Z-shaped braided stent

Abstract

A Z-braided stent implantable in a human organ, comprising: a first tubular wire mesh having N braided rings formed by continuously braiding a first braiding wire (I) in a Z-shape, each braided ring of the first tubular wire mesh having a plurality of first bending points (A) formed by bending the first braiding wire (I) and distributed at intervals, and a second tubular wire mesh having N braided rings formed by continuously braiding a second braiding wire (II) in a Z-shape, each braided ring of the second tubular wire mesh having a plurality of second bending points (B) formed by bending the second braiding wire (II) and distributed at intervals. The second tubular wire mesh and the first tubular wire mesh are connected together by hooking the first bending point (A) and the second bending point (B) to form a Z-braided stent, which is axially deformable in compression but essentially axially immobile in extension.

Description

Technical Field

[0001] The present invention relates to a stent that can be implanted into a human organ, and more particularly to a braided stent having unique deformation characteristics.

Background Art

[0002] With the development of medical technology, the treatment of various diseases in the human body has evolved into interventional treatment. Among them, the most widespread is the vascular stent, which is basically made by braiding shape memory alloy wires into tubular structures with various radii. The stent can be deformed both radially and axially so as to be inserted into a delivery device. When the delivery device enters a specific position in the human body, the stent is released to support the blood vessel and maintain or induce blood flow. Therefore, the deformation of the stent is a common feature of existing stents. At the same time, the stent is in a preset basic form in the released state, and then the stent deforms again together with the structure of the human organ, and this deformed stent will have a deforming force, which will act on the human organ. In the process of use, at best, the patient will feel discomfort, and at worst, the organ will be damaged, resulting in a medical accident. Therefore, due to the diversity of human organs, it is difficult to adapt existing braided stents to various organ requirements and treatment requirements. For this reason, designing a stent with a specific structure to solve various needs is an urgent problem to be solved.

Summary of the Invention

Problems to be Solved by the Invention

[0003] An object of the present invention is to disclose a stent having a specific braided structure for coping with a specific desired treatment.

Means for Solving the Problems

[0004] According to a first aspect of the present invention, a Z-shaped braided stent that can be implanted into a human organ, wherein the Z-shaped braided stent A first tubular or cylindrical wire mesh formed by having N braided rings and continuously braiding a first braiding wire in a Z shape, wherein each braided ring of the first tubular wire mesh is formed by bending the first braiding wire and has a plurality of first bending points that are distributed at intervals, the first tubular or cylindrical wire mesh; A second tubular or cylindrical wire mesh formed by having N braided rings and continuously braiding a second braiding wire in a Z shape, wherein each braided ring of the second tubular wire mesh is formed by bending the second braiding wire and has a plurality of second bending points that are distributed at intervals, the second tubular or cylindrical wire mesh; and By hooking the first bending point (A) and the second bending point (B), the second tubular wire mesh and the first tubular wire mesh are connected together to form a Z-shaped braided stent. Continuously braiding the first braiding wire in a Z shape means that the first braiding wire is braided into a continuous first saw-tooth-shaped mesh that is tubular between two adjacent braided rings and is finally braided into the first tubular wire mesh. Continuously braiding the second braiding wire in a Z shape means that the second braiding wire is braided into a continuous second saw-tooth-shaped mesh that is tubular between two adjacent braided rings and is finally braided into the second tubular wire mesh, which is a tubular stent, characterized in that.

[0005] Preferably, the bending apex of the first saw-tooth-shaped mesh between two adjacent braided rings is the first bending point, and the bending apex of the second saw-tooth-shaped mesh between two adjacent braided rings is the second bending point.

[0006] Preferably, after the first braiding wire jumps from the first bending point at the end of the i-th braiding ring to the (i + 2)-th braiding ring and a Z-shaped continuous braiding is started, a plurality of first bending points are formed on the (i + 2)-th braiding ring and the (i + 1)-th braiding ring. At this time, the first bending point at the tip is formed on the (i + 2)-th braiding ring, and the first bending point at the end is formed on the (i + 1)-th braiding ring. After the second braiding wire jumps from the second bending point at the end of the i-th braiding ring to the (i + 2)-th braiding ring and a Z-shaped continuous braiding is started, a plurality of second bending points are formed on the (i + 2)-th braiding ring and the (i + 1)-th braiding ring. At this time, the second bending point at the tip is formed on the (i + 2)-th braiding ring, and the second bending point at the end is formed on the (i + 1)-th braiding ring.

[0007] Preferably, the first and second braiding rings and the (N - 1)-th and N-th braiding rings of the first tubular wire mesh and the second tubular wire mesh extend circumferentially parallel to the tubular stent, and the third to (N - 2)-th braiding rings extend spirally at a helix angle α.

[0008] Preferably, the helix angle α is 10° to 50°.

[0009] Preferably, the bending angle β between the first bending point and the second bending point is 30° to 60°.

[0010] Preferably, the first and second braiding rings and the (N - 1)-th and N-th braiding rings of the first tubular wire mesh and the second tubular wire mesh extend circumferentially parallel to the tubular stent, and the third to (N - 2)-th braiding rings extend spirally at a helix angle α. The spiral pitch S between the braiding wire I and the braiding wire II from the third braiding ring to the N-th braiding ring is 0.2 to 10 mm.

[0011] Preferably, the first braiding wire and / or the second braiding wire is made of a decomposable material.

[0012] Preferably, the Z-shaped braided stent of the present invention further comprises a traction device that connects the Nth braiding ring of the first tubular wire mesh and the Nth braiding ring of the second tubular wire mesh, and the traction device comprises a traction wire braided mesh having one end connected to the Nth braiding ring of the first tubular wire mesh and the Nth braiding ring of the second tubular wire mesh, and a connection end connected to the other end of the traction wire braided mesh.

[0013] Preferably, the traction wire braided mesh is braided from a plurality of traction wires or formed by laser etching a metal tube.

[0014] Preferably, the connection end is offset from the axis of the circular stent.

[0015] Preferably, the connection end is hook-shaped or tubular.

[0016] According to another aspect of the present invention, there is provided a method for implementing a Z-shaped braided stent that can be implanted into a human organ, wherein the Z-shaped braided stent is tubular, and the method comprises forming a first tubular wire mesh having N braiding rings by continuously braiding a first braiding wire in a Z shape, and each braiding ring of the first tubular wire mesh is formed by bending the first braiding wire and has a plurality of first bending points distributed at intervals, forming; After forming the first tubular wire mesh having N braiding rings, forming a second tubular wire mesh having N braiding rings by continuously braiding a second braiding wire in a Z shape, and each braiding ring of the second tubular wire mesh is formed by bending the second braiding wire and has a plurality of second bending points distributed at intervals, forming. By hooking the first bending point (A) and the second bending point (B), the second tubular wire mesh and the first tubular wire mesh are connected together to form a Z-shaped braided stent. Continuously braiding the first braiding wire in a Z-shape means that the first braiding wire is braided into a continuous tubular first sawtooth-shaped mesh between two adjacent braiding rings and finally braided into the first tubular wire mesh. Continuously braiding the second braiding wire in a Z-shape means that the second braiding wire is braided into a continuous tubular second sawtooth-shaped mesh between two adjacent braiding rings and finally braided into the second tubular wire mesh.

[0017] The above-described technical solutions disclosed in the present invention have very unique technical features. The braided stent is axially deformable and compressible, but is substantially axially non-deformable and non-extendable. The reason is that each bending point is a point where the braiding wires I and II are hooked to each other or is regarded as a constraint point. Therefore, axial stretching and elongation are restricted at the bending point, but axial separation and compression are not restricted. During compression, the radius of the tubular braided stent does not substantially change, and thus the radius of the entire tubular braided stent also does not substantially change. Another feature of the present invention is that the entire braided stent can be bent and deformed, and the deformed braided stent can still maintain its deformed state after the external force is lost, that is, the deformed braided stent substantially does not have an internal elastic force to return to its original state. This avoids the application of unnecessary or harmful forces to the body cavity of the human body, which is very beneficial for the long-term maintenance of the braided stent after implantation in the human body.

Brief Description of the Drawings

[0018]

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Mode for Carrying Out the Invention

[0019] A detailed description of specific embodiments of the present invention is provided in conjunction with the accompanying drawings. It should be noted that the detailed description of specific embodiments is intended to facilitate the understanding of the technical spirit of the present invention and should not be construed as limiting the scope of the claims of the present invention.

[0020] FIG. 1 shows a Z-shaped braided stent that can be implanted into a human organ according to the present invention. The Z-shaped braided stent is tubular as shown in FIGS. 2a and 2b. FIG. 1 is an enlarged view of the tubular stent as shown in FIGS. 2a and 2b, and the vertical column 1 and the vertical column 17 are the same.

[0021] The Z-shaped braided stent that can be implanted into a human organ of the present invention is a first tubular wire mesh (i.e., the wire mesh shown by the thick solid line in FIG. 1) formed by having N braided rings and continuously braiding the first braiding wire I in a Z shape. Each braided ring of the first tubular wire mesh is formed by bending the first braiding wire I and has a plurality of first bending points A that are distributed at intervals. The first tubular wire mesh and a second tubular wire mesh (i.e., the wire mesh shown by the thin solid line in FIG. 1) formed by having N braided rings and continuously braiding the second braiding wire II in a Z shape. Each braided ring of the second tubular wire mesh is formed by bending the second braiding wire II and has a plurality of second bending points B that are distributed at intervals. The second tubular wire mesh, and is provided with As shown in FIGS. 1 and 4, the first bending point A formed by bending the first braiding wire I includes the first bending point 11A of the first braiding wire and the second bending point 12A of the first braiding wire. As shown in FIGS. 1 and 6, the second bending point B formed by bending the second braiding wire II includes the first bending point 11B of the second braiding wire and the second bending point 12B of the second braiding wire. The Z-shaped braided stent is formed by hooking the second bending point B and the first bending point A so that the second tubular wire mesh and the first tubular wire mesh are connected (as shown in the figure, the second bending point B is hooked to the first bending point A from the second braided ring to the (N - 1)th braided mesh). exist. Continuously braiding the first braiding wire I in a Z shape means that the first braiding wire I is braided into a tubular and continuous first sawtooth-shaped mesh (for example, the sawtooth-shaped mesh shown by the thick solid line between the first braiding ring and the second braiding ring in FIG. 1) between two adjacent braiding rings, and finally braided into the first tubular wire mesh. exist. Here, continuously braiding the second braiding wire II in a Z shape means that the second braiding wire II is braided into a tubular and continuous second sawtooth-shaped mesh (for example, the sawtooth-shaped mesh shown by the thin solid line between the first braiding ring and the second braiding ring in FIG. 1) between two adjacent braiding rings, and finally braided into the second tubular wire mesh.

[0022] As shown in FIG. 1, the bending vertex of the first sawtooth-shaped mesh between two adjacent braiding rings is the first bending point A, and the bending vertex of the second sawtooth-shaped mesh between two adjacent braiding rings is the second bending point B.

[0023] As shown in FIG. 1, the first braiding wire I jumps from the first bending point at the end of the i-th braiding ring to the (i + 2)-th braiding ring, and continuous Z-shaped braiding is started. A plurality of first bending points are formed on the (i + 2)-th braiding ring and the (i + 1)-th braiding ring. At this time, a first bending point is formed at the tip on the (i + 2)-th braiding ring, and a first bending point is formed at the end on the (i + 1)-th braiding ring. For example, when i is 1, the first braiding wire I jumps from the first bending point at the end of the first braiding ring (the first bending point located in the first row of the first braiding ring) to the third braiding ring, and continuous Z-shaped braiding is started. A plurality of first bending points are formed on the third braiding ring and the second braiding ring. At this time, the first bending point at the tip on the third braiding ring (the first bending point located in the second row of the third braiding ring) and the first bending point at the end on the second braiding ring (the first bending point located in the first row of the second braiding ring) are formed.

[0024] As shown in Fig. 1, the second braiding wire jumps from the second bending point at the end of the i-th braiding ring to the (i + 2)-th braiding ring, and a Z-shaped continuous braiding is started. A plurality of second bending points are formed on the (i + 2)-th braiding ring and the (i + 1)-th braiding ring. At this time, the second bending point is formed at the tip on the (i + 2)-th braiding ring, and the second bending point is formed at the end on the (i + 1)-th braiding ring. For example, when i is 1, the second braiding wire II jumps from the second bending point at the end of the first braiding ring (the second bending point located in the second row of the first braiding ring) to the third braiding ring, and a Z-shaped continuous braiding is started. A plurality of second bending points are formed on the third braiding ring and the second braiding ring. At this time, the second bending point at the tip on the third braiding ring (the second bending point located in the third row of the third braiding ring) and the second bending point at the end on the second braiding ring (the second bending point located in the second row of the second braiding ring) are formed.

[0025] As shown in Fig. 1, the first and second braiding rings and the (N - 1)-th and N-th braiding rings of the first tubular wire mesh and the second tubular wire mesh extend circumferentially parallel to the tubular stent, and the third to (N - 2)-th braiding rings extend spirally at a helix angle α.

[0026] As shown in Fig. 1, the braided stent has a helix angle α of 10° to 50°. The bending angle β between the first bending point and the second bending point is 30° to 60°.

[0027] As shown in Fig. 1, the first and second braiding rings and the (N - 1)-th and N-th braiding rings of the first tubular wire mesh and the second tubular wire mesh extend circumferentially parallel to the tubular stent, and the third to (N - 2)-th braiding rings extend spirally at a helix angle α. The spiral pitch S of the braiding wires I and II from the third braiding ring to the N-th braiding ring is 0.2 to 10 mm.

[0028] The first braiding wire I and / or the second braiding wire II of the present invention are composed of the same material or different materials, particularly including combinations of metal wire + metal wire, metal wire + non-metal wire, and non-metal wire + non-metal wire.

[0029] Generally, the metal wire is selected from materials such as stainless steel wire, cobalt-chromium alloy wire, nickel-titanium alloy wire, and degradable zinc / magnesium alloy wire, and the non-metal wire is selected from materials such as degradable polylactic acid wire.

[0030] Furthermore, the present invention further comprises a traction device for connecting the Nth braiding ring of the first tubular wire mesh and the Nth braiding ring of the second tubular wire mesh as shown in FIGS. 9 to 16. The traction device includes a traction wire braiding mesh with one end connected to the Nth braiding ring of the first tubular wire mesh and the Nth braiding ring of the second tubular wire mesh, and a connection end portion connected to the other end of the traction wire braiding mesh. The traction wire braiding mesh is braided from a plurality of traction wires or formed by laser etching a metal tube. The connection end portion is offset from the axis of the circular stent. The connection end portion is hook-shaped or tubular.

[0031] FIGS. 3a and 3b show a mold for braiding the first braiding wire I and the second braiding wire II according to the present invention. The mold is a tubular body provided with a plurality of raised portions for braiding on the surface.

[0032] The Z-shaped braided stent transplantable into the human organ of the present invention is manufactured by braiding the first braiding wire I or the second braiding wire II in the mold according to the marking mode shown in FIGS. 5a and 5b.

[0033] The implementation method for the Z-shaped braided stent transplantable into the human organ of the present invention is A first tubular wire mesh formed by having N braided rings and continuously braiding a first braiding wire I in a Z shape, wherein each braided ring of the first tubular wire mesh is formed by bending the first braiding wire I and has a plurality of first bending points distributed at intervals, the first tubular wire mesh; A second tubular wire mesh having N braided rings formed by continuously braiding a second braiding wire II in a Z shape after forming the first tubular wire mesh, wherein each braided ring of the second tubular wire mesh is formed by bending the second braiding wire II and has a plurality of second bending points distributed at intervals, the second tubular wire mesh; and By hooking the first bending point (A) and the second bending point (B), the second tubular wire mesh and the first tubular wire mesh are connected together to form a Z-shaped braided stent. Continuously braiding the first braiding wire I in a Z shape means that the first braiding wire I is braided into a continuous first saw-tooth-shaped mesh in a tubular form between two adjacent braided rings. Continuously braiding the second braiding wire II in a Z shape means that the second braiding wire II is braided into a continuous second saw-tooth-shaped mesh in a tubular form between two adjacent braided rings.

[0034] Hereinafter, the present invention will be described in detail with reference to FIGS. 1 to 16. The technical solution of a specific embodiment of the present invention is as follows: The braiding wire I of the tubular braided stent is repeatedly and continuously bent in a Z shape to form a plurality of bending points, and it forms a tubular shape by going around once, and extends from one end to the other end of the tubular shape in a rotating manner. The first and second bending points are located on the circumference of the same radius. The third to (N - 2)th bending points extend spirally to the other end with a helix angle α. The bending points of the (N - 1)th and Nth braiding rings are located on the circumference of the same radius. The braiding wire II is repeatedly and continuously bent in a Z shape to form a plurality of bending points. The braiding wires I and II are hooked to each other at corresponding bending points, and the braiding wire II extends from one end to the other end of the tubular shape. The structure of the tubular braided stent according to the above aspect of the present invention is shown in FIG. 1. In order to better understand the three-dimensional structure, the tubular braided stent shown in FIG. 1 is axially cut and unfolded into a plane, and the braiding wire I is wound around the mold of the braided stent (shown in FIG. 3) (shown in FIG. 5). FIG. 4 shows the structure of the flat unfolded state of the braiding wire I, and FIG. 6 shows the structure of another flat unfolded state of the braiding wire II. As shown in FIG. 4, a and a1 are actually the same point, that is, a = a1. For the same reason, b = b1 and P = P1. As shown by the arrow in FIG. 4, the braiding wire I is repeatedly and continuously bent in a Z shape from point a to point a1, and the lengths of the bent parts are the same, that is, it returns to point a. Then, as shown by the arrow, the repeated bending of the second ring is started. The length of the bent part of the braiding wire I of the ring gradually becomes longer. When passing point b1, the repeated bending of the third ring is started and repeated up to the Nth ring. The lengths of the bent parts of the braiding wire 1 are the same. The length of the bent part of the braiding wire 1 in the (N + 1)th part gradually becomes longer. The bent part of the braiding wire 1 in the last (N + 1)th part has the same length, which constitutes the structure of the braiding wire 1 of the present invention.FIG. 6 shows the structure of another braiding wire II in a flat-expanded state. The braiding wire II is repeatedly and continuously bent in a Z shape to form a plurality of bending points. The braiding wires I and II are hooked to each other at corresponding bending points (shown in FIG. 7). As shown in FIGS. 4 and 6, the plurality of bending points on the line segments aa1 and bb1 are the first and second bending points. The bending points of the first circle and the second circle are located on the circumferences of the same radius, but the bending points of the third to (N - 2)th circles extend spirally to the other end with a winding angle α, and the bending points of the (N - 1)th and Nth circles are located on the circumferences of the same radius. According to the present invention described above, since the braiding wires I and II are hooked to each other and constrained by each other at the bending points, when the tubular braided stent receives an axial tensile force, the braided stent does not substantially undergo tensile deformation and at the same time does not cause a change in radius. When the braided stent receives an axial compressive force, the hooking structure at the bending points does not limit the displacement of the braiding wires I and II to the center or intermediate position. That is, the braiding wires I and II at each bending point are disengaged from the hooked state. That is, the braided stent as a whole exhibits a shortened length or a compressed state. Similarly, the radius of the braided stent does not change, and the entire braided stent is in a relaxed state. When the braided stent is inserted into the body cavity of the human body, the braided stent of the present invention does not change in radius and does not exert a force on the wall surface of the body cavity of the human body, so damage to the body cavity of the human body is prevented. When the body cavity of the human body is in a bent state, the above-described braided stent is bent together with the body cavity of the human body. The inner bent portion of the bent braided stent is similar to the above-described compressed state, and a part of the bending points of the braiding wires I and II is separated. That is, the inner bent portion is in a relaxed state. On the other hand, the outer bent portion of the braided stent remains in a hooked state, but at the same time, no repulsive force is generated after bending. When the entire braided stent is bent, the whole is in a relaxed state, and no elastic force is generated after bending the whole. Therefore, the bent braided stent does not generate an acting force on the body cavity of the human body, and damage to the body cavity of the human body is avoided. Alternatively, the braided stent of the present invention can be randomly deformed and bent, and the bent and deformed state is maintained.The present invention is particularly suitable for curved body cavities of the human body, such as curved intestinal tracts with a relatively large diameter in the human body, or cerebral blood vessels in the narrow part of the human brain. The braided stent of the present invention greatly improves safety.

[0035] In order to provide a braided stent suitable for body cavities of the human body in various states, the helix angle α of the braided stent is 10° to 50°, whereby a braided stent with different shrinkage rates can be provided. The bending angles β of the braiding wires I and II of the braided stent are 30° to 60°. The difference in the bending angle β can change the braiding grid density of the braided stent, whereby the radial supporting force of the entire braided stent can be adjusted. The bending angle β is preferably 35° to 45°. The helix pitch S of the braiding wires I and II from the third braiding ring to the Nth braiding ring of the braided stent is 0.2 to 10 mm, which can be adapted to the states of braided stents with different diameters. The braided stent is composed of a plurality of braiding wires. Both of the above-mentioned braiding wires I and II are single filaments, that is, the braided stent of the present invention can be braided with two filaments, but the production efficiency of the manufacturing process will decrease. If a plurality of braiding wires are used, and 1 / 3 to 2 / 3 of the plurality of braiding wires are occupied by braiding wires made of degradable materials, the braiding efficiency can be greatly improved. For example, the braided stent is composed of three braiding wires according to the above-mentioned braiding structure, two of which are metal alloy wires and one is a braiding wire made of degradable material, or the braided stent is composed of four braiding wires, two of which are metal alloy wires. Two braiding wires made of degradable materials, of course, even five or six wires, can form a braided stent. The above-mentioned braiding wires made of degradable materials may be braided according to the structure of the above-mentioned braiding wires. Alternatively, they can be braided after being mixed with metal alloy braiding wires. The diameter of the mixed braided metal alloy wire can be reduced without reducing the initial radial supporting force of the braided stent. After entering the human body for a certain period, the degradable braiding wire is decomposed, the amount of metal in the body cavity of the human body decreases, and the rejection reaction of the human body to foreign objects is reduced.

[0036] FIG. 10 shows the structure of the traction device with the braiding wire flattened. FIG. 11 shows a schematic diagram showing the appearance of the traction device after combining the braiding stents of the braiding wire. FIG. 12 shows a schematic diagram of a partially enlarged structure of the connection part between the traction device and the braiding stent. FIG. 13 shows a schematic diagram of the structure of the traction device which is a metal tube formed by laser etching. FIG. 14 shows a schematic diagram of a partially enlarged structure of the connection part between the traction device and the braiding stent.

[0037] FIG. 15 is a schematic diagram of the structure of the hook-shaped connection end portion at the end portion of the braiding stent. FIG. 16 is a schematic diagram of the structure of the tubular connection end portion at the end portion of the braiding stent.

[0038] In use, the present invention is installed in the delivery tube by forced radial compression, and then delivered into the necessary body cavity of the human body. When released, the braiding stent returns to a preset normal state and serves to support the body cavity. After a certain period of actual use, it is necessary to remove the above-mentioned braiding stent from the human body. Therefore, a traction device for facilitating the release and recovery of the stent is provided at one end of the tubular braiding stent. As shown in FIGS. 8 and 9, the traction device has a plurality of traction wires 1 composed of braiding wires. The plurality of traction wires 1 converge and are fixedly connected to the connection end 2. By connecting to the connection end 2, the braiding stent is recovered through a capture device inserted into the body cavity of the human body, and the human body is taken out. In order to avoid the influence of the connection end 2 on the movable body in the body cavity of the human body, the above-mentioned connection end 2 is arranged eccentrically, that is, the connection end 2 is positioned on the extension line of the braided wall surface of the inner cavity of the braiding stent. This can reduce the obstructing liquid flow and improve the therapeutic effect.

[0039] Although the present invention has been described in detail above, the present invention is not limited thereto, and those skilled in the art can make various modifications in accordance with the principles of the present invention. Therefore, while it is intended that the present invention include modifications and variations thereof, provided that such modifications and variations are within the scope of the appended claims and their equivalents.

Claims

1. A Z-shaped braided stent for implantation into a human organ, wherein the Z-shaped braided stent comprises a first tubular wire mesh having N (N>4) braided rings formed by continuously braiding a first braiding wire in a Z shape, and the first tubular wire mesh includes a plurality of first saw-tooth-shaped meshes that do not intersect each other and are formed by continuously bending the first braiding wire between two adjacent braided rings among the N braided rings, a second tubular wire mesh having N braided rings formed by continuously braiding a second braiding wire in a Z shape, and the second tubular wire mesh includes a plurality of second saw-tooth-shaped meshes that do not intersect each other and are formed by continuously bending the second braiding wire between two adjacent braided rings among the N braided rings, each braided ring from the second braided ring to the (N-1)-th braided ring in the first tubular wire mesh has a plurality of first bending points (11A) of the first braided wire and a plurality of second bending points (12A) of the first braided wire that are formed by bending the first braided wire and are distributed at intervals, and each braided ring from the second braided ring to the (N-1)-th braided ring in the second tubular wire mesh has a plurality of first bending points (11B) of the second braided wire and a plurality of second bending points (12B) of the second braided wire that are formed by bending the second braided wire and are distributed at intervals, a tubular stent comprising N braided rings in which the second tubular wire mesh and the first tubular wire mesh are connected together at each braided ring from the second braided ring to the (N-1)-th braided ring by hooking the first bending point (11B) of the second braided wire with the second bending point (12A) of the first braided wire and hooking the second bending point (12B) of the second braided wire with the first bending point (11A) of the first braided wire. The Z-shaped braided stent is characterized by the above. Claim 2: The peaks and valleys of the first sawtooth-shaped mesh are respectively the first bending point (11A) of the first braiding wire and the second bending point (12A) of the first braiding wire, and the peaks and valleys of the second sawtooth-shaped mesh are the first bending point (11B) of the second braiding wire and the second bending point (12B) of the second braiding wire. The Z-shaped braided stent according to claim 1, characterized in that.

3. The first braiding wire jumps from the second bending point (12A) of the first braiding wire at the end of the i-th braiding ring of the first tubular wire mesh to the (i + 2)-th braiding ring. After the Z-shaped continuous braiding is started, a plurality of first bending points (11A) of the first braiding wire and a plurality of second bending points (12A) of the first braiding wire are formed on the (i + 2)-th braiding ring and the (i + 1)-th braiding ring. At this time, the first bending point (11A) of the first braiding wire at the tip is formed on the (i + 2)-th braiding ring, and the second bending point (12A) of the first braiding wire at the end is formed on the (i + 1)-th braiding ring. The second braiding wire jumps from the second bending point (12B) of the second braiding wire at the end of the i-th braiding ring to the (i + 2)-th braiding ring. After the Z-shaped continuous braiding is started, a plurality of first bending points (11B) of the second braiding wire and a plurality of second bending points (12B) of the second braiding wire are formed on the (i + 2)-th braiding ring and the (i + 1)-th braiding ring. At this time, the first bending point (11B) of the second braiding wire at the tip is formed on the (i + 2)-th braiding ring, and the second bending point (12B) of the second braiding wire at the end is formed on the (i + 1)-th braiding ring. The Z-shaped braided stent according to claim 1 or 2, characterized in that i = 1, 2... N.

4. The first braiding ring, the second braiding ring, the (N - 1)-th braiding ring, and the N-th braiding ring of the first tubular wire mesh and the second tubular wire mesh extend circumferentially in parallel with the tubular stent, and the third to (N - 2)-th braiding rings of the first tubular wire mesh and the second tubular wire mesh extend spirally at a helix angle α. The Z-shaped braided stent according to claim 1 or 2, characterized in that.

5. The Z-shaped braided stent according to claim 4, wherein the winding angle α is 10° to 50°.

6. The Z-shaped braided stent according to claim 1 or claim 2, wherein the first bending point (11A) of the first braided wire, the second bending point (12A) of the first braided wire, the first bending point (11B) of the second braided wire, and the second bending point (12B) of the second braided wire have a bending angle β of 30° to 60°.

7. The first braided ring, the second braided ring, and the (N-1)th and Nth braided rings of the first tubular wire mesh and the second tubular wire mesh extend circumferentially in parallel with the tubular stent, and the third to (N-2)th braided rings of the first tubular wire mesh and the second tubular wire mesh extend spirally at the winding angle α. The Z-shaped braided stent according to claim 1 or claim 2, wherein the spiral interval S between the first braided wire and the second braided wire from the third braided ring to the Nth braided ring of the first tubular wire mesh and the second tubular wire mesh is 0.2 to 10 mm.

8. The first braided wire and / or the second braided wire are composed of the same material or different materials, particularly including combinations of metal wire + metal wire, metal wire + non-metal wire, and non-metal wire + non-metal wire. The Z-shaped braided stent according to any one of claims 1 or 2, wherein the metal wire is selected from materials such as stainless steel wire, cobalt-chromium alloy wire, nickel-titanium alloy wire, and degradable zinc / magnesium alloy wire, and the non-metal wire is selected from materials such as degradable polylactic acid wire.

9. The Z-shaped braided stent according to claim 1 or claim 2, further comprising a traction device connecting the Nth braided ring of the first tubular wire mesh and the Nth braided ring of the second tubular wire mesh, the traction device comprising a traction wire braided mesh having one end connected to the Nth braided ring of the first tubular wire mesh and the Nth braided ring of the second tubular wire mesh, and a connection end connected to the other end of the traction wire braided mesh.

10. The Z-shaped braided stent according to claim 9, wherein the traction wire braided mesh is braided from a plurality of traction wires or formed by laser etching a metal tube.

11. The Z-shaped braided stent according to claim 10, wherein the connection end portion is offset from the axis of the tubular stent.

12. The Z-shaped braided stent according to claim 10, wherein the connection end portion is hook-shaped or tubular.

13. A method for manufacturing a Z-shaped braided stent to be implanted into a human organ, wherein the Z-shaped braided stent is a tubular stent having N (N>4) braided rings, and the manufacturing method comprises: forming a first tubular wire mesh having N braided rings by continuously braiding a first braiding wire in a Z shape, the first tubular wire mesh including a plurality of first saw blade-shaped meshes that do not intersect each other and are formed by continuously bending the first braiding wire between two adjacent braided rings among the N braided rings; after forming the first tubular wire mesh having N braided rings, forming a second tubular wire mesh having N braided rings by continuously braiding a second braiding wire in a Z shape, the second tubular wire mesh including a plurality of second saw blade-shaped meshes that do not intersect each other and are formed by continuously bending the second braiding wire between two adjacent braided rings among the N braided rings; each of the braided rings from the second braided ring to the (N-1)th braided ring in the first tubular wire mesh has a plurality of first bending points (11A) and second bending points (12A) of the first braided wire, which are formed by bending the first braiding wire and are distributed at intervals, and each of the braided rings from the second braided ring to the (N-1)th braided ring in the second tubular wire mesh has a plurality of first bending points (11B) and second bending points (12B) of the second braided wire, which are formed by bending the second braiding wire and are distributed at intervals; In each of the braiding rings from the second braiding ring to the (N - 1)th braiding ring, by hooking the first bending point (11B) of the second braiding wire and the second bending point (12A) of the first braiding wire, and hooking the second bending point (12B) of the second braiding wire and the first bending point (11A) of the first braiding wire, the second tubular wire mesh and the first tubular wire mesh are connected together, a manufacturing method of a Z-shaped braided stent.

14. The peaks and valleys of the first saw-tooth-shaped mesh are respectively the first bending point (11A) of the first braiding wire and the second bending point (12A) of the first braiding wire, and the peaks and valleys of the second saw-tooth-shaped mesh are the first bending point (11B) of the second braiding wire and the second bending point (12B) of the second braiding wire. The manufacturing method of the Z-shaped braided stent according to claim 13.

15. The first braiding wire jumps from the second bending point (12A) at the end of the i-th braiding ring of the first tubular wire mesh to the (i + 2)-th braiding ring. After the Z-shaped continuous braiding is started, a plurality of first bending points (11A) of the first braiding wire and a plurality of second bending points (12A) of the first braiding wire are formed on the (i + 2)-th braiding ring and the (i + 1)-th braiding ring. At this time, the first bending point (11A) at the tip is formed on the (i + 2)-th braiding ring, and the second bending point (12A) at the end is formed on the (i + 1)-th braiding ring. The second braiding wire jumps from the second bending point (12B) at the end of the i-th braiding ring to the (i + 2)-th braiding ring. After the Z-shaped continuous braiding is started, a plurality of first bending points (11B) of the second braiding wire and a plurality of second bending points (12B) of the second braiding wire are formed on the (i + 2)-th braiding ring and the (i + 1)-th braiding ring. At this time, the first bending point (11B) at the tip is formed on the (i + 2)-th braiding ring, and the second bending point (12B) at the end is formed on the (i + 1)-th braiding ring., Characterized in that i = 1, 2... N. The manufacturing method of the Z-shaped braided stent according to claim 13 or 14.

16. The first braided ring, the second braided ring, the (N - 1)th braided ring, and the Nth braided ring of the first tubular wire mesh and the second tubular wire mesh extend circumferentially in parallel with the tubular stent, and the third to (N - 2)th braided rings of the first tubular wire mesh and the second tubular wire mesh extend spirally at a vine winding angle α. The manufacturing method of the Z-shaped braided stent according to claim 13 or 14, characterized in that.

17. The manufacturing method of the Z-shaped braided stent according to claim 16, characterized in that the vine winding angle α is 10° to 50°.

18. The manufacturing method of the Z-shaped braided stent according to claim 13 or 14, characterized in that the first bending point (11A) of the first braided wire, the second bending point (12A) of the first braided wire, the first bending point (11B) of the second braided wire, and the second bending point (12B) of the second braided wire have a bending angle β of 30° to 60°.

19. The first and second braided rings and the (N - 1)th and Nth braided rings of the first tubular wire mesh and the second tubular wire mesh extend circumferentially in parallel with the tubular stent, and the third to (N - 2)th braided rings of the first tubular wire mesh and the second tubular wire mesh extend spirally at a vine winding angle α. The manufacturing method of the Z-shaped braided stent according to claim 13 or 14, characterized in that the spiral interval S between the first braided wire and the second braided wire from the third braided ring to the Nth braided ring of the first tubular wire mesh and the second tubular wire mesh is 0.2 to 10 mm.

20. The manufacturing method of the Z-shaped braided stent according to claim 13 or claim 14, further comprising a traction device connecting the Nth braided ring of the first tubular wire mesh and the Nth braided ring of the second tubular wire mesh, and the traction device is A traction wire braided mesh having one end connected to the Nth braided ring of the first tubular wire mesh and the Nth braided ring of the second tubular wire mesh, And a connection end portion connected to the other end of the traction wire braided mesh.

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