocation generated during the ankle joint bending and stretching and internal and external turning actions can be effectively prevented. The ankle joint prosthesis provided by the invention can completely keep six moving modes of flexion and extension, internal and external turning and internal and external rotation.

While the present invention has been described in detail through the foregoing description of the preferred embodiment, it should be understood that the foregoing description is not to be considered as limiting the invention. Many modifications and substitutions of the present invention will become apparent to those of ordinary skill in the art upon reading the foregoing. Accordingly, the scope of the invention should be limited only by the attached claims.

Claims

1. An ankle joint prosthesis is characterized by comprising a tibia component, a liner, a talus component and a plurality of bionic ligaments which are connected in sequence;

the liner comprises a liner body, wherein a cylindrical boss is arranged on the upper surface of the liner body, the shape of the cylindrical groove is matched with that of the cylindrical boss, the cylindrical boss is inserted into the cylindrical groove, so that the liner is connected with the tibia component, and the tibia component can rotate relative to the liner; a bump is arranged in the cylindrical groove, the cylindrical boss comprises a notch, the bump is arranged in the notch, and the size of the bump is smaller than that of the notch;

the biomimetic ligament connects the pad and the talus component, respectively.

2. The ankle joint prosthesis of claim 1, wherein the upper surface of the connecting member comprises a curved surface and first and second sides on opposite sides of the curved surface, the curved surface being smoothly connected to the first and second sides, respectively.

3. The ankle joint prosthesis of claim 2, wherein the arcuate surface forms a first intersection with the first side, the arcuate surface forming a second intersection with the second side; the lower ends of the arc grooves corresponding to the first side face and the second side face are respectively bent outwards to form a first protrusion and a second protrusion;

4. The ankle joint prosthesis of claim 2, wherein the talar component is rotatable relative to the pad along a length of the arcuate surface such that an upper surface of the connector of the talar component does not disengage from the arcuate slot of the pad by traction of the biomimetic ligament.

5. The ankle joint prosthesis according to claim 1, wherein the central angle of the arc surface is 100 ° -130 °, the radius is 20mm-25mm, and the width of the arc surface is 5mm-10mm.

6. The ankle joint prosthesis of claim 1, wherein the cross-section of the projection is a first sector and the cross-section of the notch is a second sector, the central angle of the first sector being smaller than the central angle of the second sector.

7. The ankle joint prosthesis of claim 6, wherein the central angle of the first sector is 20 ° to 40 ° different from the central angle of the second sector.

8. The ankle prosthesis of claim 1, wherein through holes for filling bone cement are provided through the first and second medullary canal handles, respectively; the two sides of the first medullary cavity handle and the second medullary cavity handle are sunken to form a medullary cavity handle groove.

9. The ankle prosthesis of claim 1, wherein the bionic ligament is provided with two strips, one end of which is connected to the pad and the other end of which is connected to the talus component, symmetrically disposed on both sides of the pad and the talus component.

10. The ankle prosthesis of claim 1, wherein the tibial component and the talar component are titanium alloy materials, the liner is a polymeric polyethylene material, and the biomimetic ligament is a flexible material.