Prosthetic heart valve

Abstract

The utility model provides a kind of artificial heart valve, comprising: support, covering film, multiple first connecting line and multiple second connecting line, support includes multiple cross connection and form grid structure's support pole, grid structure includes multiple mesh units, each mesh unit includes multiple connecting portion and the section of support pole connected between adjacent two connecting portions;Support includes mutually connected first flange section and first leaf segment;Covering film includes mutually connected flange connecting section and first leaf connecting section;Each mesh unit is connected at least with one first connecting line, and first connecting line is used to connect first flange section and flange connecting section together and connect first leaf segment and first leaf connecting section together;The connecting portion of each mesh unit of first leaf section is spirally wound with second connecting line.The artificial heart valve of the utility model can solve the problem of support bruising native tissue, reduce the risk of covering film binding support.

Description

Technical Field

[0001] This utility model relates to the field of medical device technology, and in particular to an artificial heart valve. Background Technology

[0002] The heart has four chambers: the left atrium and left ventricle are located on the left side of the heart, and the right atrium and right ventricle are located on the right side. The atria and ventricles form the ventricular inflow tract, the left ventricle and aorta form the left ventricular outflow tract, and the right ventricle and pulmonary artery form the right ventricular outflow tract. At the ventricular inflow and outflow tracts are valves that function as one-way valves, ensuring normal blood flow within the heart chambers. When these valves malfunction, cardiac hemodynamics change, leading to abnormal cardiac function, a condition known as valvular heart disease.

[0003] Transcatheter valve replacement has advantages such as not requiring open-chest surgery, minimal trauma, and rapid patient recovery. Therefore, more and more surgeries are performed via the transcatheter, making artificial heart valves an important medical device for treating valvular heart disease.

[0004] The skirt 22 of the existing artificial heart valve is sutured according to the size of the stent 21, such as... Figure 1 As shown, during sewing, only the skirt hem 22 is connected to the support rod 211 of the bracket 21, as follows: Figure 2 As shown, when the artificial heart valve is compressed, because the strut 21 is non-deformable, the stent 21 will elongate as a whole after compression. The strut 211 of the stent 21 moves relative to the skirt 22, but the skirt 22 does not elongate with the stent 21. This can easily cause the stent 21 to elongate and leak out of the skirt 22 after compression, increasing the risk of the artificial heart valve damaging blood vessels during delivery. Figure 3 and Figure 4 As shown, when the artificial heart valve is released and deployed, the strut 211 also moves relative to the skirt 22. The skirt 22 is not completely fixed to the strut 211, so the artificial heart valve cannot be fully deployed as expected. The stent 21 cannot return to its original state when it was just sewn with the skirt 22, resulting in part of the stent 21 continuing to be exposed outside the skirt 22. Therefore, during the movement of the artificial heart valve released into the human body, the exposed part of the stent 21 will bruise human tissue. Utility Model Content

[0005] In view of this, the purpose of this utility model is to provide an artificial heart valve that can solve the problem of stent damage to native tissue in the prior art and reduce the risk of stent binding by the endovascular membrane.

[0006] This invention provides an artificial heart valve, comprising: a stent, including multiple cross-connected struts forming a mesh structure, wherein at least two struts are connected to each other as connecting portions, the mesh structure includes multiple mesh units, each mesh unit includes multiple connecting portions and a section of the strut connected between two adjacent connecting portions; the stent includes interconnected first flange segments and first leaflet segments along its axial direction; a covering, including interconnected flange connecting segments and first leaflet connecting segments, the flange connecting segments and the first leaflet connecting segments being arranged along the axial direction of the stent; multiple first connecting lines, each mesh unit being connected to at least one first connecting line, the first connecting lines being spirally wound around the sections of the mesh units, the first connecting lines being used to connect the first flange segments to the flange connecting segments and to the first leaflet segments to the first leaflet connecting segments; and multiple second connecting lines, each second connecting line being spirally wound around the connecting portion of each mesh unit of the first leaflet segment, each second connecting line being used to connect the first leaflet segments to the first leaflet connecting segments.

[0007] In one embodiment, the segment includes a first segment, a second segment, a third segment, and a fourth segment, and each of the mesh units has a first connecting line, which sequentially connects the first segment, the second segment, the third segment, and the fourth segment.

[0008] In one embodiment, the segment includes a first segment, a second segment, a third segment, and a fourth segment, and each of the mesh units has four first connecting lines, with the first segment, the second segment, the third segment, and the fourth segment respectively connected to each of the first connecting lines.

[0009] In one embodiment, each of the first connecting lines is connected to each of the support rods.

[0010] In one embodiment, a wave-shaped structure is formed at the end of the first flange segment away from the first leaf segment. The wave-shaped structure is circumferentially arranged around the axis of the support. The wave-shaped structure includes multiple peaks and multiple troughs, and a trough is connected between two adjacent peaks. The flange connecting segment includes multiple first connecting ends and multiple second connecting ends that are fixedly connected in sequence. The distance from the first connecting end to the first leaf connecting segment is greater than the distance from the second connecting end to the first leaf connecting segment. Each first connecting end is connected to each peak, and each second connecting end is connected to each trough.

[0011] In one embodiment, the edge of the first connecting end away from the first leaflet connecting segment is defined as the first edge, and the edge of the second connecting end away from the first leaflet connecting segment is defined as the second edge. The distance between the first edge and the first leaflet segment is greater than the distance between the wave crest and the first leaflet segment, and the distance between the second edge and the first leaflet segment is greater than the distance between the wave trough and the first leaflet segment.

[0012] In one embodiment, the connection between the first flange segment and the first leaf segment is defined as a transition section. The first leaf segment is provided with a plurality of through holes, each of which is located in the transition section. Each of the through holes is correspondingly provided with each of the support rods, and each of the through holes is circumferentially arranged around the axis of the bracket.

[0013] In one embodiment, the length of the through hole along the axial direction of the bracket is greater than the length of the through hole along the radial direction of the bracket.

[0014] In one embodiment, the through hole is quadrilateral, vertical line, or elliptical.

[0015] In one embodiment, the support further includes a second leaf segment, which is disposed along the axial direction of the support and connected to the first leaf segment. The covering film further includes a second leaf connecting segment, which is connected to the section of each of the mesh units and does not cover the mesh units.

[0016] In one embodiment, the density of the mesh structure in the first flange segment is less than the density of the mesh structure in the first leaf segment.

[0017] This invention relates to an artificial heart valve that wraps around the first flange segment and the first leaflet segment of a stent. Different suturing methods are used depending on the different stiffnesses of the first flange segment and the first leaflet segment. A first connecting line is used to fix the flange connecting segment of the wrapping to a section within the mesh unit of the first flange segment, and the first leaflet connecting segment of the wrapping is also fixed to a section within the mesh unit. A second connecting line is used to connect the first leaflet connecting segment of the wrapping to the connecting part of the mesh unit. This allows the first flange segment of the stent to move relative to the first leaflet connecting segment of the wrapping when the stent is gripped, preventing the first leaflet connecting segment from restricting the gripping and unfolding of the first flange segment, thus reducing the risk of the wrapping binding the stent. Furthermore, when the first leaflet segment of the stent is gripped, the corresponding first leaflet connecting segment moves with it. The first leaflet segment and the first leaflet connecting segment maintain a fixed connection at all times, preventing any part of the stent structure from protruding outside the wrapping after gripping or unfolding, thereby reducing the risk of the stent damaging the body's original tissues. Attached Figure Description

[0018] To more clearly illustrate the technical solutions of the embodiments of this utility model, the drawings used in the embodiments will be briefly introduced below. It should be understood that the following drawings only show some embodiments of this utility model and should not be regarded as a limitation on the scope. For those skilled in the art, other related drawings can be obtained based on these drawings without creative effort.

[0019] Figure 1 This is a schematic diagram of a partial structure of an existing artificial heart valve after the stent and skirt are sutured together.

[0020] Figure 2 This is a schematic diagram of the local structure of an existing artificial heart valve after compression.

[0021] Figure 3 This is a schematic diagram of the stent structure after deployment in an existing artificial heart valve.

[0022] Figure 4 This is a schematic diagram of the local structure of an existing artificial heart valve after deployment.

[0023] Figure 5 This is a schematic diagram of the structure of the artificial heart valve according to the first embodiment of this utility model.

[0024] Figure 6 This is a schematic diagram of the partially unfolded structure of the stent and diaphragm of the artificial heart valve according to the first embodiment of this utility model.

[0025] Figure 7 This is a partial structural diagram of the artificial heart valve after the stent and the lining are sutured together according to the first embodiment of this utility model.

[0026] Figure 8 This is a partial structural schematic diagram of the first flange section of the first embodiment of this utility model.

[0027] Figure 9 This is a partial structural schematic diagram of the first petal segment of the first embodiment of this utility model.

[0028] Figure 10 This is a partial structural diagram of the connection between the second leaf segment and the second leaf connecting segment in the first embodiment of this utility model.

[0029] Figure 11 This is a partial structural schematic diagram of the transition portion of the coating according to the first embodiment of this utility model.

[0030] Figure 12 yes Figure 11 A schematic diagram of another preferred shape for the through hole.

[0031] Figure 13 yes Figure 11A schematic diagram of another preferred shape for the through hole.

[0032] Figure 14 This is a partial structural schematic diagram of the first flange section of the second embodiment of this utility model.

[0033] Figure 15 This is a partial structural schematic diagram of the first flange section of the third embodiment of this utility model.

[0034] Reference numerals: Mesh unit - 101; Through hole - 102; Bracket - 11; Support rod - 111; Section - 1111; First section - 1111a; Second section - 1111b; Third section - 1111c; Fourth section - 1111d; Connecting part - 1112; First flange section - 112; Crest - 1121a; Valley - 1121b; First leaf section - 113; Second leaf section - 114; Transition part - 115; Coating - 12; Flange connecting section - 121; First connecting end - 1211; First edge - 1211a; Second connecting end - 1212; Second edge - 1212a; First leaf connecting section - 122; Second leaf connecting section - 123; First connecting line - 13; Second connecting line - 14; Leaf - 15. Detailed Implementation

[0035] The specific embodiments of this utility model will now be described in detail with reference to the accompanying drawings. Obviously, the described embodiments are merely some, not all, of the embodiments of this utility model. Based on the description of this utility model, all other embodiments obtained by those skilled in the art without inventive effort are within the scope of protection of this utility model.

[0036] In the description of this utility model, unless otherwise explicitly specified and limited, the terms "set," "install," and "connect," etc., should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium. Those skilled in the art can understand the specific meaning of the above terms according to the specific circumstances.

[0037] The terms “upper,” “lower,” “left,” “right,” “front,” “back,” “top,” “bottom,” “inner,” and “outer,” etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, or the orientation or positional relationship commonly used when the product is in use. They are used only for the convenience of description and simplification, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this utility model.

[0038] The terms “first,” “second,” “third,” etc., are used merely to distinguish elements with similar properties, not to indicate or imply relative importance or a specific order.

[0039] The terms “include,” “comprising,” or any other variation thereof are intended to cover non-exclusive inclusion, which includes not only the elements listed but also other elements not expressly listed.

[0040] As described herein, when referring to the heart valve stent or stent, "proximal" refers to the side of the heart valve stent in its extended state that is located on the delivery device or in the direction of the user-operated end. Correspondingly, "distal" refers to the side of the heart valve stent in its extended state that is away from the delivery device or in the direction of the user-operated end. In this application, when describing the heart valve stent, "proximal" refers to the side of the heart valve stent in its extended state that is closer to the apex of the heart. Correspondingly, "distal" refers to the side of the heart valve stent in its extended state that is away from the apex of the heart. Because the heart valve stent described herein is delivered via catheter through the aorta, "distal" and "proximal" refer to the same location, and "proximal" and "distal" refer to the same location. However, this does not preclude implantation via the apex of the heart; this description simply uses the example of the heart valve stent being delivered via catheter through the aorta.

[0041] First Embodiment

[0042] like Figures 5 to 15As shown, the artificial heart valve includes a stent 11, a diaphragm 12, leaflets 15, multiple first connecting lines 13, and multiple second connecting lines 14. The diaphragm 12 covers the stent 11. At least two leaflets 15 are provided, housed within the stent 11, and symmetrically distributed along the circumferential direction of the inner surface of the stent 11. When the artificial heart valve is closed, adjacent leaflets 15 are tightly closed or joined together in a sealing manner. The leaflets 15 can be made of biological tissue, such as chemically stable tissue from animal heart valves, such as porcine heart valves, or pericardial tissue from animals, preferably bovine pericardial tissue, but also sheep pericardium, porcine pericardium, or equine pericardium; the leaflets 15 can also be made of submucosal tissue of the small intestine; the leaflets 15 can also be made of synthetic materials, such as expanded polytetrafluoroethylene, polyester, thermoplastic polycarbonate polyurethane, polyether polyurethane, segmented polyether polyurethane, or silicone polyether. The stent 15 can be made of polyurethane, silicone polycarbonate polyurethane, or ultra-high molecular weight polyethylene. Additionally, the leaflet 15 can be made of biocompatible polymers such as polyolefins, elastomers, polyethylene glycol, polyethersulfone, polysulfone, polyvinylpyrrolidone, polyvinyl chloride, other fluoropolymers, silicone polyesters, siloxane polymers, and combinations thereof. The stent 11 can provide multiple functions for the artificial heart valve, such as serving as the main structure of the artificial heart valve, supporting the artificial leaflet, and connecting to the delivery system (hook or fixation ear). The stent 11 is made of braided or cut materials such as nickel-titanium, titanium alloy, cobalt-chromium alloy, MP35n, or 316 stainless steel. The stent 11 can also be made of other biocompatible metals, such as a biocompatible metal frame or a laser-cut solid metal tube, like nickel-titanium. The stent 11 can also be made of elastically or plastically deformable materials, such as balloon-expandable materials.

[0043] like Figure 5 and Figure 6As shown, the stent 11 includes multiple cross-connected struts 111 forming a grid structure. At least two struts 111 are connected to each other as connecting portions 1112. The grid structure includes multiple mesh units 101, each mesh unit 101 including multiple connecting portions 1112 and a section 1111 of the strut 111 connecting adjacent connecting portions 1112. The stent 11 includes a first flange section 112 and a first leaflet section 113 connected to each other along its axial direction. When the artificial heart valve deploys, the first flange section 112 deploys away from the axial direction of the stent 11. It also includes a second leaf segment 114, which is connected to the first leaf segment 113. The first leaf segment 113 is located between the first flange segment 112 and the second leaf segment 114. The first flange segment 112, the first leaf segment 113, and the second leaf segment 114 are arranged along the axial direction of the support 11. The density of the grid structure of the first flange segment 112 is less than the density of the grid structure of the first leaf segment 113. The density of the grid structure of the second leaf segment 114 is equal to the grid density of the first leaf segment 113. Both the first leaf segment 113 and the second leaf segment 114 are arranged parallel to the axis of the support 11.The coating 12 includes an interconnected flange connection section 121 and a first leaflet connection section 122, which are arranged along the axial direction of the support 11. Each mesh unit 101 is connected to at least one first connecting line 13, which is spirally wound around a section 1111 of the mesh unit 101. The first connecting line 13 is used to connect the first flange section 112 to the flange connection section 121 and the first leaflet section 113 to the first leaflet connection section 122. A second connecting line 14 is spirally wound around the connection portion 1112 of each mesh unit 101 of the first leaflet section 113. Each second connecting line 14 is used to connect the first leaflet section 113 to the first leaflet connection section 122. Since the first leaflet section 113 has greater rigidity than the first flange section 112, the flange connection section 121 of the coating 12 is only connected to a section of the mesh unit 101 of the first flange section 112. The membrane 12 is connected to the mesh unit 101 of the first flange segment 112, but not to the connecting part 1112 of the mesh unit 101, so as to avoid the flange connecting part 121 of the membrane 12 binding the first flange segment 112 of the support 11; the first leaf connecting part 122 of the membrane 12 is fixed to the section 1111 and the connecting part 1112 of the mesh unit 101, so as to avoid the relative sliding between the first leaf connecting part 122 and the support 11. When the support 11 is compressed and elongated or unfolded, the first leaf connecting part 122 of the membrane 12 can be compressed and elongated or unfolded with the support 11. The first leaf connecting part 122 is always covering the support 11, reducing the risk of the support 11 bruising human tissue. Moreover, the connection method of the first leaf connecting part 122 does not need to increase the size of the first leaf connecting part 122, reducing the loading size of the membrane 12 and the loading pressure of the support 11. It can be understood that the membrane 12 and the support 11 are fixedly connected by the first connecting line 13 and the second connecting line 14. The material of the coating 12 can be knitted, woven, or braided polyester fabric, and the material of the coating 12 can also be PTFE or ePTFE, etc.; the first connecting line 13 is preferably single-strand, double-strand, or multi-strand, and the material of the first connecting line 13 is preferably PE or PP, etc.; the second connecting line 14 is preferably single-strand, double-strand, or multi-strand, and the material of the first connecting line 13 is preferably PE or PP, etc. In this embodiment, the second leaf segment 114 is exposed, that is, the coating 12 does not cover the second leaf segment 114 and is not connected to the second leaf segment 114.

[0044] In other embodiments, such as Figure 10 As shown, the membrane 12 also includes a second leaflet connecting segment 123, which is connected to the segment 1111 of each mesh unit 101. The second leaflet connecting segment 123 does not cover the mesh unit 101, that is, the second leaflet connecting segment 123 is only individually wrapped and sutured with the segment 1111. When the artificial heart valve is squeezed, the stent 11 will not squeeze the leaflet, so as to reduce the compression damage of the stent 11 to the leaflet after squeezing.

[0045] The shape of the mesh unit 101 is preferably rhomboid or quadrilateral.

[0046] like Figure 6 , Figure 8 and Figure 9 As shown, segment 1111 includes a first segment 1111a, a second segment 1111b, a third segment 1111c, and a fourth segment 1111d. The first segment 1111a, the second segment 1111b, the third segment 1111c, and the fourth segment 1111d are sequentially fixedly connected to form the mesh unit 101. Each mesh unit 101 has a first connecting line 13. The first connecting line 13 sequentially connects the first segment 1111a, the second segment 1111b, the third segment 1111c, and the fourth segment 1111d. That is, the first connecting line 13 sequentially connects the first segment 1111a, the second segment 1111b, the third segment 1111c, and the fourth segment 1111d of a mesh unit 101 to the coating 12. It is understood that the aforementioned mesh unit 101 can be the mesh unit 101 of the first flange section 112 or the mesh unit 101 of the first leaf section 113.

[0047] like Figure 6 As shown, the end of the first flange section 112 away from the first leaf segment 113 has a wave-shaped structure. The wave-shaped structure is circumferentially arranged around the axis of the support 11. The wave-shaped structure includes multiple peaks 1121a and multiple troughs 1121b. A trough 1121b is connected between two adjacent peaks 1121a. The flange connecting section 121 includes multiple first connecting ends 1211 and multiple second connecting ends 1212 that are fixedly connected in sequence. A second connecting end 1212 is fixedly connected between two adjacent first connecting ends 1211. The first connecting ends 1211 and second connecting ends 1212 are connected in an arc shape. The distance from the first connecting end 1211 to the first leaf connecting section 122 is greater than... The distance from the second connecting end 1212 to the first leaflet connecting section 122 is such that each first connecting end 1211 is connected to each peak 1121a and each second connecting end 1212 is connected to each trough 1121b. In other words, the end of the flange connecting section 121 away from the first leaflet connecting section 122 is also wavy. This structural design can reduce the amount of material and the size of the artificial heart valve after compression, so as to reduce the damage to blood vessels after the artificial heart valve enters the human heart chamber. At the same time, the wavy design of the flange connecting section 121 of the membrane 12 can increase the imaging effect under ultrasound after the artificial heart valve is implanted in the human body, making the implantation operation of the artificial heart valve simpler.

[0048] like Figures 5 to 7As shown, the edge of the first connecting end 1211 away from the first leaflet connecting segment 122 is defined as the first edge 1211a, and the edge of the second connecting end 1212 away from the first leaflet connecting segment 122 is defined as the second edge 1212a. The distance between the first edge 1211a and the first leaflet segment 113 is greater than the distance between the peak 1121a and the first leaflet segment 113, and the distance between the second edge 1212a and the first leaflet segment 113 is greater than the distance between the trough 1121b and the first leaflet segment 113. Since the stent 11 will elongate after the artificial heart valve is compressed because the stent 11 is not deformable, it can only elongate along the space of the connecting part 1112 of the stent 11. Therefore, the dimensions of the first connecting end 1211 and the second connecting end 1212 of the covering 12 are both set beyond the first flange segment 112 of the stent 11 to compensate for the elongation of the stent 11 after the artificial heart valve is compressed and reduce the risk of the stent 11 bruising human tissue.

[0049] like Figure 5 and Figure 11 As shown, due to the significant curvature change in the connection area between the first flange segment 112 and the first leaflet segment 113 of the stent 11, the covering 12 is prone to generating more redundancy. Therefore, the connection between the first flange segment 112 and the first leaflet segment 113 is defined as the transition portion 115. The first leaflet connecting segment 122 is provided with multiple through holes 102, each through hole 102 is located in the transition portion 115, and each through hole 102 is correspondingly arranged with each support rod 111. Each through hole 102 is circumferentially arranged around the axis of the stent 11, and the through holes 102 are evenly spaced apart. This releases the redundancy of the covering 12, allowing the covering 12 to be evenly laid on the transition portion 115 of the stent 11, reducing the loading size of the artificial heart valve after compression, and reducing damage to blood vessels. In this embodiment, the through hole 102 is quadrilateral (e.g., Figure 11 As shown), vertical lines (such as...) Figure 12 (as shown) or elliptical (as shown) Figure 13 (as shown); wherein, the quadrilateral is preferably a rectangle, square or rhombus, etc.; the length direction of the vertical linear is the same as the axis direction of the support 11.

[0050] Preferably, the length of the through hole 102 along the axial direction of the bracket 11 is greater than the length of the through hole 102 along the radial direction of the bracket 11.

[0051] Second Embodiment

[0052] like Figure 14 As shown, the artificial heart valve in this embodiment is structurally similar to the artificial heart valve in the first embodiment, except that the first connecting line 13 is connected in a different way.

[0053] Specifically, segment 1111 includes a first segment 1111a, a second segment 1111b, a third segment 1111c, and a fourth segment 1111d. The first segment 1111a, the second segment 1111b, the third segment 1111c, and the fourth segment 1111d are connected in sequence to form a mesh unit 101. Each mesh unit 101 has four first connecting lines 13. The first segment 1111a, the second segment 1111b, the third segment 1111c, and the fourth segment 1111d are respectively connected to each of the first connecting lines 13 to increase the stability of the connection between the film 12 and the support 11.

[0054] Third Embodiment

[0055] like Figure 15 As shown, the artificial heart valve in this embodiment is structurally similar to the artificial heart valve in the first embodiment, except that the first connecting line 13 is connected in a different way.

[0056] Specifically, each first connecting line 13 is connected to each support rod 111. In this embodiment, since the support 11 includes multiple support rods 111, and the multiple support rods 11 intersect to form a grid structure, each support rod 111 is inclined relative to the axis of the support 11. Each support rod 111 participates in the formation of at least two mesh units 101. Therefore, in this embodiment, a first connecting line 13 stitches the film 12 to a complete support rod 111, which is a simple and quick stitching method.

[0057] The artificial heart valve of this invention uses a membrane 12 to wrap the first flange segment 112 and the first leaflet segment 113 of a stent 11. Different suturing methods are used depending on the different stiffnesses of the first flange segment 112 and the first leaflet segment 113 of the stent 11. A first connecting line 13 is used to fix the flange connecting segment 121 of the membrane 12 to a section 1111 in the mesh unit 101 of the first flange segment 112, and to fix the first leaflet connecting segment 122 of the membrane 12 to the section 1111 of the mesh unit 101. A second connecting line 14 is used to connect the first leaflet connecting segment 122 of the membrane 12 to the connecting portion 1112 of the mesh unit 101. This allows the first flange segment 112 of the stent 11 to move relative to the first leaflet connecting segment 122 of the cover 12 when it is gripped. The first leaflet connecting segment 122 will not restrict the gripping and unfolding of the first flange segment 112, reducing the risk of the cover 12 restricting the stent 11. When the first leaflet segment 113 of the stent 11 is gripped, the corresponding first leaflet connecting segment 122 can move with the movement of the first leaflet segment 113. The first leaflet segment 113 and the first leaflet connecting segment 122 always maintain a fixed connection relationship, preventing part of the structure of the stent 11 from being exposed outside the cover 12 after gripping or unfolding, thereby reducing the risk of the stent 11 damaging the original tissue of the human body.

[0058] The above are merely specific embodiments of this utility model, but the protection scope of this utility model is not limited thereto. Any variations or substitutions that can be easily conceived by those skilled in the art within the technical scope disclosed in this utility model should be included within the protection scope of this utility model. Therefore, the protection scope of this utility model should be determined by the appended claims.

Claims

1. An artificial heart valve, characterized in that, include: The support (11) includes a plurality of cross-connected support rods (111) forming a grid structure, and the portion where at least two of the support rods (111) are connected to each other is a connecting part (1112). The grid structure includes a plurality of mesh units (101), and each mesh unit (101) includes a plurality of the connecting parts (1112) and a section (1111) of the support rod (111) connected between two adjacent connecting parts (1112). The support (11) includes a first flange section (112) and a first leaf section (113) connected to each other along its axial direction. The membrane (12) includes a flange connection section (121) and a first leaflet connection section (122) connected to each other, the flange connection section (121) and the first leaflet connection section (122) being arranged along the axial direction of the bracket (11); Multiple first connecting lines (13), each mesh unit (101) is connected to at least one first connecting line (13), the first connecting line (13) is spirally wound around the segment (1111) of the mesh unit (101), the first connecting line (13) is used to connect the first flange segment (112) to the flange connecting segment (121) and to connect the first leaf segment (113) to the first leaf connecting segment (122); and Multiple second connecting lines (14) are spirally wound on the connecting portion (1112) of each mesh unit (101) of the first leaf segment (113), and each second connecting line (14) is used to connect the first leaf segment (113) and the first leaf connecting segment (122) together.

2. The artificial heart valve as described in claim 1, characterized in that, The segment (1111) includes a first segment (1111a), a second segment (1111b), a third segment (1111c), and a fourth segment (1111d). Each mesh unit (101) has a first connecting line (13), which connects the first segment (1111a), the second segment (1111b), the third segment (1111c), and the fourth segment (1111d) in sequence.

3. The artificial heart valve as described in claim 1, characterized in that, The segment (1111) includes a first segment (1111a), a second segment (1111b), a third segment (1111c), and a fourth segment (1111d). Each mesh unit (101) has four first connecting lines (13). The first segment (1111a), the second segment (1111b), the third segment (1111c), and the fourth segment (1111d) are respectively connected to each of the first connecting lines (13).

4. The artificial heart valve as described in claim 1, characterized in that, Each of the first connecting lines (13) is connected to each of the support rods (111) along the length direction of the support rod (111).

5. The artificial heart valve as described in claim 1, characterized in that, The end of the first flange section (112) away from the first leaf section (113) has a waveform structure. The waveform structure is arranged circumferentially around the axis of the support (11). The waveform structure includes multiple peaks (1121a) and multiple troughs (1121b). A trough (1121b) is connected between two adjacent peaks (1121a). The flange connecting section (121) includes multiple first connecting ends (1211) and multiple second connecting ends (1212) that are fixedly connected in sequence. The distance from the first connecting end (1211) to the first leaf connecting section (122) is greater than the distance from the second connecting end (1212) to the first leaf connecting section (122). Each first connecting end (1211) is connected to each peak (1121a), and each second connecting end (1212) is connected to each trough (1121b).

6. The artificial heart valve as described in claim 5, characterized in that, The edge of the first connecting end (1211) away from the first leaflet connecting segment (122) is defined as the first edge (1211a), and the edge of the second connecting end (1212) away from the first leaflet connecting segment (122) is defined as the second edge (1212a). The distance between the first edge (1211a) and the first leaflet segment (113) is greater than the distance between the crest (1121a) and the first leaflet segment (113), and the distance between the second edge (1212a) and the first leaflet segment (113) is greater than the distance between the trough (1121b) and the first leaflet segment (113).

7. The artificial heart valve as described in claim 1, characterized in that, The connection between the first flange section (112) and the first leaf section (113) is defined as the transition section (115). The first leaf connecting section (122) is provided with a plurality of through holes (102). Each through hole (102) is provided in the transition section (115). Each through hole (102) is correspondingly provided with each support rod (111). Each through hole (102) is circumferentially arranged around the axis of the bracket (11).

8. The artificial heart valve as described in claim 7, characterized in that, The length of the through hole (102) along the axis of the bracket (11) is greater than the length of the through hole (102) along the radial direction of the bracket (11).

9. The artificial heart valve as described in claim 8, characterized in that, The through hole (102) is quadrilateral, vertical line, or elliptical.

10. The artificial heart valve as described in claim 1, characterized in that, The support (11) further includes a second leaf segment (114), which is arranged along the axial direction of the support (11) and connected to the first leaf segment (113). The covering film (12) further includes a second leaf connecting segment (123), which is connected to the section (1111) of each of the mesh units (101). The second leaf connecting segment (123) does not cover the mesh unit (101).

11. The artificial heart valve according to any one of claims 1 to 10, characterized in that, The density of the mesh structure in the first flange segment (112) is less than the density of the mesh structure in the first leaf segment (113).

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