Lumen stent

Abstract

The present invention provides a lumen stent, which includes a mesh cover. The mesh cover includes at least one row of hooking units. Each hooking unit includes a first hooking member and a second hooking member that are sequentially hooked to each other from the proximal end to the distal end. The first hooking member includes a trough and two first wave rods connected to the trough. The second hooking member includes a crest and two second wave rods connected to the crest. The trough of the first hooking member and the crest of the second hooking member can move relative to each other axially; in the axial direction, the mesh cover includes a proximal cover and a distal cover. In the proximal cover, the first wave rod on the side close to the radial edge of the mesh cover in the same hooking unit straddles from above the second wave rod; and / or, in the distal cover, the second wave rod on the side close to the radial edge of the mesh cover in the same hooking unit straddles from above the first wave rod. The present invention enables the mesh holes on the radial sides of the proximal cover and / or the distal cover to undergo large deformations under external forces, so as to expand large enough to facilitate the guide wire and the bridging stent to pass through the mesh holes.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and particularly to a lumen stent. Background Art

[0002] Traditional open surgeries for treating vascular diseases such as aortic aneurysm and aortic dissection have problems such as large trauma, high mortality rate, long operation time, high incidence of postoperative complications, and high operation difficulty. While the minimally invasive interventional procedure for treating vascular diseases has advantages such as small trauma, high safety, and high effectiveness, and thus has been affirmed by doctors and patients and has become an important treatment method for vascular diseases. The interventional treatment method refers to implanting a vascular stent into the diseased segment of a patient's blood vessel through a delivery system. The implanted vascular stent can support the stenosed or occluded blood vessel segment or block the tear in the blood vessel dissection through expansion, reduce the elastic recoil and remodeling of the blood vessel, maintain the patency of the lumen blood flow, and prevent blood vessel stenosis.

[0003] When an aneurysm or arterial dissection is located at a position on the aorta close to a branch blood vessel, a stent with a groove can be implanted. The groove corresponds to the branch blood vessel to ensure that the blood in the aorta enters the branch blood vessel through the groove, which can not only support the stenosed or occluded blood vessel segment or block the tear in the blood vessel dissection, but also maintain the patency of the blood supply of the branch. For a blood vessel with a true lumen stenosis or distortion, a mesh cover can also be correspondingly arranged on the groove. The mesh cover has a good supporting effect and can avoid the extrusion of the lumen on the groove and compress the operation space. However, the arrangement of the mesh cover is likely to cause obstruction to the guide wire or bridging stent. Summary of the Invention

[0004] Aiming at the deficiencies in the above-mentioned technology, the present invention provides a lumen stent that can reduce the obstruction to the guide wire or bridging stent.

[0005] A lumen stent includes a mesh cover. The mesh cover includes at least one column of hooking units. Each hooking unit includes a first hooking member and a second hooking member that are sequentially hooked to each other from the proximal end to the distal end. The first hooking member includes a trough and two first wave bars connected to the trough. The second hooking member includes a crest and two second wave bars connected to the crest. The trough of the first hooking member and the crest of the second hooking member can move relatively axially. The mesh cover includes a proximal cover and a distal cover axially. In the proximal cover, the first wave bar of the same hooking unit close to the radial edge of the mesh cover crosses over the second wave bar; and / or, in the distal cover, the second wave bar of the same hooking unit close to the radial edge of the mesh cover crosses over the first wave bar.

[0006] In one embodiment, there is a hooking gap between the first hooking member and the second hooking member of the same hooking unit.

[0007] In one embodiment, the troughs and the peaks include cross bars, and the two first wave bars are connected by the cross bars, and / or the two second wave bars are connected by the cross bars.

[0008] In one embodiment, the angle formed between the first wave bar and the cross bar is an obtuse angle, and / or the angle formed between the second wave bar and the cross bar is an obtuse angle.

[0009] In one embodiment, the cross bar is a straight bar or an arc-shaped bar.

[0010] In one embodiment, along the circumference of the lumen stent, the mesh cover includes a first mesh area and at least two second mesh areas respectively connected to both sides of the first mesh area; the second mesh area includes at least one row of the hook units, and the first mesh area includes multiple rows of cross units.

[0011] In one embodiment, the first wave bar and the second wave bar on one side of the hook unit close to the radial edge of the mesh cover form an axial interval, and the multiple axial intervals formed by the hook units in the same row include an end interval and an intermediate interval. The end interval is closer to the axial end of the mesh cover than the intermediate interval, and the maximum axial length of at least one end interval is greater than the maximum axial length of the intermediate interval.

[0012] In one embodiment, the mesh cover further includes at least one row of side connectors provided on the radial side of the mesh cover. The side connectors are connected to the hook units, and the side connectors include connection holes for connection.

[0013] In one embodiment, the mesh cover further includes side end connectors provided at the axial ends of the mesh cover. The multiple side connectors in the same row include two first side connectors and a second side connector located between the two first side connectors. The first side connectors are respectively connected to the side end connectors and the hook units in the axial direction, and the second side connector is respectively connected to a first hook member and a second hook member.

[0014] In one embodiment, the lumen stent further includes a main stent. The main stent includes an inner cavity, and the side surface of the main stent is radially recessed inward to form a groove. The mesh cover is connected to the groove, and at least a part of the mesh cover and the bottom of the groove form a radial interval in the radial direction of the lumen stent. The radial interval communicates with the inner cavity.

[0015] In one embodiment, the mesh cover is connected to the main stent through multiple side connectors, and the interval formed between two adjacent side connectors communicates with the radial interval.

[0016] The beneficial effects of the present invention are as follows: Compared with the prior art, the present invention provides a lumen stent, including a mesh cover. The mesh cover includes at least one row of hooking units. Each hooking unit includes a first hooking member and a second hooking member that are successively hooked to each other from the proximal end to the distal end. The first hooking member includes a trough and two first wave rods connected to the trough. The second hooking member includes a peak and two second wave rods connected to the peak. The trough of the first hooking member and the peak of the second hooking member are axially relatively movable; the mesh cover includes a proximal cover and a distal cover axially. In the proximal cover, the first wave rod on the side close to the radial edge of the mesh cover in the same hooking unit straddles above the second wave rod; and / or, in the distal cover, the second wave rod on the side close to the radial edge of the mesh cover in the same hooking unit straddles above the first wave rod. The wave rod above can be separated from the wave rod below in the radial direction of the lumen stent, so as to have better upward deformation ability and space, so that the mesh holes on the radial side edges of the proximal cover and / or the distal cover can be greatly deformed under the action of an external force to expand large enough to facilitate the guide wire and the bridging stent to pass through the mesh holes. When the external force is withdrawn, the mesh holes can retract to play a certain supporting and limiting role for the bridging stent, reducing the situation that the bridging stent swings with the blood flow or heart pulsation, so as to ensure the stability of the branch blood supply. BRIEF DESCRIPTION OF THE DRAWINGS

[0017] Figure 1 Schematic diagram of the lumen stent of the present invention;

[0018] Figure 2 Schematic diagram of the unfolded structure of the mesh cover of the present invention;

[0019] Figure 3 Schematic diagram of the unfolded structure of the mesh cover of another embodiment of the present invention;

[0020] Figure 4 Stereogram of the mesh cover structure of the present invention;

[0021] Figure 5 Of the present invention Figure 4 Partial enlarged view of position A;

[0022] Figure 6 Of the present invention Figure 4 Partial enlarged view of position B;

[0023] Figure 7 Of the present invention Figure 4 Partial enlarged view of position C;

[0024] Figure 8 Of the present invention Figure 4 Partial enlarged view of position D;

[0025] Figure 9 A perspective view of the mesh cover structure in another embodiment of the present invention;

[0026] Figure 10 of the present invention Figure 9 A partially enlarged view of position E in

[0027] Figure 11 A perspective view of the mesh cover structure in yet another embodiment of the present invention;

[0028] Figure 12 A schematic perspective view of the proximal segment of the lumen stent of the present invention;

[0029] Figure 13 of the present invention Figure 12 A partially enlarged view of position F in

[0030] Figure 14 A schematic view of the suture of the middle wave angle and the proximal main body film in an embodiment of the present invention;

[0031] Figure 15 of the present invention Figure 14 A partially enlarged view of position G in Detailed implementation manners

[0032] To better understand the concept of the present invention, the following specifically describes the implementation manners of the present invention with reference to the accompanying drawings. The following specific embodiments are only partial embodiments of the present invention and do not limit the present invention.

[0033] For ease of description, spatial relative relationship terms may be used in the text to describe the relationship of one element or feature shown in the figure relative to another element or feature. These relative relationship terms are, for example, "inside", "outside", "inner side", "outer side", "below", "beneath", "above", "over". Such spatial relative relationship terms are intended to include different orientations of the device in use or operation in addition to the orientation depicted in the figure. For example, if the device in the figure is flipped, then an element described as "below" or "beneath" other elements or features will then be oriented as "above" or "over" other elements or features. Thus, the exemplary term "below" can include both the upper and lower orientations. The device may be otherwise oriented (rotated 90 degrees or in other directions) and the spatial relative relationship descriptors used in the text are accordingly interpreted.

[0034] To more clearly describe the structure of the present application, the terms "proximal end" and "distal end" are defined herein as the commonly used terms in the field of interventional medicine. Specifically, the "distal end" refers to the end where blood flows out, and the "proximal end" refers to the end where blood flows in. For example, after stent implantation, blood flows from the proximal end to the distal end of the stent; the "axial direction" refers to its length direction, and the "radial direction" refers to the direction perpendicular to the "axial direction".

[0035] The "wave loop" (also known as the waveform ring) in the present invention is a closed ring structure, and the "waveform unit" is an arc structure. The "wave loop" and the "waveform unit" are made by weaving or cutting a metal elastic material or a polymer material. The metal elastic material includes known materials implanted in medical devices or combinations of various biocompatible materials, such as alloys of two or more single metals among cobalt, chromium, nickel, titanium, magnesium, iron, and 316L stainless steel, nickel-titanium-tantalum alloy, etc., or other metal elastic materials with biocompatibility. The polymer material includes biocompatible materials such as polylactic acid. Both the "wave loop" and the "waveform unit" have the ability to expand radially, can achieve radial contraction under external force, and can self-expand or expand mechanically (for example, expand by balloon dilation) to return to and maintain their initial shape after the external force is withdrawn. Thus, after being implanted into the lumen, they can closely adhere to the inner wall of the lumen through their radial supporting force. The waveform of the waves in the "wave loop" and the "waveform unit" is not limited, including Z-shaped waves, M-shaped waves, V-shaped waves, sine waves, etc. Both the "wave loop" and the "waveform unit" include multiple wave peaks (also known as proximal vertices), multiple wave valleys (also known as distal vertices), and wave rods connecting adjacent wave peaks and wave valleys. Among them, one vertex (proximal vertex or distal vertex) and the two wave rods connected to this vertex form a wave.

[0036] The "coating" in the present invention can isolate liquid to a certain extent, and it can be made of polymer materials with good biocompatibility such as polytetrafluoroethylene (abbreviated as PTFE), polyethylene terephthalate (abbreviated as PET), etc.

[0037] Embodiment 1

[0038] Please refer to Figure 1, the lumen stent 100 of this embodiment includes a main stent 10 and a mesh cover 4 connected to the main stent 10. The main stent 10 is integrally in a hollow tubular structure with openings at both ends. A groove 5 is formed by radially inward depression on its side surface. The mesh cover 4 is connected to the groove 5, and at least a part of the mesh cover 4 and the bottom 51 of the groove 5 form a radial interval in the radial direction of the lumen stent 100, and this radial interval communicates with the inner cavity of the main stent 10. The lumen stent 100 of the present invention is applicable to various blood vessels. In this embodiment of the present invention, the aortic arch is taken as the target implanted lumen for illustration. The aortic arch has a large curvature side (i.e., the side with a smaller degree of curvature and a larger radius of curvature) and a small curvature side (i.e., the side with a larger degree of curvature and a smaller radius of curvature). When the lumen stent 100 is implanted into the aortic arch, the mesh cover 4 faces the large curvature side and is opposite to the branch blood vessels. The externally connected bridging stent connects the branch blood vessels and passes through the mesh holes of the mesh cover 4 and communicates with the main stent 10 through the groove 5.

[0039] The main stent 10 includes a main support part and a main film covering 31. The main film covering 31 can be arranged on the inner surface and / or the outer surface of the main support part, or the main film covering 31 can be arranged on a part of the inner surface of the main support part and a part of the outer surface of the main support part.

[0040] Please refer to Figure 1 , the main stent 10 can be axially divided into a proximal section 2, a distal section 1, and an intermediate section 7 located between the proximal section 2 and the distal section 1; the proximal section 2 includes a tubular proximal support part and a proximal main film covering. The proximal main film covering can be covered on the inner side and / or the outer side of the proximal support part by methods such as sewing, bonding, and hot melting. The proximal support part includes a plurality of main wave circles arranged at axial intervals; the distal section 1 includes a tubular distal support part and a distal main film covering. The distal main film covering can also be covered on the inner side and / or the outer side of the distal support part by methods such as sewing, bonding, and hot melting. The distal support part includes a plurality of main wave circles arranged at axial intervals.

[0041] The intermediate section 7 includes an intermediate unit and at least one mesh cover 4. The intermediate unit includes an intermediate main film covering 3 and an intermediate support part (which can be omitted in other embodiments). The inner cavity enclosed by the intermediate main film covering 3 communicates with the inner cavity enclosed by the proximal main film covering and the inner cavity enclosed by the distal main film covering; wherein a groove 5 is formed by radially inward depression on the side surface of the intermediate unit. A part of the intermediate main film covering 3 serves as the film covering of the bottom 51 of the groove 5, and a bottom support member can also be arranged on the bottom 51 of the groove 5. The bottom support member can include one or more of a corrugated unit, a mesh structure, etc. In other embodiments, the bottom support member can be omitted. The two sides of the mesh cover 4 in the radial direction are fixedly connected to the intermediate main film covering 3 by means such as sewing, bonding, and hot melting, and at least a part of the mesh cover 4 forms a radial interval (or called gap, void, cavity) with the outer surface of the intermediate unit 51.

[0042] The branch stent 6 can be arranged in the proximal segment 2 and / or the distal segment 1. The inner cavity of the branch stent 6 is communicated with the inner cavity of the main stent 10, and is communicated with the radial interval formed between the bottom 51 of the groove 5 and the mesh cover 4. Among them, multiple branch stents 6 can be arranged. For example, a branch stent 10 is arranged at a proximal position close to the groove 5 and a distal position close to the groove 5 respectively.

[0043] Please refer to Figure 2 and Figure 4 , in one embodiment, the mesh cover 4 is in an arc structure in the circumferential direction of the lumen stent 100 and is formed into a mesh structure by braided wires. For example, the mesh cover 4 can be integrally woven by the braided wires or can be woven separately and then spliced. In other embodiments, the mesh cover 4 can also be made by cutting. The central angle corresponding to the projection of the mesh cover 4 on the radial plane of the lumen stent 100 can be less than or equal to 180 degrees, so that the mesh cover 4 has good radial support force and ensures that there is enough space in the middle unit for blood flow to pass through.

[0044] In this embodiment, the projection of the edge of the groove 5 on the plane passing through its two radial side edges is substantially rectangular (it can also be said that the opening of the groove 5 is substantially rectangular); the groove 5 includes a first edge, a second edge, a third edge and a fourth edge, and the four edges enclose the opening of the groove 5. Among them, the first edge and the second edge are oppositely arranged in the radial direction of the lumen stent 100, and the extending directions of the first edge and the second edge are the same as the length extending direction of the lumen stent 100, and the third edge and the fourth edge are oppositely arranged in the axial direction of the lumen stent 100. It can be understood that in other embodiments, the opening of the groove 5 can also be any other suitable shape. For example, the first edge and the second edge can form a certain angle with the axis of the lumen stent 100, so that the opening of the groove 5 is substantially trapezoidal, or the first edge and the second edge can be arc-shaped, so that the opening of the groove 5 is similar to an ellipse). The present invention does not limit the specific shape of the groove 5. In this embodiment, please refer to Figure 2 and Figure 3 , along the circumferential direction of the lumen stent 100, the mesh cover 4 includes a first mesh area 41 and a second mesh area 42 connected to each other. Both the first mesh area 41 and the second mesh area 42 can be radially contracted under the action of an external force and can self-expand or be mechanically expanded (for example, expanded by balloon dilation) after the external force is withdrawn to restore to the initial shape and maintain the initial shape; preferably, along the circumferential direction of the lumen stent 100, the mesh cover 4 includes a first mesh area 41 and two second mesh areas 42 respectively connected to both sides of the first mesh area 41.

[0045] Please refer to Figure 7, the first mesh region 41 includes a plurality of first-direction support wires 481 arranged at intervals and a plurality of second-direction support wires 482 arranged at intervals. The first-direction support wires 481 extend substantially along the first direction, and the second-direction support wires 482 extend substantially along the second direction. The first-direction support wires 481 and the second-direction support wires 482 overlap (or intersect) with each other to form multiple columns of mesh holes and multiple columns of intersection units 48. Each column of mesh holes includes a plurality of mesh holes arranged substantially along the axial direction. Each column of intersection units 48 includes a plurality of intersection units 48 arranged at intervals substantially along the axial direction. The mesh holes are generally diamond-shaped, and can also be other shapes such as square or rectangular; four intersection units 48 are correspondingly arranged at the four corner positions of the mesh hole. Each intersection unit 48 includes an intersection point formed by the overlapping of the first-direction support wire 481 and the second-direction support wire 482. At this intersection point, the first-direction support wire 481 and the second-direction support wire 482 can move relative to each other. Among them, in some intersection units 48, the first-direction support wire 481 is located outside the second-direction support wire 482, and in some intersection units 48, the first-direction support wire 481 is located inside the second-direction support wire 482. In other embodiments, all the first-direction support wires 481 in the first mesh region 41 are located outside the second-direction support wires 482, or all the first-direction support wires 481 are located inside the second-direction support wires 482. Since the first-direction support wire 481 and the second-direction support wire 482 at the intersection point of the intersection unit 48 overlap and can move relative to each other, the mesh holes in the first mesh region 41 can be deformed and enlarged under an external force to facilitate the guide wire and the bridging stent to pass through the mesh holes. When the external force is withdrawn, the mesh holes can retract to play a certain supporting and limiting role for the bridging stent, reducing the occurrence of the bridging stent swinging with the blood flow or the heartbeat, so as to ensure the stability of the branch blood supply.

[0046] Please refer to Figure 6, the second mesh region 42 includes at least one column of hooking units 47, each column of hooking units 47 includes a plurality of hooking units 47 arranged axially in sequence, and each hooking unit 47 includes a first hooking member 471 and a second hooking member 472. Among them, both the first hooking member 471 and the second hooking member 472 are part of the support wire; the first hooking member 471 includes a wave bulging towards the distal direction, that is, it includes a wave valley 4711 (also known as the distal vertex) and two first wave rods 4712 connected to the wave valley 4711; the second hooking member 472 includes a wave bulging towards the proximal direction, that is, it includes a wave peak 4721 (also known as the proximal vertex) and two second wave rods 4722 connected to the wave peak 4721. In this embodiment, the first hooking member 471 and the second hooking member 472 of each hooking unit 47 are substantially hooked to each other along the axis. It should be noted that the "substantially along the axis" here means that the connection line between the distal vertex of the first hooking member 471 and the proximal vertex of the second hooking member 472 is parallel to the axis of the mesh cover 4, or the included angle between this connection line and the axis of the mesh cover 4 is less than or equal to 45°.

[0047] The hooking state of the first hooking member 471 and the second hooking member 472 includes at least a first hooking state and a second hooking state. The first hooking state is: in the natural deployment state, the first hooking member 471 and the second hooking member 472 are hooked to each other, and there is a hooking gap L0 (that is, separated by a certain distance) between the wave valley 4711 of the first hooking member 471 and the wave peak 4721 of the second hooking member 472. Therefore, the first hooking member 471 can move towards the proximal or distal direction, and the second hooking member 472 can also move towards the proximal or distal direction, but the hooking gap L0 limits the distance of the first hooking member 471 moving towards the proximal direction and the second hooking member 472 moving towards the distal direction; it can be understood that the hooking gap can also form a mesh structure for the bridging stent to use as an access mesh when necessary; the second hooking state is: in the natural deployment state, the first hooking member 471 and the second hooking member 472 are hooked to each other, and an abutment is formed at the wave valley 4711 of the first hooking member 471 and the wave peak 4721 of the second hooking member 472 (the hooking gap L0 is 0). Therefore, there is a constraint on the first hooking member 471 moving towards the proximal direction and the second hooking member 472 moving towards the distal direction.

[0048] Please refer to Figure 2 , the axial direction of the mesh cover 4 from the proximal end to the distal end includes a proximal cover 43 and a distal cover 45. Please also refer to Figure 6 、 Figure 9 and Figure 11, when the first hook member 471 and the second hook member 472 are hooked to form the hook unit 47, the hook unit 47 in the proximal end cap 43 is different from the hook unit 47 in the distal end cap 45. In the proximal end cap 43, the first wave bar 4712 on the side close to the radial edge of the mesh cover 4 in the same hook unit 47 crosses over the second wave bar 4722; and / or, in the distal end cap 45, the second wave bar 4722 on the side close to the radial edge of the mesh cover 4 in the same hook unit 47 crosses over the first wave bar 4712. Here, please refer to Figure 2 the deployment structure in, the upper side refers to the side that is further away from the inner cavity of the main body bracket 10, and can also be understood as the outer side of the arched structure of the mesh cover 4; the reason for such a setting is that the bridging bracket usually enters the groove 5 from the mesh hole on the proximal end 43 and then connects to the branch bracket 6 located in the proximal segment 2. Since in the proximal end cap 43, the first wave bar 4712 on the side close to the radial edge of the mesh cover 4 in the same hook unit 47 crosses over the second wave bar 4722, therefore, the first wave bar 4712 can be separated from the second wave bar 4722 located below it in the radial direction of the lumen bracket 100, so as to have better upward deformation ability and space, so that the mesh holes on the radial side of the proximal end cap 43 can undergo large deformation under the action of external force to expand large enough to facilitate the guide wire and the bridging bracket to pass through the mesh hole. When the external force is withdrawn, the mesh hole can retract to play a certain supporting and limiting role for the bridging bracket, reducing the situation that the bridging bracket swings with the blood or heart pulsation to ensure the stability of the branch blood supply. On the contrary, if the second wave bar 4722 at this position crosses over the first wave bar 4712, the first wave bar 4712 is restricted by the second wave bar 4722 above it and it is difficult to be further lifted, so it will cause the first hook member 471 and the second hook member 472 to be knotted together at the hooked position, which is not conducive to the expansion and deformation of the mesh opening, thus affecting the entry of the bridging bracket.

[0049] In the distal end cap 45, the second wave bar 4722 on the side close to the radial edge of the mesh cover 4 in the same hook unit 47 crosses over the first wave bar 4712; the principle and effect applied by this structure are similar to those of the proximal end cap 43, and will not be elaborated here.

[0050] It can be understood that to achieve the easy expansion and deformation of the mesh holes on the radial side of the mesh cover 4, it is not required that the structure of the first mesh area 41 is the same as that described in this embodiment. In other embodiments, the structure of the first mesh area 41 can be similar to the structure of the second mesh area 42 in this embodiment, including at least one row of hook units 47, or the structure of the first mesh area 41 can also be any other suitable structure.

[0051] Please refer to Figure 2 、 Figure 4, Further, in one embodiment, the first wave rod 4712 and the second wave rod 4722 on one side of the hooking unit 47 close to the radial edge of the mesh cover 4 form an axial interval, and the maximum axial lengths of the axial intervals formed by the hooking units 47 in the same column may be equal or unequal. Exemplarily, in this embodiment, the maximum axial lengths of the axial intervals formed by the hooking units 47 in the same column are unequal. For example, the multiple axial intervals formed between the multiple hooking units 47 include end intervals and intermediate intervals. The end intervals are closer to the axial ends of the mesh cover 4 than the intermediate intervals, and the maximum axial length ( Figure 2 shown as L1) of at least one end interval is greater than the maximum axial length ( Figure 2 shown as L2) of the intermediate interval. For example, the maximum axial length of the end interval near the proximal end of the mesh cover 4 is greater than the maximum axial length of the intermediate interval, and the maximum axial length of the end interval near the distal end of the mesh cover 4 is greater than the maximum axial length of the intermediate interval. In other embodiments, if the branch bracket 6 is only provided near one axial end of the mesh cover 4, it is only necessary that the maximum axial length of the end interval near this axial end is greater than the maximum axial length of the intermediate interval. The axial ends of the mesh cover 4 are opposite to the edges of the branch bracket 6, so that the probability of the bridging bracket entering the branch bracket 6 from the mesh holes near the axial ends of the mesh cover 4 is relatively high. By setting the maximum axial length L1 of the end interval to be greater than the maximum axial length L2 of the intermediate interval, the size of the side mesh holes of the mesh cover 4 near its axial ends is further increased, facilitating the entry of the guide wire and the bridging bracket. It can be understood that to make the mesh holes on the radial sides of the mesh cover 4 easy to expand and deform, it is not necessarily required that the maximum axial length L1 of the end interval is greater than the maximum axial length L2 of the intermediate interval. The maximum axial length L1 of the end interval can be approximately equal to the maximum axial length L2 of the intermediate interval. As long as in the proximal end cap 43, the first wave rod 4712 on one side of the hooking unit 47 close to the radial edge of the mesh cover 4 straddles above the second wave rod 4722; and / or, in the distal end cap 45, the second wave rod 4722 on one side of the hooking unit 47 close to the radial edge of the mesh cover 4 straddles above the first wave rod 4712, the effect of easy expansion and deformation of the mesh holes on the radial sides of the mesh cover 4 can be achieved.

[0052] Further, the mesh cover 4 of this embodiment further includes at least one column of side connectors 46 provided on the radial sides of the mesh cover 4. Each column of side connectors 46 includes at least one side connector 46, and the mesh cover 4 is connected to the main body bracket 10 through the side connectors 46. Exemplarily, the side connector 46 includes a connection hole 46a, and the mesh cover 4 and the main body bracket 10 can be sutured through the connection hole 46a. In other embodiments, they can also be fixedly connected by bonding or other means.

[0053] Refer to Figure 2, the side connectors 46 are all connected to the hooking units 47. For example, the side connectors 46 are respectively connected to two axially adjacent hooking units 47. Among the adjacent hooking units 47, in the hooking unit 47 closer to the proximal end of the lumen stent 100, after the second wave rod 4722 in the second hooking member 472 continues to extend and bends to form a connection hole, it is then connected to the first wave rod 4712 of the first hooking member 471 of the hooking unit 47 closer to the distal end of the lumen stent 100. Both the first wave rod 4712 and the second wave rod 4722 are wave rods closer to the radial side of the mesh cover 4 in the hooking unit 47. The connection hole can be used for fixedly connecting to the film or the stent body by suturing. The connection hole not only facilitates the suturing operation but also plays a limiting role to prevent relative slippage between the suture and the mesh cover 4. In this embodiment, the connection hole is a closed hole, so it is beneficial to further improve the limiting effect. In other embodiments, the connection hole can be an open hole.

[0054] Exemplarily, referring to Figure 4 , Figure 5 , in this embodiment, the side connector 46 is generally triangular, including two waists 461 and a base 462 connecting the two waists 461. Its base 462 extends substantially axially and is connected to the radial edge of the groove 5. One waist 461 is formed by extending a first wave rod 4712 of the first hooking member 471, and the other waist 461 is formed by extending a second wave rod 4722 of the second hooking member 472 adjacent to and not hooking with the first hooking member 471. The intersection of the two waists 461 of the side connector 46 forms a vertex. At this vertex position, the two waists 461 overlap and are fixed to each other. For example, they are fixedly connected by suturing. This connection method can make the radial sides of the mesh cover 4 have better stability, thus ensuring the overall supporting force after the mesh cover 4 is connected. In another embodiment, when the side connector 46 is connected to the radial two-side edges of the groove 5 by suturing or bonding, the base 462 is connected to the edge of the groove 5, and the intersection of the two waists 461 can relatively slide, which is beneficial to further increase the expansion size of the side mesh holes of the mesh cover 4.

[0055] In other embodiments, the side connecting member 46 may be of other shapes. For example, the side connecting member 46 includes a wave that bulges towards the radial side of the mesh cover 4, and this wave shares a wave rod with the first hook member 471 and also shares a wave rod with the second hook member 472 respectively. A side connecting member 46 and the connected first hook member 471 and second hook member 472 together enclose a mesh hole. The side connecting member 46 can be fixedly connected to the main body bracket 10 by methods such as stitching and bonding. Since the side connecting member 46 has a vertex protruding towards the radial side edge of the mesh cover 4, by fixedly connecting at the position of this vertex with the edge of the groove 5, the connection can be made more firm. In other embodiments, the side connecting member 46 can also be in other suitable shapes such as a water droplet shape, a circular shape, an oval shape, etc.

[0056] Please refer to Figure 2 , in this embodiment, the mesh cover 4 further includes a side end connecting member 42a provided at the axial end of the mesh cover 4. For example, side end connecting members 42a are provided at both the distal end and the proximal end of the mesh cover 4, and this side end connecting member 42a is used to connect with the edge of the groove 5. The above-mentioned side connecting member 46 is arranged between the side end connecting member 42a at the distal end of the mesh cover 4 and the side end connecting member 42a at the proximal end of the mesh cover 4, and the side end connecting member 42a and the side connecting member 46 are arranged at intervals. By providing the side end connecting member 42a, the mesh cover 4 can better follow the bending deformation of the main body bracket 10 to better fit the blood vessel and provide support for the groove 5. In addition, in this embodiment, the side end connecting member 42a includes an edge wave angle 421 that bulges towards the axial end of the mesh cover 4, and it is connected to the main body bracket 10 through this edge wave angle 421. For example, it can be fixedly connected by stitching, bonding and other methods. Since the vertex 4211 of this edge wave angle 421 itself does not form a closed connection hole structure, it can not only reduce the sheath size at the corner of the mesh cover 4, but also enable the edge wave angle 421 and the adjacent hook unit 47 to form a mesh hole in the shape of a polygon with a relatively large size. The size of this polygon-shaped mesh hole is relatively large, so it is beneficial for the guide wire and the bridging stent to enter through this mesh hole. In other embodiments, the side end connecting member 42a can be omitted.

[0057] When the maximum axial length of at least one end interval is greater than the maximum axial length of the middle interval, since the side end connecting member 42a is connected to the hook unit 47, therefore, the maximum interval distance between the side end connecting member 42a and the adjacent side connecting member 46 is also greater than the maximum interval distance between two adjacent side connecting members 46. This is beneficial for increasing the size of the side mesh hole of the mesh cover 4 near its axial end to facilitate the entry of the guide wire and the bridging stent. In other embodiments, the maximum interval distance between the side end connecting member 42a and the adjacent side connecting member 46 can also be approximately equal to the maximum interval distance between two adjacent side connecting members 46.

[0058] Example 2

[0059] The lumen stent 100 of this embodiment is substantially the same as that of Example 1, except that the side end connector 42a is connected to the side connector 46.

[0060] Referring to Figure 3 , a plurality of side connectors 46 include two first side connectors 46a and a second side connector 46b located between the two first side connectors 46a. The second side connector 46b is respectively connected to a first hook member 471 and a second hook member 472. The first side connectors 46a are respectively connected to the side end connector 42a and the hook unit 47 in the axial direction. Exemplarily, the first side connector 46a near the proximal end of the mesh cover 4 is respectively connected to the side end connector 42a located at the proximal end of the mesh cover 4 and the first hook member 471 in the axial direction. For example, in the first hook member 471 of the hook unit 47 at the proximal end, the first wave rod 4712 near the radial edge of the mesh cover 4 continues to extend in the direction close to the proximal end of the mesh cover 4, and then bends reversely to form the first side connector 46a and is connected to the side end connector 42a located at the proximal end of the mesh cover 4; the first side connector 46a near the distal end of the mesh cover 4 is respectively connected to the side end connector 42a located at the distal end of the mesh cover 4 and the second hook member 472 in the axial direction. For example, in the second hook member 472 of the hook unit 47 at the distal end, the second wave rod 4722 near the radial edge of the mesh cover 4 continues to extend in the direction close to the distal end of the mesh cover 4, and then bends reversely to form the first side connector 46a and is connected to the side end connector 42a located at the distal end of the mesh cover 4. In this embodiment, the side end connector 42a includes an edge wave angle 421 that bulges toward the axial end of the mesh cover 4. The edge wave angle 421 and the adjacent hook unit 47 form a polygonal mesh hole with a relatively large size, so it is beneficial for the guide wire and the bridging stent to enter through this mesh hole. Also, since the side end connector 42a of this embodiment is connected to the first side connector 46a, and there is a distance between the first side connector 46a and the vertex 4211 of the edge wave angle 421 of the end connector, not only will the sheath-retracting size of the corners of the mesh cover 4 not be increased, but it can also ensure that a relatively large mesh hole is formed between the side end connector 42a and the adjacent hook unit 47, and it can also prevent the edge wave angle 421 fixed by suturing from shifting relative to the groove 5 and piercing out to damage biological tissues when the mesh cover 4 is compressed or deformed.

[0061] In this embodiment, when the maximum axial length of at least one end interval is greater than the maximum axial length of the middle interval, the maximum spacing distance between the first side connector 46a and the adjacent second side connector 46b is also greater than the maximum spacing distance between two adjacent second side connectors 46b, which is conducive to increasing the size of the side mesh holes of the mesh cover 4 close to its axial end, facilitating the entry of the guide wire and the bridging stent. In other embodiments, the maximum spacing distance between the first side connector 46a and the adjacent second side connector 46b can also be roughly equal to the maximum spacing distance between two adjacent second side connectors 46b.

[0062] Embodiment 3

[0063] In this example, see Figure 4 and Figure 6 The structure of the luminal support 100 is substantially the same as that of the first and second embodiments, except that the trough 4711 of the first hook 471 and the crest 4721 of the second hook 472 of the present embodiment both include a cross bar 473, and the two first wave bars 4712 of the first hook 471 are connected by the cross bar 473, and the two second wave bars 4722 of the second hook 472 are connected by the cross bar 473. The cross bar 473 forms a transitional connection distance at one end between the two interconnected wave bars, so that the formed hooking gap also has a certain distance in the lateral direction, further expanding the size of the mesh formed by the hooking gap, so that the hooking gap is more suitable as a mesh for the bridging stent to enter; another purpose is that in the absence of the cross bar 473, the two wave bars are directly connected, and the wave angles of the crest 4721 or the trough 4711 formed by the connection are relatively sharp. When the mesh cover 4 bends with the tubular stent, it will warp on the curved surface. Under long-term use, the wave angles will scratch the inner wall of the blood vessel and cause unnecessary damage.

[0064] The angle formed by the cross bar 473 and the first wave bar 4712 and / or the second wave bar 4722 is an obtuse angle, so as to further expand the size of the mesh formed by the hooking gap. The length of the cross bar 473 should be appropriate, ranging from 1 mm to 4 mm, which can not only expand the hooking gap and protect the inner wall of the blood vessel, but also avoid the problem of excessive radial compression size of the mesh cover 4 caused by the cross bar 473 being too long.

[0065] Preferably, see Figure 9 and Figure 10 The crossbar 473 is a straight bar, which can directly and effectively avoid scratching the blood vessel wall. When the straight bar is used, an arc transition is used when the straight bar is connected to the two wave bars.

[0066] Preferably, see Figure 4 and Figure 6, the crossbar 473 is an arc-shaped rod. An arc-shaped rod with a relatively small degree of bending should be selected. The preferred arc range can be 60° to 140°.

[0067] Embodiment 4

[0068] Please refer to Figure 3 、 Figure 4 and Figure 8 , on the basis of any one of Embodiments 1 to 3 in this embodiment, the mesh cover 4 of this embodiment further includes a bending portion 422. The bending portion 422 includes a first rod 4222 and a second rod 4223 that are connected to each other. A bending angle 4221 is formed between the first rod 4222 and the second rod 4223. The first rod 4222 extends from the bending angle 4221 toward an axial end of the mesh cover 4, and the second rod 4223 extends from the bending angle 4221 toward the other axial end of the mesh cover 4. Since the first rod 4222 and the second rod 4223 of the bending portion 422 extend toward opposite axial ends of the mesh cover 4 respectively, when the mesh cover 4 is radially squeezed by the blood vessel wall and bends conforming to the blood vessel shape, the first rod 4222 and the second rod 4223 forming the bending angle 4221 can move relative to each other, so that the bending portion 422 can bulge toward a direction away from the groove 5, and the mesh cover 4 is more likely to form an arch in this area, avoiding compressing the space in the groove 5 and facilitating the guide wire and the bridging stent to enter the groove 5. Especially when the bending angle 4221 formed by the bending portion 422 is an obtuse angle, the relative movement space between the first rod 4222 and the second rod 4223 increases, and it can deform more flexibly. Moreover, when the bending portion 422 bulges toward a direction away from the groove 5, it can avoid forming a sharp structure that damages the blood vessel wall.

[0069] In this embodiment, the bending angle 4221 of the bending portion 422 is located at a position close to the axial end of the mesh cover 4. For example, the bending angle 4221 is located between the axial end of the mesh cover 4 and the hooking unit 47 closest to the axial end. When a branch stent 6 is provided near the axial end of the mesh cover 4, the bending portion 422 can form an arch structure that bulges toward a direction away from the groove 5 after the lumen stent 100 is implanted, providing a larger groove 5 space for the branch opening of the branch stent 6 toward the groove 5 and facilitating the guide wire and the bridging stent to enter the branch stent 6.

[0070] Furthermore, the bending angle 4221 of the bending portion 422 bends toward the axial end of the mesh cover 4 that it is close to. Such a setting can make the mesh hole sizes of its accessories more uniform. In other embodiments, the bending angle 4221 of the bending portion 422 bends toward the axial end of the mesh cover 4 that it is away from.

[0071] The first rod 4222 of the bent portion 422 extends from the bent angle 4221 towards one axial end of the net cover 4 that is closer. While the second rod 4223 of the bent portion 422 extends from the bent angle 4221 towards the other axial end of the net cover 4 that is closer, the first rod 4222 of the bent portion 422 extends towards one radial edge of the net cover 4 that is closer, and the second rod 4223 extends towards the other radial edge of the net cover 4 that is closer. The advantage of such a setting is that both the first rod 4222 and the second rod 4223 extend obliquely relative to the axial and radial directions of the net cover 4, enabling the bent portion 422 to better conform to the radial deformation of the net cover 4 and at the same time better conform to the axial bending deformation of the net cover 4.

[0072] One end of the first rod 4222 of the bent portion 422 that is away from the bent angle 4221 is connected to the edge of the groove 5. Such a setting enables the edge of the groove 5 to provide a certain supporting force for the first rod 4222. When the groove 5 is subjected to a radial force, the end of the first rod 4222 that is away from the bent angle 4221 can better transmit the radial force, enabling the first rod 4222 to more sensitively deform following the groove 5.

[0073] Exemplarily, in this embodiment, referring to Figure 4 and Figure 8 , the edge wave angle 421 includes a vertex 4211 and two third wave rods 4212 connected to the vertex. The first rod 4222 serves as one of the third wave rods 4212 of the edge wave angle 421. The other third wave rod 4212 of the edge wave angle 421 extends from its vertex 4211 towards the axial end of the net cover 4 that is away from the vertex 4211. The two third wave rods 4212 form an angle at the vertex 4211 of the edge wave angle 421. The size of the angle formed at the vertex 4211 of the edge wave angle 421 should be appropriate. When the angle is too large, on the one hand, it will cause the sizes of the mesh holes on both sides of the first rod 4222 to be uneven. On the other hand, it may cause the first rod 4222 to extend approximately along the radial direction, resulting in difficulty in sheathing the lumen stent 100. When the angle is too small, it will also cause the sizes of the mesh holes on both sides of the first rod 4222 to be uneven, and it may cause the vertex 4211 of the edge wave angle 421 to be prone to piercing and injuring blood vessels. Therefore, the angle can be an acute angle. For example, the range of the angle can be 30° to 70°. Within this range, not only can the sizes of the mesh holes on both sides of the first rod 4222 be relatively uniform, but also the lumen stent 100 can be easily sheathed and has good safety. The edge wave angle 421 is connected to the corner 52 of the groove 5 (refer to Figure 14 ). For example, the vertex 4211 of the edge wave angle 421 is connected to the corner of the groove 5. Therefore, it can play a role in supporting the corner of the groove 5 to a certain extent, enabling the corner of the groove 5 to fully expand and better maintaining the shape of the opening of the groove 5.

[0074] The second rod 4223 of the bent portion 422 passes through the first mesh region 41 and is connected to the vertex of the first hook member 471 or the second hook member 472 on the opposite side. For example, a part of the second rod 4223 serves as the support wire of the first mesh region 41 and a part serves as the wave rod of the hook unit. Such a setting enables the vertex of the first hook member 471 or the second hook member 472 to provide a certain supporting force for the second rod 4223. When the mesh cover 4 of the groove 5 is subjected to a radial force, the end of the second rod 4223 away from the bending angle 4221 can better transmit the radial force, enabling the second rod 4223 to more sensitively deform following the mesh cover 4. In addition, since the second rod 4223 passes through the first mesh region 41 to reach the opposite side, the first rod 4222 and the second rod 4223 can respectively transmit the extrusion pressures received on both radial sides of the mesh cover 4, thereby adaptively deforming and well maintaining the space within the groove 5.

[0075] In this embodiment, the mesh cover 4 includes four side end connectors 42a and four bent portions 422. Among them, two side end connectors 42a and two bent portions 422 are located at the proximal end of the mesh cover 4. The two side end connectors 42a are respectively connected to the two corners at the proximal end of the groove 5, and the two bent portions 422 are respectively connected to the two side end connectors 42a; two side end connectors 42a and two bent portions 422 are located at the distal end of the mesh cover 4. The two side end connectors 42a are respectively connected to the two corners at the distal end of the groove 5, and the two bent portions 422 are respectively connected to the two side end connectors 42a. In other embodiments, the number of side end connectors 42a and bent portions can be selected according to the actual application scenario.

[0076] Embodiment Five

[0077] Referring to Figure 3 、 Figure 4 Based on any one of Embodiments One to Four, this embodiment includes a side end connector 42a and an intermediate end connector 41a connected to the main body bracket 10. The side end connector 42a is closer to the radial edge of the mesh cover 4 than the intermediate end connector 41a. Compared with the scheme where the intermediate end connector 41a is not connected to the main body bracket, since the intermediate end connector 41a is connected to the main body bracket 10, when the main body bracket 10 bends, it can better drive the mesh cover 4 to bend and deform conforming to the shape of the blood vessel. Moreover, the intermediate end connector 41a connected to the main body bracket 10 can also provide better support force for the axial end of the groove 5, avoiding the formation of an axial gap between the main body bracket 10 and the intermediate end connector 41a when the lumen bracket 10 bends, and further avoiding the inner wall of the blood vessel with a relatively narrow true lumen from squeezing the gap and entering the internal space of the groove 5, thereby blocking the guide wire and the bridging stent from entering the branch stent 6.

[0078] Further, the middle end connector 41a located at the proximal end of the mesh cover 4 is closer to the proximal end of the lumen stent 100 than the side end connector 42a located at the proximal end of the mesh cover 4, and / or, the middle end connector 41a located at the distal end of the mesh cover 4 is closer to the distal end of the lumen stent 100 than the side end connector 42a located at the distal end of the mesh cover 4. Compared with the scheme where the axial ends of the side end connector 42a and the middle end connector 41a are flush, the scheme of this embodiment makes the mesh cover 4 at the position of the middle end connector 41a have a larger axial dimension, so that the mesh cover 4 can form a better arched structure after following the bending of the main body stent 10, which can effectively prevent the axial ends of the mesh cover 4 from forming an approximate plane when the main body stent 10 bends, better maintain the internal space of the groove 5, facilitate the guide wire and the bridging stent to enter the groove, and avoid excessive extrusion of the bridging stent after the bridging stent is implanted.

[0079] Exemplarily, referring to Figure 3 , the middle end connector 41a includes a middle wave angle 411, the side end connector 42a includes an edge wave angle 421, and the vertex 4112 of the middle wave angle 411 located at the proximal end of the mesh cover 4 is closer to the proximal end of the lumen stent 100 than the vertex 4211 of the edge wave angle 421, and the vertex 4112 of the middle wave angle 411 located at the distal end of the mesh cover 4 is closer to the distal end of the lumen stent 100 than the vertex 4211 of the edge wave angle 421. Compared with the scheme where the vertex 4112 of the middle wave angle 411 is flush with the vertex 4211 of the edge wave angle 421 (which can be referred to Figure 2 ), after the mesh cover 4 bends, due to the longer protruding length of the middle wave angle 411, the stretching degree of the two side edge wave angles 421 in the axial direction is smaller, which can better maintain the shape and size of the mesh holes in the area where the edge wave angle 421 is located, and is beneficial for the guide wire and the bridging stent to pass through these mesh holes. Further, the middle middle wave angle 411 provides sufficient stretching length, which can ensure that the proximal and distal ends of the mesh cover 4 will not be stretched and deformed too much towards the inner cavity direction of the groove 5, can effectively prevent the axial ends of the mesh cover 4 from forming an approximate plane when the main body stent 10 bends, but form a better arched structure, so as to effectively maintain the internal space formed by the mesh cover 4 and the groove 5 at the proximal and distal ends.

[0080] In other embodiments, it can be similar to Figure 2 where the vertex 4112 of the middle wave angle 411 is flush with the vertex 4211 of the edge wave angle 421; or, make the vertex 4211 of the edge wave angle 421 closer to the corresponding axial end of the lumen stent 100 than the vertex 4112 of the middle wave angle 411.

[0081] In one embodiment, specifically as Figure 8 , Figure 11 and Figure 14As shown, the middle wave angle 411 includes two fourth wave rods 4113 connected to its vertex 4112. The vertex 4112 of the middle wave angle 411 is connected to one axial end of the groove 5, and the two fourth wave rods 4113 extend from the vertex 4112 of the middle wave angle 411 towards the other axial end of the groove 5. Further, the vertex 4112 of the middle wave angle 411 is axially opposite to the first mesh area 41, and the two fourth wave rods 4113 extend from the vertex 4112 of the middle wave angle 411 in directions away from each other to be respectively connected to the second mesh areas 42 on both radial sides of the first mesh area 41. For example, they are respectively connected to the hooking units 47 on both radial sides of the mesh cover 4. When the main body bracket 10 bulges and bends towards the opening direction of the groove 5, the middle wave angle 411 can drive the second mesh area 42 connected thereto to bend, and at the same time drive the first mesh area 41 connected to the second mesh area 42 to bend. Also, since the second mesh area 42 includes multiple hooking units 47, when the middle wave angle 411 is connected to the hooking units 47, it can drive the meshes of the second mesh area 42 to fully expand during bending, thus making it more convenient for the guide wire and the bridging stent to penetrate. At the same time, the hooking units 47 can also limit the stretching length of the second mesh area 42 to a certain extent, and further limit the stretching length of the first mesh area 41 connected thereto, avoiding problems such as the compression of the internal space of the groove 5 and the excessive contraction of the meshes of the first mesh area 41 due to the over-stretching of the first mesh area 41. Therefore, the internal space of the groove 5 and the shape of the meshes of the first mesh area 41 can be better maintained, further facilitating the penetration of the guide wire and the bridging stent.

[0082] As Figure 3 , Figure 4 , Figure 6As shown, two fourth wave rods 4113 of the middle wave angle 411 at the proximal end of the mesh cover 4 extend from the vertex 4112 of the middle wave angle 411 in directions away from each other to form the first wave rods 4712 of two hooking units 47 on both radial sides of the mesh cover 4. Two fourth wave rods 4113 of the middle wave angle 411 at the distal end of the mesh cover 4 extend from the vertex 4112 of the middle wave angle 411 in directions away from each other to form the second wave rods 4722 of two hooking units 47 on both radial sides of the mesh cover 4. The two fourth wave rods 4113 of the middle wave angle 411 can be substantially parallel to the first-direction support wires 481 and the second-direction support wires 482 of the first mesh area 41 respectively. In other embodiments, the two fourth wave rods 4113 of the middle wave angle 411 may not be parallel to the first-direction support wires and the second-direction support wires of the first mesh area 41. The angle of the middle wave angle 411 (i.e., the included angle formed by the two fourth wave rods 4113 at the vertex 4112 of the middle wave angle 411) should be appropriate. When the angle of the middle wave angle 411 is too large and it is connected to the main body film 31 by suturing, it may cause the middle wave angle 411 to be prone to slip relative to the main body film 31 in the length direction of its fourth wave rod 4113. When the angle of the middle wave angle 411 is too small, the middle wave angle 411 is likely to pierce the main body film 31 and damage the blood vessel wall. Therefore, the angle range of the middle wave angle 411 can be set to 20° to 80°, which can, on the one hand, stably fix the middle wave angle 411 and, on the other hand, avoid its piercing the main body film 31 and damaging the blood vessel wall.

[0083] Furthermore, referring to Figure 8 , the mesh cover 4 of this embodiment further includes a bending part 422 as described in Embodiment 4, and the two fourth wave rods 4113 of the middle wave angle 411 respectively cross over above the bending part 422. In this embodiment, the two fourth wave rods 4113 of the middle wave angle 411 respectively cross over above the second rods 4223 of the two bending parts 422. In other embodiments, the two fourth wave rods 4113 of the middle wave angle can also cross over above the first rods 4222 of the two bending parts 422, as long as it is ensured that the two fourth wave rods 4113 of the middle wave angle 411 respectively cross over above the bending part 422. The advantage of such a setting is that when the mesh cover 4 is radially compressed or bent, the bending part 422 can bulge in a direction away from the groove 5, thereby lifting the fourth wave rod 4113 that crosses over above it, avoiding the middle wave angle 411 from forming a relatively flat structure due to excessive stretching after the lumen stent 100 is bent. Therefore, the mesh cover 4 can better maintain the internal space of the groove 5 at the axial end and avoid occupying the space near the opening of the branch stent 6.

[0084] When the lumen stent 100 is in the deployed state, the fourth wave rod 4113 of the middle wave angle 411 and the bending part 422 can be in contact with each other; or, as Figure 12 and Figure 13As shown, there is a gap 8 in the radial direction of the lumen stent 100 between the fourth wave rod 4113 of the middle wave angle 411 and the bent portion 422; whether in contact with each other or forming a gap 8, the middle wave angle 411 can move relative to the bent portion 422, so that whether the mesh cover 4 is in a bent or straight state, it has better deformation ability and compliance, and can better maintain the internal space formed between the mesh cover 4 and the groove 5. When there is a gap 8 in the radial direction of the lumen stent 100 between the fourth wave rod 4113 of the middle wave angle 411 and the bent portion 422, the formed gap 8 can enable the bent portion 422 to have a larger movement space, which is beneficial for the mesh cover 4 to form an arched structure better when bending in the direction away from the groove 5, and is more conducive to the guide wire and the bridging stent entering the branch stent 6.

[0085] In one embodiment, please refer to Figure 12 and Figure 13 , the fourth wave rod 4113 of the middle wave angle 411 can be an arc rod 4111, and the arc rod 4111 is an upwardly convex arched bending structure. Here, the upward convexity is specifically a convexity along the radial direction of the lumen stent 100 away from the central axis of the lumen stent 100. The convex arched bending structure can be more conducive to forming a gap 8 between the middle wave angle 411 and the bent portion 422. Further, the arc rod 4111 of the arched bending structure can enable the axial end of the mesh cover 4 to conform to the arc rod 4111 to form an arched structure after the mesh cover 4 axially bends as the main body stent 10 bends, providing stronger support performance, so that the internal space at the axial end position of the groove 5 can be better maintained and the internal space is prevented from being excessively squeezed.

[0086] Please refer to Figure 14 and Figure 15, the branch stent 6 of the main body stent 10 located in the proximal segment 2 is a double-branch orifice stent 61. The double-branch orifice stent 61 is formed by two single-branch orifice stents 62 connected to the inner wall of the proximal segment 2 of the lumen stent 100 side by side through suture or bonding. The two single-branch orifice stents 62 are usually set as approximately circular orifice openings, and a gap 612 will be formed between the two orifice openings. Thus, when the double-branch orifice stent 61 is sutured to the proximal main body membrane of the lumen stent 100 at the proximal edge of the groove 5, the gap 612 will form a blank segment of the proximal main body membrane. When the mesh cover 4 is installed in the groove 5, the intermediate end connector 41a in the middle of the mesh cover 4 is connected to the proximal main body membrane at the gap 612. For example, the vertex 4112 of the intermediate wave angle 411 extends to the gap 612, making the vertex 4112 of the intermediate wave angle 411 closer to the proximal end of the lumen stent 100 than the proximal edge of the groove 4, and the intermediate wave angle 411 is connected to the proximal main body membrane at the gap 612. The advantage of this setting is that the orifice opening 611 of the double-branch orifice stent 61 can play a certain supporting role for the intermediate wave angle 411, and can prevent the intermediate wave angle 411 from piercing the main body membrane 31.

[0087] It can be understood that the above-mentioned intermediate end connector 41a can be connected to the inner wall or the outer wall of the main body membrane 31. For example, the vertex 4112 of the intermediate wave angle 411 and a part of the fourth wave rod 4113 extend to the inner wall of the main body membrane 31 at the gap 612, that is, the main body membrane 31 at the gap 612 covers the outside of the vertex 4112 of the intermediate wave angle 411 and a part of the fourth wave rod 4113, and the vertex 4112 of the intermediate wave angle 411 and a part of the fourth wave rod 4113 are connected to the inner wall of the main body membrane 31 by suture; or, the main body membrane 31 at the gap 612 covers the inside of the vertex 4112 of the intermediate wave angle 411 and a part of the fourth wave rod 4113, and the vertex 4112 of the intermediate wave angle 411 and a part of the fourth wave rod 4113 are connected to the outer wall of the main body membrane 31 by suture. When the intermediate end connector 41a is connected to the inner wall of the main body membrane 31, it can prevent the intermediate end connector 41a from tilting outwards and damaging the inner wall of the blood vessel when the lumen stent 100 deforms, which is beneficial to improving the safety performance.

[0088] In other embodiments, the branch stent 6 of the main body stent 10 located in the proximal segment 2 may not be the double-branch orifice stent 61, while the branch stent 6 of the distal segment 2 is the double-branch orifice stent 61. In this way, the intermediate wave angle 411 at the distal end of the mesh cover 4 can be connected to the main body stent 10 with reference to the above connection method. In other embodiments, the connection position and connection method of the intermediate wave angle 411 and the main body stent 10 are not limited to this, and appropriate connection positions and connection methods can be selected according to actual needs.

[0089] Further, a support member is also provided at the edge of the branch opening 611 of the double-branch opening stent 61 to better maintain the shape of the branch opening 611. At least a part of the support member is connected to the main body film 31 and is located on both sides of the intermediate end connector 41a to better provide support for the intermediate wave angle 411.

[0090] The above specific embodiments are only part of the embodiments of the present invention and do not limit the present invention. This specification cannot list all the embodiments of the inventive concept of the present invention exhaustively, and some features of the above different embodiments can be mutually replaced or combined. Those skilled in the art can also make simple replacements according to actual needs. The inventive concept of the present invention shall be subject to the scope of protection required.

Claims

1. A luminal stent, characterized in that, It includes a net cover, the net cover includes at least one column of hooking units, each hooking unit includes a first hooking member and a second hooking member that are hooked to each other in sequence from the proximal end to the distal end. The first hooking member includes a trough and two first wave bars connected to the trough. The second hooking member includes a crest and two second wave bars connected to the crest. The trough of the first hooking member and the crest of the second hooking member are axially relatively movable; in the axial direction, the net cover includes a proximal cover and a distal cover. In the proximal cover, the first wave bar of the same hooking unit on the side close to the radial edge of the net cover straddles above the second wave bar; and / or, in the distal cover, the second wave bar of the same hooking unit on the side close to the radial edge of the net cover straddles above the first wave bar.

2. The lumen stent according to claim 1, wherein, There is a hooking gap between the first hooking member and the second hooking member of the same hooking unit.

3. The lumen stent according to claim 1, wherein, The trough and the crest include cross bars, and the two first wave bars are connected by the cross bar, and / or, the two second wave bars are connected by the cross bar.

4. The lumen stent according to claim 3, characterized in that, The included angle formed between the first wave bar and the cross bar is an obtuse angle, and / or, the included angle formed between the second wave bar and the cross bar is an obtuse angle.

5. The lumen stent according to claim 3, characterized in that, The cross bar is a straight bar or an arc-shaped bar.

6. The luminal stent according to claim 1, wherein Along the circumferential direction of the lumen stent, the net cover includes a first mesh area and at least two second mesh areas respectively connected to both sides of the first mesh area; the second mesh area includes at least one column of the hooking units, and the first mesh area includes multiple columns of cross units.

7. The lumen stent according to claim 1, characterized in that, The first wave bar and the second wave bar of the hooking unit on the side close to the radial edge of the net cover form an axial interval. The multiple axial intervals formed by the same column of hooking units include an end interval and a middle interval. The end interval is closer to the axial end of the net cover than the middle interval, and the maximum axial length of at least one end interval is greater than the maximum axial length of the middle interval.

8. The lumen stent according to claim 1, wherein The net cover further includes at least one column of side connectors provided on the radial side of the net cover. The side connectors are connected to the hooking units, and the side connectors include connection holes for connection.

9. The lumen stent according to claim 8, wherein The net cover further includes side end connectors provided at the axial ends of the net cover. Among the multiple side connectors in the same column, there are two first side connectors and a second side connector located between the two first side connectors. The first side connectors are axially connected to the side end connectors and the hooking units respectively, and the second side connector is connected to a first hooking member and a second hooking member respectively.

10. The luminal stent according to any one of claims 1-9, characterized in that, The lumen stent further includes a main stent. The main stent includes an inner cavity, and a groove is formed by the side surface of the main stent being radially recessed inward. The net cover is connected to the groove, and at least a part of the net cover and the bottom of the groove form a radial interval in the radial direction of the lumen stent, and the radial interval communicates with the inner cavity.

11. The lumen stent according to claim 10, wherein, The net cover is connected to the main stent through multiple side connectors, and the interval formed between adjacent two side connectors communicates with the radial interval.

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