CN219021754U - Stent and valve prosthesis - Google Patents

Abstract

The utility model relates to a stent and a valve prosthesis. The first support section and the second support section of the support respectively comprise a plurality of wave rods which are connected end to end in sequence and are arranged in a V shape, and two adjacent wave rods of the same support section are in smooth transition; the adjacent two first support sections are connected in a staggered manner, so that a node part is formed between the corresponding crest part and trough part, and the minimum width D1 of the node part is more than or equal to 2 times of the width D2 of the wave rod of the first support section; the trough or crest of the second bracket section is connected with the corresponding node on the adjacent first bracket section through the axial strut. Through the arrangement, the expansion stability of the stent can be integrally improved, and the expansion uniformity of the stent is further improved, so that the valve works normally, and the anchoring strength of the stent can be ensured.

Description

Stent and valve prosthesis

Technical Field

The utility model relates to the technical field of medical equipment, in particular to a bracket and a valve prosthesis.

Background

Valves of the heart (e.g., aortic, pulmonary, tricuspid, and mitral valves) may suffer from various diseases that lead to cardiac dysfunction. Diseased heart valves (also known as native valves) may be stenotic and/or incompetent. The stenosed valve cannot be opened sufficiently to allow adequate blood flow. The incompetent valve cannot be fully closed resulting in backflow of blood and an increased number of valves than normal. Furthermore, the annulus and leaflets of the native valve become narrowed and calcification may occur. Accordingly, there has been a valve prosthesis that is implanted in the site of a native valve to firmly hold the valve stent within a stenotic annulus that may have calcified leaflets, with the diseased native valve being replaced by the valve prosthesis.

At present, two main valve stents have been put into clinical application, one is a balloon-expandable valve stent which is formed by a main stent structure of non-memory alloy and needs to be released in a balloon expansion mode; another type is a self-expandable valve stent, in which a stent body structure is formed of a memory metal material, and the self-expansion characteristic of the metal material is utilized to perform in vivo release and to stably anchor the stent in a lesion area.

For a balloon expandable valve stent, its transcatheter release is: the valve support is pressed and held onto the balloon by the pressing and holding machine, and the conveying system is connected with the balloon to convey the valve support into a patient for release. In the release process, as the expansion stroke of the valve stent is long, the plastic deformation degree is large, and the calcification condition of the lesion part is different, the valve stent is easy to deform unevenly, so that the valve cannot work normally, factors such as failure to close, reflux, EOA (effective opening area) reduction and the like are easy to occur, and the anchoring of the valve stent is easy to be influenced by the uneven deformation.

Disclosure of Invention

Based on the above, the stent and the valve prosthesis can solve the problem that the existing valve stent is unevenly deformed in the release process.

The support comprises a plurality of first support sections and second support sections which are sequentially arranged along the direction from an inflow end to an outflow section, wherein the first support sections and the second support sections comprise a plurality of wave rods which are sequentially connected end to end and are arranged in a V shape, and two adjacent wave rods of the same support section are in smooth transition;

the adjacent two first bracket sections are connected in a staggered manner, so that a node part is formed between corresponding wave crest parts and wave trough waves, and the minimum width D1 of the node part is more than or equal to 2 times of the wave rod width D2 of the first bracket sections; the trough part or the crest part of the second bracket section is connected with the corresponding node part on the adjacent first bracket section through an axial supporting rod; the trough parts of the first bracket section and the second bracket section are respectively one end relatively close to the inflow end of the bracket, and the crest parts are respectively one end relatively close to the outflow end of the bracket.

In one embodiment, the radius R1 of the transition fillet between two adjacent wave rods of the same bracket section is greater than or equal to 0.5mm and less than or equal to 2mm.

In one embodiment, the node portion has a smooth or rounded transition between the inflow end and the outflow end.

In one embodiment, a radius R2 of a transition fillet between the inflow end and the outflow end of the node portion is greater than or equal to 0.5mm and less than or equal to 2mm.

In one embodiment, at least one of the node portions spaced closest to the stent outflow end is connected to a corresponding one of the axial struts.

In one embodiment, the width D3 of the wave rod of the second bracket segment is greater than the width D2 of the wave rod of the first bracket segment.

In one embodiment, an angle formed between two adjacent waverods of the same bracket section is greater than or equal to 90 °.

In one embodiment, the axial struts are either non-porous struts or at least a portion of the axial struts are porous struts.

A valve prosthesis comprising the stent of any one of the above and at least two leaflets, the petals She Shezhi on the stent.

In one embodiment, the leaflet is connected to the axial strut; and/or

The valve prosthesis further includes a leaflet connector for positioning the valve She Anzhuang on an axial strut of the stent.

In one embodiment, the leaflet connecting piece comprises a clamping part, a first connecting part and a second connecting part, wherein the clamping part is clamped on the axial supporting rod, a gap is reserved between the head and the tail of the clamping part, the first connecting part and the second connecting part are respectively connected with the head and the tail of the clamping part, and the leaflet extends into the space between the first connecting part and the second connecting part and is connected with the first connecting part and the second connecting part.

Above-mentioned support and valve prosthesis, the smooth transition between adjacent ripples pole on the same first support section of support, and the minimum width D1 of the node between two adjacent first support sections is greater than or equal to 2 times first support section's ripples pole width D2, improves support inflow end expansion stability, and then improves support expansion homogeneity, and the support can not touch between the ripples pole in the pressure holding in-process, helps reducing the risk that the ripples pole pressed from both sides valve leaflet and sacculus. Smooth transition between adjacent wavebars on the same first support section, and trough parts or wave crest parts are connected with corresponding node parts on the first support section through axial struts, so that the expansion stability of the outflow end of the support can be improved, the traction deformation in the working process of the support can be reduced, the risk of failure of a valve after the support is completely expanded is reduced, and the service life of the valve leaflet is prolonged. In conclusion, through the arrangement, the expansion stability of the stent can be integrally improved, and the expansion uniformity of the stent is further improved, so that the valve works normally, and the anchoring strength of the stent can be ensured.

Drawings

FIG. 1 is a schematic structural view of a bracket according to an embodiment of the present utility model;

FIG. 2 is a schematic view of a stent according to an embodiment of the present utility model after being deployed;

FIG. 3 is an enlarged partial schematic view of FIG. 2;

FIG. 4 is a schematic view of a stent according to another embodiment of the present utility model after deployment;

FIG. 5 is a schematic view of a stent according to another embodiment of the present utility model after deployment;

FIG. 6 is a schematic view of a stent according to another embodiment of the present utility model after deployment;

FIG. 7 is a schematic view of a valve prosthesis according to another embodiment of the present utility model, as seen from the outflow end to the inflow end;

fig. 8 and 9 are enlarged schematic views of a valve prosthesis according to another embodiment of the present utility model, from different angles.

Wherein, the reference numerals in the drawings are as follows:

10. a bracket; 100. a first bracket section; 10a, a wave rod; 10b, trough portions; 10c, a peak portion; 10d, a node part; 200. a second bracket section; 300. an axial strut; 300a, suture holes; 20. valve leaves; 30. a leaflet attachment; 30a, an engagement portion; 30b, a first connection portion; 30c, third connection portion.

Detailed Description

In order that the above objects, features and advantages of the utility model will be readily understood, a more particular description of the utility model will be rendered by reference to the appended drawings. In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present utility model. The present utility model may be embodied in many other forms than described herein and similarly modified by those skilled in the art without departing from the spirit of the utility model, whereby the utility model is not limited to the specific embodiments disclosed below.

In the description of the present utility model, it should be understood that the terms "center", "longitudinal", "lateral", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "radial", "circumferential", etc. indicate orientations or positional relationships based on the orientations or positional relationships shown in the drawings are merely for convenience in describing the present utility model and simplifying the description, and do not indicate or imply that the device or element being referred to must have a specific orientation, be configured and operated in a specific orientation, and therefore should not be construed as limiting the present utility model.

Furthermore, the terms "first," "second," and the like, are used for descriptive purposes only and are not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include at least one such feature. In the description of the present utility model, the meaning of "plurality" means at least two, for example, two, three, etc., unless specifically defined otherwise.

In the present utility model, unless explicitly specified and limited otherwise, the terms "mounted," "connected," "secured," and the like are to be construed broadly, and may be, for example, fixedly connected, detachably connected, or integrally formed; can be mechanically or electrically connected; either directly or indirectly, through intermediaries, or both, may be in communication with each other or in interaction with each other, unless expressly defined otherwise. The specific meaning of the above terms in the present utility model can be understood by those of ordinary skill in the art according to the specific circumstances.

In the present utility model, unless expressly stated or limited otherwise, a first feature "up" or "down" a second feature may be the first and second features in direct contact, or the first and second features in indirect contact via an intervening medium. Moreover, a first feature being "above," "over" and "on" a second feature may be a first feature being directly above or obliquely above the second feature, or simply indicating that the first feature is level higher than the second feature. The first feature being "under", "below" and "beneath" the second feature may be the first feature being directly under or obliquely below the second feature, or simply indicating that the first feature is less level than the second feature.

It will be understood that when an element is referred to as being "fixed" or "disposed" on another element, it can be directly on the other element or intervening elements may also be present. When an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may also be present. The terms "vertical," "horizontal," "upper," "lower," "left," "right," and the like are used herein for illustrative purposes only and are not meant to be the only embodiment.

Referring to fig. 1 and 2, fig. 1 shows a schematic structural view of a stent 10 according to an embodiment of the present utility model, and fig. 2 shows a schematic structural view of a stent 10 according to an embodiment of the present utility model after being unfolded. According to the bracket 10 provided by the embodiment of the utility model, the bracket 10 comprises a first bracket section 100 and a second bracket section 200 which are sequentially arranged along the direction from an inflow end to an outflow end, wherein the first bracket section 100 and the second bracket section 200 respectively comprise a plurality of wave rods 10a which are sequentially connected end to end and are arranged in a V shape, and two adjacent wave rods 10a of the same bracket section are in smooth transition; the adjacent two first bracket sections 100 are connected in a staggered manner, so that the corresponding crest portions 10c and trough portions 10b form node portions 10D, and the minimum width D1 of the node portions 10D is greater than or equal to 2 times the wave rod width D2 of the first bracket sections 100; the trough portions 10b or the crest portions 10c of the second stent section 200 are connected with the corresponding node portions 10d on the adjacent first stent section 100 by the axial struts 300; the trough portions 10b of the first and second stent sections 100, 200 each refer to an end relatively close to the inflow end of the stent 10, and the crest portions 10c each refer to an end relatively close to the outflow end of the stent 10.

It will be appreciated that the peak portions 10c of two adjacent first carrier sections 100 are offset, and the valley portions 10b of two adjacent first carrier sections 100 are also offset. For any two adjacent first stent sections 100, the trough portion 10b of one first stent section 100 that is relatively close to the second stent section 200 is connected to the corresponding crest portion 10c of the other first stent section 100 to form a node portion 10d.

Throughout, the term "axial direction" refers to the direction in which the central axis of the stent 10 extends.

As shown in fig. 3, the minimum width D1 of the node portion 10D refers to the minimum distance between the opposite faces, and the width D2 of the wave rod of the first bracket segment 100 refers to the distance between the opposite faces of the wave rod.

It should be noted that, the smooth transition refers to no edge angle between two adjacent waverods 10a of the same stent segment, so that the stress distribution of the stent 10 in the expanding process is more uniform, and the situation of instability is not easy to occur.

The stent 10 may be installed in various arterial vessels, venous vessels, etc., such as the location of a native valve. It should be noted that, the terms "inflow end" and "outflow end" of the stent 10 are defined throughout in terms of the blood flow direction, wherein blood enters from the inflow end of the stent 10 and exits through the outflow end of the stent 10, so that after the stent 10 is implanted at the aortic valve, the inflow end of the stent 10 faces the left ventricle and the outflow end faces the ascending aorta.

The first and second stent sections 100, 200, 300 of the stent 10 described above include, but are not limited to, cobalt chrome alloy, nickel titanium alloy, stainless steel, but may be formed from other medical grade metallic materials and/or medical grade nonmetallic materials. The characteristics of good biocompatibility, durability and longer service life of cobalt-chromium alloy, nickel-titanium alloy and stainless steel are considered, and the cobalt-chromium alloy, nickel-titanium alloy and stainless steel can be preferentially adopted.

In the stent 10 described above, the adjacent waverods 10a on the same first stent segment 100 are in smooth transition, and the minimum width D1 of the node 10D between two adjacent first stent segments 100 is greater than or equal to 2 times the waverod width D2 of the first stent segment 100, so that the stability of expansion of the inflow end of the stent 10 is improved, and further the uniformity of expansion of the stent 10 is improved, and the waverods 10a are not touched in the pressing and holding process of the stent 10, which is helpful for reducing the risk of damaging the valve leaflet and the balloon by the waverods 10a; smooth transition is carried out between adjacent waverods 10a on the same first support section 100, and trough parts 10b or crest parts 10c are connected with corresponding node parts 10d on the first support section 100 through axial struts 300, so that the expansion stability of the outflow end of the support 10 can be improved, the traction deformation of the support 10 in the working process can be reduced, the risk of failure of a valve after the support 10 is fully expanded is reduced, and the service life of the valve leaflet 20 is prolonged. In summary, through the above arrangement, the expansion stability of the stent 10 can be integrally improved, and the expansion uniformity of the stent 10 is further improved, so that the valve can work normally, and the anchoring strength of the stent 10 can also be ensured.

In some embodiments of the utility model, the sum of the number of first and second stent sections 100, 200 may be greater than or equal to 4, such as 4, 5, 6, 7, etc. Thus, the anchoring strength and the radial supporting strength of the stent 10 can be ensured, and the occurrence of paravalvular leakage can be effectively avoided.

Optionally, the number of wavebars per first stent section 100 is less than or equal to 24, such as 24, 23, 22, 21, etc.

Wherein the number of the first support sections 100 may be greater than or equal to 3, such as 3, 4, 5, etc., and the number of the second support sections 200 is greater than or equal to 1, preferably 1. When the number of second stent sections 200 is plural, wherein a second stent section 200 relatively near the inflow end of the stent 10 is connected to the first stent section 100 by axial struts 300, the troughs (peaks) of adjacent second stent sections 200 are aligned or staggered, and adjacent second stent sections 200 may be connected in the manner of the connection of the first stent section 100 or may be connected by axial struts 300.

In some embodiments of the present utility model, the angle formed between two waverods 10a adjacent to the same stent segment is greater than or equal to 90 °, such as 90 °, 100 °, 110 °, 120 °, 130 °, 140 °, 150 °, etc. This increases the radial support force of the stent 10 and is beneficial for reducing the overall height of the stent 10.

In some embodiments of the utility model, the radius R1 of the transition fillet between two adjacent stems 10a of the same carrier section is greater than or equal to 0.5mm and less than or equal to 2mm, for example the transition fillet R may be set to 0.5mm, 1mm, 1.5mm, 2mm, etc. In this manner, stability of stent 10 in the expansion of the inflow end can be improved.

In some embodiments of the present utility model, the node portion 10d has a smooth transition or rounded transition between the inflow end and the outflow end. It should be noted that the above-described smooth transition means that the width between the inflow end and the outflow end of the node portion 10d has no stepwise abrupt change; the smooth transition refers to no edge angle between the inflow end and the outflow end of the node portion 10d, so that the stress distribution of the node portion 10d is relatively uniform in the expansion process of the stent 10, and instability is not easy to occur.

Specifically, in some embodiments of the present utility model, the radius R2 of the transition fillet between the inflow end and the outflow end of the node portion 10d is greater than or equal to 0.5mm and less than or equal to 2mm, and for example, the transition fillet R2 may be set to 0.5mm, 1mm, 1.5mm, 2mm, or the like. By means of the arrangement, on the premise that the stress distribution of the node part 10D is uniform, the width D1 of the node part 10D can be ensured to be larger than the width D2 of the wave rod of the first support segment 100 by 2 times, meanwhile, the wave rods 10a cannot be completely closed when the support 10 is pressed and held by utilizing large-fillet transition, and the risk that the wave rods 10a clamp the balloon and the valve leaflet is reduced.

As shown in fig. 1-5, in some embodiments of the present utility model, the axial struts 300 have inflow ends connected to corresponding nodes 10d and outflow ends connected to corresponding valleys 10b on the second stent section 200. Compared with the connection of the axial strut 300 with the corresponding crest portion 10c of the second stent section 200, the connection provided in this embodiment can reduce the height of the stent 10, facilitate the release of the stent 10, and reduce the dog bone effect when the stent 10 is expanded. The dog bone effect is a phenomenon that when the stent 10 expands to the maximum, inflow and outflow ends are tilted first, and the diameters of the two ends of the stent 10 are larger than the diameter of the middle part of the stent 10, so that the stent looks like a dog bone, and the dog bone effect is called, wherein the larger dog bone rate can cause damage to blood vessels, and the dog bone rate is reduced as much as possible. The middle portion of the stent 10 refers to a portion between the outflow end and the inflow end of the stent 10.

In some embodiments of the present utility model, as shown in fig. 1, 3 and 4, at least one node 10d spaced closest to the outflow end of the stent 10 is connected to a corresponding axial strut 300. By the arrangement, the grids formed between the second bracket section 200 and the first bracket section 100 are larger and sparser, and the number of the wave rods 10a of the second bracket section 200 distributed in the circumferential direction of the bracket 10 can be reduced, so that the risk of the collision of the bracket 10 in the pressing and holding process can be avoided, the diameter of the bracket 10 after pressing and holding can be reduced, and the intervention of the PCI (Percutaneous Coronary Intervention percutaneous coronary intervention) of a later patient can be facilitated.

As an example, referring to fig. 2, each node portion 10d closest to the outflow end of the stent 10 is connected to a corresponding axial strut 300, i.e., one node portion 10d is distributed between two adjacent axial struts 300.

Further, in some embodiments of the present utility model, the wave rod width D3 of the second bracket segment 200 is greater than the wave width D2 of the first bracket segment 100. Since the number of the wave rods 10a of the second bracket section 200 distributed in the circumferential direction of the bracket 10 is reduced, resulting in a decrease in the strength of the outflow end of the bracket 10, the strength of the outflow end of the bracket 10 is increased by increasing the wave rod width of the second bracket section 200.

As shown in fig. 3, the width D3 of the wave beam of the second bracket segment 100 refers to the distance between the opposite faces of the wave beam.

As shown in fig. 1, 2, and 4-6, in some embodiments of the utility model, axial struts 300 are all non-porous struts or at least a portion of axial struts 300 are porous struts. It should be noted that the axial struts 300 which are provided with suture holes for suturing the leaflet 20 are defined as holed struts, and the axial struts 300 which are not provided with suture holes for suturing the leaflet 20 are defined as non-holed struts. The leaflet 20 can be secured by the leaflet attachment 30, which reduces the width of the axial strut 300 from about 1.3mm to 0.3mm to 0.4mm, which further reduces the diameter of the stent 10 after crimping. It should be noted that, regarding the structure of the leaflet attachment 30 and how to implement the leaflet 20 disposed on the axial strut 300, the following description will not be made here in detail.

Wherein, the axial struts 300 on the stent 10 may be non-porous struts (see fig. 5 and 6); only a part of the axial struts 300 may be porous struts, and the other part of the axial struts 300 may be non-porous struts (see fig. 1, 2, and 4), and 1 or more axial struts 300 not having suture holes 300a may be provided for every 1 or more axial struts 300 having suture holes 300a (i.e., non-porous struts), for example, 1 axial strut 300 not having suture holes 300a may be provided for every 1 axial strut 300 having suture holes 300a.

In another aspect, as shown in fig. 7, an embodiment of the present utility model further provides a valve prosthesis, which includes the stent 10 of any one of the above and at least two leaflets 20, wherein the leaflets 20 are disposed on the stent 10.

In the valve prosthesis, the adjacent waverods 10a on the same first support section 100 of the support 10 are in smooth transition, the minimum width D1 of the node part 10D between the adjacent two first support sections 100 is more than or equal to 2 times of the waverod width D2 of the first support section 100, so that the expansion stability of the inflow end of the support 10 is improved, the expansion uniformity of the support 10 is further improved, the waverods 10a of the support 10 cannot touch each other in the pressing and holding process, and the risk that the waverods 10a clamp the valve leaflets and the sacculus is reduced; smooth transition is carried out between adjacent waverods 10a on the same first support section 100, and trough parts 10b or crest parts 10c are connected with corresponding node parts 10d on the first support section 100 through axial struts 300, so that the expansion stability of the outflow end of the support 10 can be improved, the traction deformation of the support 10 in the working process can be reduced, the risk of failure of a valve after the support 10 is fully expanded is reduced, and the service life of the valve leaflet 20 is prolonged.

In some embodiments of the utility model, the leaflet 20 is attached to the axial struts 300, such as by suturing with sutures.

Of course, as shown in fig. 7 and 8, in other embodiments of the present utility model, the valve prosthesis further includes a leaflet attachment 30, the leaflet attachment 30 being used to mount the leaflet 20 on the axial struts 300 of the stent 10. In this way, the width of the axial strut 300 can be reduced without providing a suture hole 300a for suturing the leaflet 20 to the axial strut 300 on the axial strut 300 of the stent 10, so that the diameter of the stent 10 after crimping can be further reduced.

As an alternative, as shown in fig. 9, the leaflet attachment 30 includes: the engaging portion 30a, the first connecting portion 30b, and the second connecting portion 30c; the engaging portion 30a is clamped on the axial strut 300, the head and the tail of the engaging portion 30a have a gap, the first connecting portion 30b and the second connecting portion 30c are connected with the head and the tail of the engaging portion 30a respectively, and the valve leaflet 20 extends between the first connecting portion 30b and the second connecting portion 30c and is connected with the first connecting portion and the second connecting portion. The engaging portion 30a may be clamped to the axial strut 300 by its own elasticity, and of course, the engaging portion 30a may be bound to the axial strut 300 by a suture.

Alternatively, the material of the leaflet attachment member 30 may be the same as that of the stent 10, such as cobalt chrome alloy, nickel titanium alloy, stainless steel, etc.; the material of the valve leaflet 20 is the same as that of the flexible material such as bovine pericardium and porcine pericardium. The engaging portion 30a, the first connecting portion 30b, and the second connecting portion 30c may be integrally formed and may be formed by bending a metal sheet.

Alternatively, the first and second connection portions 30b and 30c may cooperate to clamp the leaflet 2. Wherein, holes can be perforated on the first connecting part 30b and the second connecting part 30c, so that the leaflet connecting piece 30 and the leaflet 20 are sutured together, and the stent 10 and the leaflet 20 are connected together.

To further describe the stent 10 as described above, four embodiments are given as follows:

example 1

As shown in fig. 1 and 2, this embodiment provides a stent 10, the stent 10 comprising 5 first stent sections 100 and 1 second stent section 200 arranged in sequence from the inflow end to the outflow end.

Each first bracket section 100 comprises 24 wave rods 10a which are connected end to end in sequence and are arranged in a V shape; the two adjacent wave rods 10a of the same bracket section are in smooth transition, the transition round angle R1 is more than or equal to 0.5mm and less than or equal to 2mm, and the angle formed between the two adjacent wave rods 10a is more than 90 degrees; the trough portions 10b and the crest portions 10c of two adjacent first bracket sections 100 are staggered, wherein the crest portions 10c of the first bracket sections 100 relatively close to the inflow end of the bracket 10 are connected with the corresponding trough portions 10b of the first bracket sections 100 relatively close to the outflow end of the bracket 10 to form a node portion 10d. The minimum width D1 of the node portion 10D is greater than or equal to 2 times the wave rod width D2 of the first bracket segment 100, and the transition angle R2 between the inflow end and the outflow end of the node portion 10D is greater than or equal to 0.5mm and less than or equal to 2mm.

Each second bracket section 200 comprises 24 wave rods 10a which are connected end to end in sequence and are arranged in a V shape; the two adjacent wave rods 10a of the same bracket section are in smooth transition, the transition round angle R1 is more than or equal to 0.5mm and less than or equal to 2mm, and the angle formed between the two adjacent wave rods 10a is more than 90 degrees; the trough portions 10b of the second stent section 200 are connected to the corresponding node portions 10d on the adjacent first stent section 100 by axial struts 300; no node 10d is distributed between two adjacent axial struts 300; suture holes 300a are provided every 1 axial strut 300.

Example 2

Unlike the stent 10 provided in embodiment 1, as shown in fig. 5, the stent 10 provided in this embodiment has no suture holes 300a formed in the axial struts 300.

Example 3

As shown in fig. 4, unlike the stent 10 provided in embodiment 1, the stent 10 provided in this embodiment includes 12 wave rods 10a per second stent section 200 and the width D3 of the wave rods 10a is greater than the wave rod width D2 of the first stent section 100, and one node portion 10D is connected to the corresponding axial strut 300 every other.

Example 4

Unlike the stent 10 provided in embodiment 3, as shown in fig. 6, the stent 10 provided in this embodiment has no suture holes 300a formed in the axial struts 300.

The technical features of the above-described embodiments may be arbitrarily combined, and all possible combinations of the technical features in the above-described embodiments are not described for brevity of description, however, as long as there is no contradiction between the combinations of the technical features, they should be considered as the scope of the description.

The above examples illustrate only a few embodiments of the utility model, which are described in detail and are not to be construed as limiting the scope of the utility model. It should be noted that it will be apparent to those skilled in the art that several variations and modifications can be made without departing from the spirit of the utility model, which are all within the scope of the utility model. Accordingly, the scope of protection of the present utility model is to be determined by the appended claims.

Claims (11)

1. The support is characterized by comprising a plurality of first support sections and second support sections which are sequentially arranged along the direction from an inflow end to an outflow end, wherein the first support sections and the second support sections comprise a plurality of wave rods which are sequentially connected end to end and are arranged in a V shape, and two adjacent wave rods of the same support section are in smooth transition;

the adjacent two first support sections are connected in a staggered mode, so that node parts are formed between corresponding wave crest parts and wave trough waves, and the minimum width D1 of the node parts is larger than or equal to 2 times of the wave rod width D2 of the first support sections; the trough part or the crest part of the second bracket section is connected with the corresponding node part on the adjacent first bracket section through an axial supporting rod; the trough parts of the first bracket section and the second bracket section are respectively one end relatively close to the inflow end of the bracket, and the crest parts are respectively one end relatively close to the outflow end of the bracket.

2. The stent of claim 1, wherein the radius R1 of a transition fillet between two adjacent struts of the same stent segment is greater than or equal to 0.5mm and less than or equal to 2mm.

3. The stent of claim 1, wherein the node portion has a smooth transition or rounded transition between the inflow end and the outflow end.

4. A stent according to claim 3, wherein the radius R2 of the transition fillet between the inflow end and the outflow end of the node portion is greater than or equal to 0.5mm and less than or equal to 2mm.

5. The stent of claim 1, wherein at least one of the node portions spaced closest to the outflow end of the stent is connected to a corresponding axial strut.

6. The stent of claim 5 wherein the strut width D3 of the second stent section is greater than the strut width D2 of the first stent section.

7. A stent according to any one of claims 1 to 6 wherein the angle formed between two adjacent wavebars of the same stent section is greater than or equal to 90 °.

8. The stent of any one of claims 1-6, wherein the axial struts are all non-porous struts or at least a portion of the axial struts are porous struts.

9. A valve prosthesis comprising the stent of any one of claims 1-8 and at least two leaflets, the leaflets She Shezhi being on the stent.

10. The valve prosthesis of claim 9, wherein the leaflet is connected to the axial struts; and/or

The valve prosthesis further includes a leaflet connector for positioning the valve She Anzhuang on an axial strut of the stent.

11. The valve prosthesis of claim 10, wherein the leaflet attachment comprises: the clamping part, the first connecting part and the second connecting part;

the clamping part is clamped on the axial supporting rod, a gap is reserved between the head part and the tail part of the clamping part, the first connecting part and the second connecting part are connected with the head part and the tail part of the clamping part respectively, and the valve leaflet extends into the space between the first connecting part and the second connecting part and is connected with the first connecting part and the second connecting part.

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