Lumen stent

Abstract

The present application relates to a kind of luminal stents, including auxiliary stent, the auxiliary stent includes the constraint hole of deformable, when the luminal stent is radially compressed to the inner diameter of the target luminal is substantially equal to the outer diameter, the constraint hole can be inserted into guide wire, and the auxiliary stent can exert clamping force to the guide wire threaded in the constraint hole.Given that the auxiliary stent can exert clamping force to the guide wire threaded in the mesh, so that the auxiliary stent plays a good positioning role to the guide wire, effectively prevent the guide wire from being pulled out of the groove during the guide wire is threaded in the groove, so that the bridging stent is smoothly implanted into branch blood vessel along the path of the guide wire, improve the implantation efficiency and precision of bridging stent.

Description

Technical Field

[0001] This invention relates to the field of interventional medical devices, and in particular to a lumen stent. Background Technology

[0002] This section provides only background information relevant to this disclosure and is not necessarily prior art.

[0003] Aneurysms and aortic dissections are common vascular diseases in clinical practice. Without medical intervention, aneurysms are at risk of rupture, posing a great threat to the patient's life.

[0004] With the continuous development of modern medical technology, minimally invasive surgery has been used to implant stents into the body to treat aneurysms and arterial dissections. This treatment method is widely used due to its minimal trauma and rapid recovery. The stent is compressed into a delivery device and guided into the body along a pre-implanted guidewire. Once it reaches the lesion, the stent is released to isolate the lesion and restore blood flow. After the aneurysm and arterial dissection lose their blood supply, the remaining blood in the aneurysm cavity gradually thrombus and myovascular tissue forms. The dilated aneurysm wall contracts under pressure, gradually returning to a near-original state, thus achieving the goal of treating aneurysms and arterial dissections.

[0005] When an aneurysm or arterial dissection is located on the aorta near a branch vessel, the implanted stent may obstruct the opening of the branch vessel, thus hindering blood flow. One current solution is to create a groove in the stent with a window allowing blood to pass through. The groove corresponds to the branch vessel, ensuring blood from the aorta can flow through this window into the branch vessel. However, after the stent is implanted in the aorta, to implant a bridging stent in the branch vessel, a guidewire must first pass through the branch vessel, through the groove, and into the window, before the bridging stent is implanted along the guidewire path. During this process, due to the relatively large space in the groove, the guidewire, after entering the groove, is easily dislodged from the window or even the groove due to blood flow impact and vascular pulsation, leading to bridging stent implantation failure. Summary of the Invention

[0006] One of the technical problems addressed by this invention is how to improve the efficiency and accuracy of bridging stent implantation.

[0007] A luminal stent for implantation into a target lumen includes an auxiliary stent comprising a deformable constraint hole. When the luminal stent is radially compressed to an outer diameter substantially equal to the inner diameter of the target lumen (i.e., the outer diameter of the radially compressed luminal stent may not be exactly equal to the inner diameter of the target lumen, allowing for a certain degree of error), the constraint hole allows for the insertion of a guidewire, and the auxiliary stent is capable of applying a clamping force to the guidewire passing through the constraint hole.

[0008] In one embodiment, the ratio between the outer diameter of the lumen support in its naturally deployed state and the inner diameter of the target lumen is 1+C%, where C% is the support magnification ratio and the value of C% ranges from 5% to 20%. When the lumen support is radially compressed to an outer diameter that is approximately equal to the inner diameter of the target lumen, the maximum inner diameter D1 of the constraint hole is less than the outer diameter D0 of the guide wire.

[0009] In one embodiment, when the lumen support is in its naturally deployed state, the maximum inner diameter of the constraint hole is D2, D2 / D0≤1+C%, and / or, where C% is the support magnification ratio; and / or, when the lumen support is in its naturally deployed state, D2 / D0≤1.

[0010] In one embodiment, the lumen support further includes a main support, the side of which is recessed toward its central axis to form a recessed section, and at least a portion of the auxiliary support forms a gap space in the radial direction between itself and the outer surface of the recessed section.

[0011] In one embodiment, the recessed section includes a groove, and the auxiliary support is at least partially received in the groove; the auxiliary support is a circumferentially closed tubular structure; or, the auxiliary support is a circumferentially non-closed structure with a notch, the length occupied by the notch in the axial direction of the auxiliary support is less than or equal to the total length of the auxiliary support, and the notch is located in the groove.

[0012] In one embodiment, the auxiliary support includes a mesh structure comprising multiple intersecting first braided wires and second braided wires, and deformable mesh holes formed by the first braided wires and second braided wires. The same first braided wire is located on the same side of the second braided wire at the intersection, or alternately located on opposite sides of the second braided wire. One or more mesh holes can serve as constraint holes.

[0013] In one embodiment, the constraint hole is circumferentially closed; or, the constraint hole is circumferentially open and has an opening, the width of which is smaller than the outer diameter of the guidewire when the lumen support is radially compressed to an outer diameter substantially equal to the inner diameter of the target lumen, or when the lumen support is in a naturally extended state.

[0014] In one embodiment, the auxiliary support includes an auxiliary support body and a barrier strip. The constraint hole is provided on the auxiliary support body and has an opening. The barrier strip can elastically expand and contract along its own length direction. The barrier strip is located in the opening and both ends are fixed to the auxiliary support body.

[0015] In one embodiment, the auxiliary support includes a plurality of auxiliary supports stacked together. The outermost auxiliary support has an external through hole, and the other auxiliary supports have internal through holes. At least one of the external through holes and the internal through holes serves as a constraint hole.

[0016] In one embodiment, the inner perforation is a constraint hole, and when the auxiliary support is in a naturally unfolded state, the maximum inner diameter of the outer perforation is greater than the maximum inner diameter of the inner perforation.

[0017] In one embodiment, the central axis of the largest inner circle of the outer perforation and the central axis of the largest inner circle of the inner perforation are coincident, parallel, and opposite to each other.

[0018] In one embodiment, the spacing between two adjacent auxiliary support layers is smaller than the outer diameter of the guide wire.

[0019] In one embodiment, the auxiliary support includes a three-dimensional mesh structure in which guide wire channels are provided through the constraint holes.

[0020] In one embodiment, the auxiliary support further includes a guide tube inserted in the guide wire channel, the lumen of the guide tube being used to pass through the guide wire.

[0021] In one embodiment, the auxiliary support further includes an elastic filler strip disposed in the gap between adjacent layers of the auxiliary support.

[0022] In one embodiment, the auxiliary support includes an auxiliary support body and a cover body connected to each other. The auxiliary support body has mesh openings, and the cover body is elastic and covers a portion of the mesh openings to form a constraint hole. The auxiliary support body and the cover body are used together to apply a clamping force to the guide wire.

[0023] One technical effect of one embodiment of the present invention is that, since the auxiliary stent can apply clamping force to the guidewire inserted in the constraint hole, the auxiliary stent can play a good positioning role for the guidewire. During the process of the guidewire being inserted into the groove, the guidewire is effectively prevented from falling out of the groove, so that the bridging stent can be smoothly implanted into the branch blood vessel along the path of the guidewire, thereby improving the implantation efficiency and accuracy of the bridging stent. Attached Figure Description

[0024] Figure 1 A schematic diagram of the aorta;

[0025] Figure 2 A schematic diagram of the structure after a luminal stent is implanted in the aorta;

[0026] Figure 3This is a schematic diagram of the front sectional view of the lumen stent;

[0027] Figure 4 for Figure 3 A top view of the structure of the lumen support;

[0028] Figure 5 for Figure 3 A side view of the lumen support structure;

[0029] Figure 6 for Figure 3 A schematic diagram of the planar structure of the closed-loop coil in the lumen support;

[0030] Figure 7 for Figure 6 A schematic diagram of the planar unfolded structure of the closed-loop waveguide shown;

[0031] Figure 8 for Figure 3 A schematic diagram of the planar structure of the open-loop waveguide in the lumen support;

[0032] Figure 9 for Figure 8 A schematic diagram of the planar unfolded structure of the open-loop waveguide shown;

[0033] Figure 10 for Figure 3 A three-dimensional structural diagram of the main support of the lumen stent;

[0034] Figure 11 for Figure 10 A front view schematic diagram of the main support structure shown;

[0035] Figure 12 for Figure 10 A side view of the main support structure shown;

[0036] Figure 13 This is a schematic diagram of the planar structure after the guidewire is inserted into the luminal stent and aorta.

[0037] Figure 14 This is a schematic diagram of the planar structure of a bridging stent implanted into a branch blood vessel via a guidewire.

[0038] Figure 15 This is a schematic diagram of the planar structure after the guidewire has been withdrawn from the branch vessel.

[0039] Figure 16 A side view of the auxiliary support structure provided in the first embodiment;

[0040] Figure 17 for Figure 16 A top view of the auxiliary support structure shown;

[0041] Figure 18 for Figure 17 A magnified structural diagram of point A in the auxiliary support shown;

[0042] Figure 19 A side view of the auxiliary support structure provided in the second embodiment;

[0043] Figure 20 A partial structural schematic diagram of the auxiliary support provided in the third embodiment;

[0044] Figure 21 A partial structural schematic diagram of the auxiliary support provided in the fourth embodiment;

[0045] Figure 22 A partial structural schematic diagram of the auxiliary support provided in the fifth embodiment;

[0046] Figure 23 A partial structural schematic diagram of the auxiliary support provided in the sixth embodiment;

[0047] Figure 24 A partial structural schematic diagram of the auxiliary support provided in the seventh embodiment;

[0048] Figure 25 for Figure 24 A side view of the auxiliary support structure shown;

[0049] Figure 26 A partial structural schematic diagram of the auxiliary support provided in the eighth embodiment;

[0050] Figure 27 A partial structural schematic diagram of the auxiliary support provided in the ninth embodiment;

[0051] Figure 28 A partial structural diagram of the auxiliary support provided for the tenth embodiment;

[0052] Figure 29 A partial structural diagram of the auxiliary support provided for Embodiment 11;

[0053] Figure 30 A partial structural diagram of the auxiliary support provided for the twelfth embodiment;

[0054] Figure 31 A partial structural diagram of the auxiliary support provided for Embodiment Thirteen;

[0055] Figure 32 A partial structural diagram of the auxiliary support provided for Embodiment Fourteen;

[0056] Figure 33 A partial structural diagram of the auxiliary support provided for Embodiment Fifteen;

[0057] Figure 34A partial structural diagram of the auxiliary support provided for Embodiment Sixteen;

[0058] Figure 35 A partial structural diagram of the auxiliary support provided for Embodiment Seventeen;

[0059] Figure 36 A partial structural diagram of the auxiliary support provided for Embodiment 18;

[0060] Figure 37 A side view of the structure of the drainage plate and auxiliary support after assembly for the nineteenth embodiment;

[0061] Figure 38 for Figure 37 A schematic diagram of the planar structure of the drainage plate. Detailed Implementation

[0062] To facilitate understanding of the present invention, a more complete description will be given below with reference to the accompanying drawings. Preferred embodiments of the invention are shown in the drawings. However, the invention can be implemented in many different forms and is not limited to the embodiments described herein. Rather, these embodiments are provided to provide a thorough and complete understanding of the disclosure of the invention.

[0063] It should be noted that when an element is referred to as being "fixed to" another element, it can be directly attached to the other element or there may be an intervening element. When an element is referred to as being "connected to" another element, it can be directly connected to the other element or there may be an intervening element. The terms "inner," "outer," "left," "right," and similar expressions used herein are for illustrative purposes only and do not represent the only possible implementation.

[0064] See Figure 1 and Figure 2This invention provides a luminal stent 10, which can be radially compressed under external force and radially expanded after the external force is removed. The luminal stent 10 can be implanted into a target lumen, the inner diameter of which is smaller than the outer diameter of the luminal stent 10. The ratio between the outer diameter of the luminal stent 10 in its naturally expanded state (i.e., its naturally expanded state without external force) and the inner diameter of the target lumen is 1 + C%, where C% is the stent magnification ratio (also known as the oversize value), and the value of C% ranges from 5% to 20%. After the luminal stent 10 is implanted into the target lumen, it generates a radial supporting force on the target lumen due to a certain degree of radial compression, thereby firmly anchoring itself in the target lumen. The target lumen can be a biological tissue lumen within a living organism, an artificial lumen implanted within a living organism, or an in vitro simulated lumen, etc. The target lumen of this invention is illustrated using the human aorta 20 as an example. The aorta 20 is connected to three branch vessels 31, which are located on the greater curvature side of the aorta 20. Blood flows from the aorta 20 to the branch vessels 31. An aneurysm 21 forms on the lesser curvature side of the aorta 20. By implanting a stent 10 into the aorta 20 to isolate the aneurysm 21, the blood flowing within the stent 10 cannot come into contact with the aneurysm 21, ultimately achieving the goal of treating the aneurysm 21. (See also...) Figure 13 , Figure 14 and Figure 15 A bridging stent 32 can also be implanted in each of the three branch vessels 31. This bridging stent 32 is connected to the luminal stent 10, allowing blood from the luminal stent 10 to enter the branch vessels 31 through the bridging stent 32. (See also...) Figure 3 The lumen stent 10 includes a main stent 100 and an auxiliary stent 300.

[0065] See Figure 3 , Figure 4 and Figure 5 The main support 100 is a tubular structure, such as a circular tube. The lumen of the main support 100 is used to transport blood, and the blood flows within the lumen. A side surface 110 of the main support 100 is recessed towards its central axis to form a recessed section. For example, a groove 120 is formed on the side surface 110 of the main support 100, which is recessed to a predetermined depth from the side surface 110 towards the central axis of the main support 100. In other embodiments, the recessed section may be an annular recessed region surrounding the main support 100.

[0066] See Figure 3 , Figure 4 and Figure 5The main stent 100 includes a covering 130, a closed-loop coil 140, and an open-loop coil 150. The covering 130 is made of a biocompatible thin-film material (e.g., PET, PTFE) and is used to cover the closed-loop coil 140 and the open-loop coil 150. Both the closed-loop coil 140 and the open-loop coil 150 can be made of materials such as nickel-titanium alloy or stainless steel, giving them good biocompatibility and elasticity. Therefore, when a radial force is applied to the main stent 100, the main stent 100 can undergo elastic deformation, causing a change in its outer diameter. For example, in its naturally deployed state, the outer diameter of the main stent 100 is at its maximum; when the main stent 100 is inserted into the sheath for subsequent infusion into the aorta 20, the outer diameter of the main stent 100 decreases due to compression; when the main stent 100 leaves the sheath and deploys at the implantation site in the aorta 20, the outer diameter of the main stent 100 increases.

[0067] See Figure 3 , Figure 6 and Figure 7 The closed-loop waveform 140 is a circumferentially closed circular structure. The closed-loop waveform 140 can be formed by connecting multiple metal wave rods 160 end-to-end. Therefore, the closed-loop waveform 140 forms a peak or trough at the connection point of two adjacent wave rods 160. The closed-loop waveforms 140 are located on opposite sides of the groove 120 along the axial direction of the entire main support 100. For example, there are two spaced-apart closed-loop waveforms 140 on one side near the end of the groove 120, and similarly, two spaced-apart closed-loop waveforms 140 on the other side far from the end of the groove 120. (See reference...) Figure 3 , Figure 8 and Figure 9 The open-loop wavering 150 corresponds exactly to the groove 120. It can be understood that the radial projection of the open-loop wavering 150 along the main support 100 covers the groove 120. The open-loop wavering 150 is a circumferentially non-closed arc structure, and it is also formed by multiple metal wave rods 160 connected end-to-end. The connection point of two adjacent wave rods 160 forms a crest or trough. The two ends of the open-loop wavering 150 are not connected but are spaced apart by a certain distance, forming an opening 151 between the two ends. This opening 151 corresponds to the groove 120, so the open-loop wavering 150 is located between the closed-loop waverings 140 at both ends of the groove 120. Alternatively, the main support 100 may also include a connecting rod, which is a straight line connected to both ends of the open-loop wavering 150, so that the connecting rod closes the opening 151 of the open-loop wavering 150, thus forming a closed-loop structure with the connecting rod. To prevent the end of the open-loop coil 150 from piercing the coating 130 and causing damage, the open-loop coil 150 includes a passivation structure 152 located at the end. The passivation structure 152 can be a two-dimensional circular structure, an arc-shaped structure, or a three-dimensional spherical structure, etc.

[0068] See Figure 10 , Figure 11 and Figure 12 The membrane 130 of the main support 100 forms a tubular structure with openings at both ends and a groove 120 in the middle. The groove 120 includes a bottom wall surface 123 and a first side wall surface 121 and a second side wall surface 122 surrounding the bottom wall surface 123. Along the recessed direction of the groove 120, which can also be understood as a direction perpendicular to the bottom wall surface 123, the bottom wall surface 123 is closer to the central axis of the main support 100 than the first side wall surface 121 and the second side wall surface 122. There are two of each of the first side wall surface 121 and the second side wall surface 122, and they are connected to the edge of the bottom wall surface 123. The two first side wall surfaces 121 are spaced apart along the axial direction of the main support 100, and the two second side wall surfaces 122 are spaced apart along the axial direction perpendicular to the main support 100, so that the first side wall surfaces 121 and the second side wall surfaces 122 can be perpendicular to each other. A window 124 is provided on the first side wall 121 and / or the bottom wall 123, the window 124 connecting the groove 120 and the cavity of the main support 100. (See reference...) Figure 13 and Figure 14 After the main stent 100 is implanted into the aorta 20, the groove 120 corresponds to the branch vessel 31. When the bridging stent 32 is implanted into the branch vessel 31, the bridging stent 32 will extend into the lumen of the main stent 100 through the groove 120 and cooperate with the window 124, so that the blood in the lumen of the main stent 100 flows into the branch vessel 31 through the bridging stent 32.

[0069] See Figure 3 , Figure 4 and Figure 5The auxiliary stent 300 has a roughly arc-shaped structure and is made of metal. It mates with the groove 120 of the main stent 100. The auxiliary stent 300 includes a mesh structure with multiple mesh openings 300a communicating with the outside. The auxiliary stent 300 can elastically deform to change its cross-sectional dimensions. When the bridging stent 32 needs to be implanted, the guidewire 40 is first passed through the branch vessel 31 and sequentially through the mesh openings 300a and groove 120 of the auxiliary stent 300 into the window 124. Then, the bridging stent 3 is implanted along the guidewire path formed by the guidewire 40. During this process, because the guidewire 40 passes through the auxiliary stent 300, and the auxiliary stent 300 can restrict the range of motion of the guidewire 40, the risk of the guidewire 40 dislodging from the groove 120 is reduced to a certain extent, thereby improving the implantation efficiency and accuracy of the bridging stent 32. Furthermore, by setting up the auxiliary stent 300, the supporting effect of the auxiliary stent 300 ensures that there is a certain gap space in the groove 120, effectively preventing the bottom wall surface 123 from being tightly attached to the entrance of the branch vessel 31. After the main stent 100 is implanted and before the bridging stent 32 is implanted, it ensures that the blood in the aorta 20 enters the branch vessel 31 through the window 124 and the groove 120 in sequence, and provides a stable and suitable operating space for the guide wire 40 and the bridging stent 32 to enter.

[0070] To further reduce the risk of guidewire 40 dislodging from groove 120, auxiliary stent 300 includes a deformable constraint hole. When the lumen stent 10 is implanted into the target lumen (i.e., when the lumen stent 10 is radially compressed to an outer diameter equal to the inner diameter of the target lumen), the constraint hole can deform under external force to allow guidewire 40 to be inserted, and constrains the guidewire 40 after insertion.

[0071] For example, the auxiliary stent 300 has one or more deformable mesh openings 300a, which can serve as constraint holes. When the lumen stent 10 is implanted into the target lumen, the diameter D1 of the largest inner circle of the mesh opening 300a is smaller than the outer diameter D0 of the guide wire 40. At this time, when the guide wire 40 overcomes the elasticity of the auxiliary stent 300 and passes through the mesh opening 300a, it can be figuratively understood that the mesh opening 300a will form an interference fit with the guide wire 40, so that the auxiliary stent 300 can apply a clamping force to the guide wire 40 passing through the mesh opening 300a, thereby constraining the guide wire 40.

[0072] There are several methods to verify whether the diameter D1 of the maximum inner circle of the mesh 300a is smaller than the outer diameter D0 of the guidewire 40 after the stent 10 is implanted into the target lumen. The following test example can be used as a reference:

[0073] Test Example 1: A transparent test lumen is provided to simulate the target lumen. The inner diameter of this test lumen is within the diameter range of the target lumen specified in the product manual of the stent 10 (e.g., the recommended target vessel diameter range). The stent 10 to be tested is implanted into the test lumen, and an iso-dimensional profile of the mesh 300a to be tested on the stent 10 is acquired using an image acquisition device. The diameter D1 of the largest circle that can be accommodated in the iso-dimensional profile of the mesh 300a to be tested is obtained through mathematical calculation or measurement. Then, the outer diameter D0 of the guidewire 40 is measured using calipers or other measuring tools. Comparing the size relationship between D1 and D0 verifies whether the diameter D1 of the largest inner circle of the mesh 300a is smaller than the outer diameter D0 of the guidewire 40 after the stent 10 is implanted into the target lumen.

[0074] Test Example 2: A transparent test lumen is provided to simulate the target lumen. The inner diameter of this test lumen is within the diameter range of the target lumen specified in the product manual of the stent 10 (e.g., the recommended target blood vessel diameter range), and the sidewall of the test lumen has a test hole or test groove through which the guidewire 40 can pass. The stent 10 to be tested is implanted into the test lumen, and the mesh 300a to be tested on the stent 10 is aligned with the test hole or test groove to avoid obstruction of the mesh 300a to be tested by the test lumen. The test guidewire 40 (or a test rod with the same outer diameter as the guidewire 40) is inserted into the mesh 300a to be tested through the test hole or test groove. If the guide wire 40 can pass through the mesh 300a without causing deformation, then the diameter D1 of the largest inner circle of the mesh 300a is considered to be greater than or equal to the outer diameter D0 of the guide wire 40; if the guide wire 40 inevitably causes deformation of the mesh 300a when passing through it, then the diameter D1 of the largest inner circle of the mesh 300a is considered to be less than the outer diameter D0 of the guide wire 40.

[0075] Test Example 3: When the stent 10 under test is in its naturally expanded state, an iso-dimensional contour map of the mesh 300a to be tested on the stent 10 is acquired using an image acquisition device. Then, the diameter D2 of the largest circle that can be accommodated in the iso-dimensional contour map of the mesh 300a is obtained through mathematical calculation or measurement. It is known that the ratio between the maximum outer diameter of the stent 10 in its naturally expanded state (i.e., its natural expansion state without external force) and the maximum inner diameter of the target lumen is 1+C%, where C% is the stent magnification (also known as the oversize value), and the value of C% ranges from 5% to 20%. If D2 / D0 < 1+C%, it is considered that after the stent 10 is implanted into the target lumen, the diameter D1 of the largest inner circle of the mesh 300a is smaller than the outer diameter D0 of the guidewire 40. It should be noted that this method is only applicable to mesh 300a whose mesh size (or mesh aperture) decreases with the radial compression of the lumen support 10. For mesh 300a whose mesh size does not decrease synchronously with the radial compression of the lumen support 10, other suitable test methods can be selected.

[0076] To further ensure that the deformable mesh 300a exerts a stronger restraining force on the guide wire 40 inserted therein, the diameter D2 of the largest inner circle of the mesh 300a can be smaller than the outer diameter D0 of the guide wire 40 when the lumen stent 10 is in its naturally unfolded state. In this way, after the entire lumen stent 10 is implanted into the target lumen, the lumen stent 10 will undergo a certain degree of radial contraction, which reduces the diameter of the mesh 300a. Consequently, the diameter of the largest inner circle in the mesh 300a also decreases further, thereby enabling the auxiliary stent 300 to apply a greater clamping force to the guide wire 40 inserted in the mesh 300a.

[0077] The following describes several embodiments of the auxiliary support 300:

[0078] First Embodiment

[0079] See Figure 16 , Figure 17 and Figure 18The auxiliary support 301 is a circumferentially closed structure. Specifically, the auxiliary support 301 includes an auxiliary support body 301b, the outer surface of which forms a circumferentially closed structure, and mesh 301a is formed on the auxiliary support body 301b. There is only one auxiliary support body 301b, meaning the auxiliary support 301 is a single-layer structure. The outer surface of the auxiliary support body 301b includes a cylindrical surface 301c, a plane 301e, and an arc-shaped surface 301d. There is one cylindrical surface 301c and one plane 301e, and two arc-shaped surfaces 301d. The cylindrical surface 301c can be a cylindrical surface, and the arc-shaped surface 301d can be an arc surface. One arc-shaped surface 301d connects one end of the cylindrical surface 301c and the plane 301e, and the other arc-shaped surface 301d connects the other end of the cylindrical surface 301c and the plane 301e. The connection between the curved surface 301d and the cylindrical surface 301c and the plane 301e is smooth. This can be understood as the tangent plane 301e at one end of the curved surface 301d coinciding with the tangent plane 301e at the other end of the curved surface 301d coinciding with the plane 301e. (See also...) Figure 10 The plane 301e is adapted to the shape of the bottom wall surface 123 of the main support 100, and the arc-shaped surface 301d is adapted to the shape of the second side wall surface 122 of the main support 100. After the auxiliary support 301 is assembled with the main support 100, the plane 301e contacts the bottom wall surface 123 of the main support 100, the arc-shaped surface 301d contacts the second side wall surface 122 of the main support 100, and the cylindrical surface 301c smoothly transitions to the side surface 110 of the main support 100 at their joint, that is, the tangent plane 301e of the cylindrical surface 301c and the side surface 110 coincide at their joint. At least one of the arc-shaped surface 301d and the plane 301e forms a connection relationship with the main support 100, thereby fixing the auxiliary support 301 to the main support 100. The cylindrical surface 301c can support the wall of the target lumen and constrain the guide wire 40, while the planar surface 301e helps to stabilize the shape of the bottom wall surface 123 and prevent the bottom wall surface 123 from deforming after the lumen stent 10 is implanted into the target lumen.

[0080] The auxiliary support 301b is formed in two parts, including a first braided wire 301f and a second braided wire 301g. The first braided wire 301f and the second braided wire 301g are interwoven to form a plurality of quadrilateral mesh openings 301a, which are circumferentially closed structures. The first braided wire 301f and the second braided wire 301g are not fixedly connected at the intersection, allowing relative movement at the intersection, thus the formed mesh openings 301a can deform. In addition, in this embodiment, the same first braided wire 301f is located on the same side of the second braided wire 301g at the intersection, for example, the same first braided wire 301f is located inside or outside the second braided wire 301g at the intersection. One or more mesh openings 301a formed in this way can serve as constraint holes, which have better deformation capabilities and are more conducive to the entry of guide wire 40. After the guide wire 40 is inserted, it can constrain the guide wire 40 from multiple directions. In addition, after the bridging stent 32 is implanted, the first braided wire 301f and the second braided wire 301g exert a more uniform and appropriate constraint force on the bridging stent 32, avoiding excessive constraint force from damaging the bridging stent 32.

[0081] Of course, the auxiliary support 301b can also be processed into the tubular substrate by cutting to form the aforementioned mesh 301a, so that the processed auxiliary support 301b also includes multiple intersecting mesh ribs. Alternatively, some areas of the auxiliary support 301b may have mesh 301a formed by cutting, while other areas may have mesh 301a formed by weaving.

[0082] Second Embodiment

[0083] See Figure 19The main difference between the auxiliary support 302 of the second embodiment and the auxiliary support 301 of the first embodiment is that the auxiliary support 302 is a circumferentially non-closed structure. The auxiliary support 302 includes an auxiliary support body 302b, which has a notch 302e in the circumferential direction. The length of the notch 302e in the axial direction of the auxiliary support body 302b is less than or equal to the total length of the auxiliary support body 302b; in simpler terms, the length of the notch 302e is equal to the length of the auxiliary support body 302b. Specifically, the outer surface of the auxiliary support body 302b includes a cylindrical surface 302c and an arcuate surface 302d, but does not have a plane. There is one cylindrical surface 302c and two arcuate surfaces 302d. Both ends of the cylindrical surface 302c are connected to the arcuate surfaces 302d. The arcuate surfaces 302d and the cylindrical surface 302c transition smoothly at the connection point. The arcuate surface 302d is adapted to the shape of the second side wall 122 of the main support 100. After the auxiliary bracket 302 is assembled with the main bracket 100, the arc-shaped surface 302d contacts and is fixedly connected to the second side wall surface 122 of the main bracket 100, so that the notch 302e is hidden in the groove 120, and the cylindrical surface 302c smoothly transitions to the side surface 110 of the main bracket 100 at the joint. Other similarities are described in the relevant description in the first embodiment.

[0084] The non-enclosed auxiliary support 302 in this embodiment helps to reduce the radial compression dimension of the lumen support 10 and improve the bending performance of the lumen support 10.

[0085] Third Embodiment

[0086] See Figure 20 The main difference between the auxiliary stent 303 of the third embodiment and the auxiliary stent 302 of the first embodiment is that all the meshes 303a are circumferentially non-closed structures, that is, the meshes 303a have openings 303b in the circumferential direction. These openings 303b connect with other adjacent meshes 303a to form a constraint hole. When the auxiliary stent 303 is in its naturally unfolded state, the width of the opening 303b is smaller than the outer diameter of the guide wire 40. Therefore, for the guide wire 40 inserted in one of the meshes 303a, the guide wire 40 cannot slide into the adjacent mesh 303a through the opening 303b. Furthermore, after the entire lumen stent 10 is implanted, the auxiliary stent 303 contracts relatively, the width of the opening 303b becomes smaller, while the outer diameter of the guide wire 40 remains constant, making it even more impossible for the guide wire 40 to slide from one mesh 303a to another through the opening 303b. The auxiliary stent 303 ensures proper positioning of the guidewire 40, effectively preventing the guidewire 40 from dislodging from the groove 120 and improving the implantation efficiency and accuracy of the bridging stent 32. For other similarities, please refer to the relevant description in the first embodiment.

[0087] Fourth embodiment

[0088] See Figure 21 The main difference between the auxiliary support 304 in the fourth embodiment and the auxiliary support 303 in the third embodiment is that some mesh openings 304a are circumferentially open structures and can be used as constraint holes, while the remaining mesh openings 304a are circumferentially closed structures. In other words, all mesh openings 304a are divided into two parts, one part being circumferentially open structures and the other part being circumferentially closed structures. Of course, the number of circumferentially closed mesh openings 304a can be greater than the number of circumferentially open mesh openings 304a, or the number of circumferentially closed mesh openings 304a can be less than or equal to the number of circumferentially open mesh openings 304a.

[0089] Fifth Embodiment

[0090] See Figure 22 The main difference between the auxiliary support 305 of the fifth embodiment and the auxiliary support 303 of the third embodiment is that the auxiliary support 305 further includes a barrier strip 305c. The barrier strip 305c is located in the opening 305b to separate two adjacent mesh holes 305a, and the two mesh holes 305a can each serve as constraint holes. Specifically, the barrier strip 305c is elastic and can elastically stretch and deform along its own length. For example, the barrier strip 305c can be made of materials such as silicone, PET, or PTFE, and both ends of the barrier strip 305c can be fixed to the auxiliary support 301b by sewing or heat fusion, so that the barrier strip 305c spans across the opening 305b, thereby blocking the opening 305b and ultimately isolating the two mesh holes 305a that are interconnected through the opening 305b. Therefore, when the guide wire 40 is inserted into one of the mesh openings 305a, due to the limiting effect of the barrier head, the guide wire 40 will not be able to enter into the other mesh opening 305a, further improving the positioning function of the auxiliary support 305 for the guide wire 40. Furthermore, the elastic barrier strip 305c helps limit the deformation range of the mesh opening 305a. After deformation, it helps the mesh opening 305a to recover its shape, thus assisting the mesh opening 305a in forming a more effective constraint on the guide wire 40 after it is inserted.

[0091] Sixth Embodiment

[0092] See Figure 23The main difference between the auxiliary support 306 of the sixth embodiment and the auxiliary support 301 of the first embodiment is that the same first braided wire 306f is not located on the same side of the second braided wire 306g at the intersection. Specifically, using a plain weave, the same first braided wire 306f alternately lies on opposite sides of the second braided wire 306g at the intersection. For example, for multiple intersections arranged sequentially along the extension direction of the first braided wire 306f, the first braided wire 306f is located outside the second braided wire 306g at the first intersection, inside the second braided wire 306g at the second intersection, outside the second braided wire 306g at the third intersection, inside the second braided wire 306g at the fourth intersection, and so on. In other embodiments, a twill weave can also be used to form the mesh 306a.

[0093] The above weaving method not only allows the mesh 301a to deform, but also provides stronger constraint on the guide wire 40.

[0094] Seventh Embodiment

[0095] See Figure 24 and Figure 25 The main difference between the auxiliary support 307 of the seventh embodiment and the auxiliary support 301 of the first embodiment is that the number of auxiliary support bodies 307b is multiple, that is, the auxiliary support 307 has a multi-layer structure. Specifically, multiple auxiliary support bodies 307b are stacked on top of each other in a direction perpendicular to their own axial direction. The outermost auxiliary support body 307b is designated as the outer auxiliary support body 307b1, and an outer perforation 307a1 is formed on the outer auxiliary support body 307b1. The other auxiliary support bodies 307b are designated as the inner auxiliary support bodies 307b2, and an inner perforation 307a2 is formed on the inner auxiliary support body 307b2. The mesh 307a includes an outer perforation 307a1 and an inner perforation 307a2, that is, the outer perforation 307a1 and the inner perforation 307a2 used for passing through the same guide wire 40 form the mesh 307a.

[0096] At least one of the external perforation 307a1 and the internal perforation 307a2 can serve as a constraint hole. When the lumen stent 10 is implanted into the target lumen, the diameter of the largest inner circle of at least one of the external perforation 307a1 and the internal perforation 307a2 is smaller than the outer diameter of the guidewire 40. Alternatively, further, when the lumen stent 10 is in its naturally deployed state, the diameter of the largest inner circle of at least one of the external perforation 307a1 and the internal perforation 307a2 is smaller than the outer diameter of the guidewire 40. For example, when the lumen stent 10 is implanted into the target lumen, the diameter of the largest inner circle of the internal perforation 307a2 is smaller than the outer diameter of the guidewire 40, while the diameter of the largest inner circle of the external perforation 307a1 is greater than or equal to the outer diameter of the guidewire 40. Alternatively, when the lumen stent 10 is in its naturally deployed state, the diameter of the largest inner circle of the internal perforation 307a2 is smaller than the outer diameter of the guidewire 40, while the diameter of the largest inner circle of the external perforation 307a1 is greater than or equal to the outer diameter of the guidewire 40. The advantage of this design is that after the stent 10 is implanted, the inner auxiliary support 307b2 will clamp the guide wire 40, which is inserted through the inner perforation 307a2, thus providing good positioning for the guide wire 40 and effectively preventing it from coming out of the groove 120. This improves the implantation efficiency and accuracy of the bridging stent 32 and enhances the overall ease of use of the stent 10. Simultaneously, given that the mesh size of the outer perforation 307a1 is larger than that of the inner perforation 307a2, the guide wire 40 can more easily enter the outer perforation 307a1. Guided by the outer perforation 307a1, the guide wire 40 will quickly pass through the entire mesh 307a in a short time, further improving the implantation efficiency of the bridging stent 32. The maximum inner circle 307d1 of the outer perforation 307a1 and the maximum inner circle 307d2 of the inner perforation 307a2 are coaxially arranged. The spacing B between two adjacent auxiliary support layers 307b is smaller than the outer diameter of the guide wire 40. This effectively prevents the guide wire 40 from entering the gap 307e between the two adjacent auxiliary support layers 307b during the insertion process, ensuring that the guide wire 40 is quickly and accurately inserted into the mesh 307a. Each auxiliary support layer 307b is manufactured relatively independently and stacked to form the auxiliary support 307, making the auxiliary support 307 a modular connection structure.

[0097] Eighth embodiment

[0098] See Figure 26The main difference between the auxiliary support 308 of the eighth embodiment and the auxiliary support 307 of the seventh embodiment is that the maximum inner circle of the outer perforation 308a1 and the maximum inner circle of the inner perforation 308a2 are not coaxial. For example, the central axis of the maximum inner circle 308d1 of the outer perforation 308a1 and the central axis of the maximum inner circle 308d2 of the inner perforation 308a2 are parallel, or they are skewed. Because the maximum inner circle of the outer perforation 308a1 and the maximum inner circle of the inner perforation 308a2 are not coaxial, when the guide wire 40 passes through the outer perforation 308a1 and the inner perforation 308a2, it is beneficial for the auxiliary support 307 to constrain the guide wire 40 in multiple directions.

[0099] Ninth Embodiment

[0100] See Figure 27 The main difference between the auxiliary support 309 of the ninth embodiment and the auxiliary support 307 of the seventh embodiment is that the auxiliary support 309 further includes a filler strip 309c, which is fixed in the gap 309d between two adjacent auxiliary supports 309b. For example, the filler strip 309c extends along a direction perpendicular to the gap between two adjacent auxiliary supports 309b, and can fill the entire gap 309d, thereby filling the entire gap 309d and ultimately eliminating its existence. Specifically, the filler strip 309c is elastic; for example, it can be made of materials such as silicone, PET, or PTFE, and can be fixed to the auxiliary support 309b by sewing or heat fusion. Since the filler strip 309c can fill and eliminate the gap 309d, it further prevents the guide wire 40 from entering the gap 309d, ensuring that the guide wire 40 is quickly and accurately threaded through the mesh 309a. Furthermore, by incorporating a radiopaque element or doping it with a radiopaque material, the filler strip 309c can be made radiopaque, thereby enabling doctors to quickly identify the restraining mesh 309a during surgery and improving surgical efficiency.

[0101] Tenth Embodiment

[0102] See Figure 28The main difference between the auxiliary stent 310 of the tenth embodiment and the auxiliary stent 308 of the eighth embodiment is that the auxiliary stent 310 is an integrally connected structure made up of multiple auxiliary supports 310b. For example, the auxiliary stent 310 includes a three-dimensional mesh structure woven from multiple braided filaments using a three-dimensional braiding method. This three-dimensional mesh structure has multiple deformable internal perforations, which can be arranged coaxially or non-coaxially. One or more of the internal perforations form a guide wire channel, which connects the outside world to the window 124. One or more of the internal perforations can serve as constraint holes, allowing the guide wire channel to pass through the constraint holes, thereby constraining the guide wire after it has passed through the guide wire channel. When the lumen stent 10 is implanted into the target lumen or when the lumen stent 10 is in its naturally deployed state, at least one internal perforation in the guide wire channel can serve as a constraint hole, the diameter of which is smaller than the outer diameter of the guide wire 40, to improve the constraint ability of the auxiliary stent 310 on the guide wire 40. When the guidewire channel has multiple internal perforations, the guidewire 40 can be constrained in multiple directions within the guidewire channel.

[0103] Eleventh Embodiment

[0104] See Figure 29 The main difference between the auxiliary support 311 of the eleventh embodiment and the auxiliary support 310 of the tenth embodiment is that the auxiliary support 311 further includes a guide tube 311c. The guide tube 311c is a tubular structure and has elasticity. For example, the guide tube 311c can be made of materials such as silicone, PET, or PTFE, and can be fixed to the auxiliary support 311b by stitching or heat fusion. The guide tube 311c is inserted into the guide wire channel, for example, into the mesh 311a, which serves as a constraint hole. The lumen of the guide tube 311c is used to pass through the guide wire 40. By providing the guide tube 311c, the guide wire 40 can be inserted into the window 124 more quickly and accurately.

[0105] Twelfth Embodiment

[0106] See Figure 30The main difference between the auxiliary support 312 of the twelfth embodiment and the auxiliary support 301 of the first embodiment is that the auxiliary support 312 further includes a cover body 312c, which covers a portion of the mesh 312a to form a constraint hole. The cover body 312c is elastic; for example, it can be made of materials such as silicone, PET, or PTFE, and can be fixed to the auxiliary support body 312b by sewing or heat fusion. The cover body 312c can be a strip structure, spanning across the mesh 312a and fixed at both ends to the auxiliary support body 312b. The cover body 312c can also be a block structure, covering a portion of the mesh 312a. When the guide wire 40 is inserted into the mesh 312a, the auxiliary support body 312b and the cover body 312c together apply a clamping force to the guide wire 40. Therefore, by setting the cover body 312c, the diameter of the mesh 312a can be reasonably reduced, thereby improving the clamping force and positioning effect of the auxiliary stent 312 on the guide wire 40, and further improving the implantation efficiency and accuracy of the bridging stent 32. In addition, since the cover body 312c is elastic, after the bridging stent 32 is implanted, the cover body 312c can reduce the friction and cutting force of the auxiliary stent 312 on the outer surface of the bridging stent 32 caused by blood flow impact and vascular pulsation, reducing the probability of damage to the bridging stent 32.

[0107] Furthermore, by adding a developing element or doping a material with developing function into the masking body 312c, the masking body 312c can be made to have developing properties, thereby making it easier for doctors to quickly identify the restraining mesh 312a during surgery and improving surgical efficiency.

[0108] Thirteenth Embodiment

[0109] See Figure 31The main difference between the auxiliary stent 313 of the thirteenth embodiment and the auxiliary stent 301 of the first embodiment is that the auxiliary stent 313 also includes a guide strip 313c. The guide strip 313c is a strip-shaped structure and is fixed on the auxiliary support body 313b. The guide strip 313c of this strip-shaped structure can adhere to blood and also change the hemodynamics of the blood in the groove 120, thereby accelerating the formation of thrombus in all the blood in a short time, so that the thrombus quickly fills the groove 120, thereby sealing the groove 120. This is beneficial for providing support for the implanted bridging stent 32, preventing the bridging stent 32 from twisting and shifting, and also facilitating the rapid endothelialization of the lumen stent 10. The auxiliary support 313b has a lower end 313b2 and an upper end 313b1. A groove 120 is formed along the recessed direction of the side wall 110, which can also be understood as a direction perpendicular to the bottom wall surface 123. The lower end 313b2 of the auxiliary support 313b is closest to the central axis of the main support 100, and the upper end 313b1 is furthest from the central axis of the main support 100. The guide strip 313c can be made of an elastic material. One end of the guide strip 313c is a fixed end and fixed to the auxiliary support 313b near its upper end 313b1. The other end of the guide strip 313c is a free end that is not fixed and maintains a certain distance from the lower end 313b2 of the auxiliary support 313b. Alternatively, the other end of the guide strip 313c can also be a fixed end and maintain a distance from the lower end 313b2 of the auxiliary support 313b.

[0110] Fourteenth Embodiment

[0111] See Figure 32 The main difference between the auxiliary support 314 of the fourteenth embodiment and the auxiliary support 313 of the thirteenth embodiment is that one end of the fluid guide 314c is fixed and fixed to the lower end 314b2 of the auxiliary support 314b. Specifically, the other end of the fluid guide 314c is also fixed and fixed near the upper end 314b1 of the auxiliary support 314b.

[0112] Fifteenth Embodiment

[0113] See Figure 33The main difference between the auxiliary stent 315 of the fifteenth embodiment and the auxiliary stent 307 of the seventh embodiment is that the auxiliary stent 315 further includes a guide strip 315c. The guide strip 315c has a strip-shaped structure and is fixed to the auxiliary support 315b. This strip-shaped guide strip 315c can adhere to blood and also change the hemodynamics of the blood in the groove 120, thereby accelerating the formation of a thrombus within a short time. This allows the thrombus to quickly fill the groove 120, thus sealing the groove 120. The guide strip 315c can be made of an elastic material, and both ends of the guide strip 315c are fixed to two different auxiliary supports 315b. The guide strip 315c can extend along the interval between two adjacent auxiliary supports 315b.

[0114] Sixteenth Embodiment

[0115] See Figure 34 The main difference between the auxiliary stent 316 of the sixteenth embodiment and the auxiliary stent 310 of the tenth embodiment is that the auxiliary stent 316 further includes a guide strip 316c. The guide strip 316c is a strip-shaped structure and is fixed to the auxiliary support 316b. This strip-shaped guide strip 316c can adhere to blood and also change the hemodynamics of the blood in the groove 120, thereby accelerating the formation of a thrombus within a short time. This allows the thrombus to quickly fill the groove 120, thus sealing the groove 120. The guide strip 316c can be made of an elastic material, and both ends of the guide strip 316c are fixed to two different auxiliary supports 316b. The guide strip 316c can extend along the interval between two adjacent auxiliary supports 316b.

[0116] Seventeenth Embodiment

[0117] See Figure 35The main difference between the auxiliary stent 317 of the seventeenth embodiment and the auxiliary stent 301 of the first embodiment is that the auxiliary stent 317 further includes a guide strip 317c. The guide strip 317c is a strip-shaped structure and is fixed to the auxiliary support 317b. This strip-shaped guide strip 317c can adhere to blood and also change the hemodynamics of the blood in the groove 120, thereby accelerating the formation of a thrombus in a short time, allowing the thrombus to quickly fill the groove 120, thus sealing the groove 120. The guide strip 317c includes a main section 317c1 and branch sections 317c2. There is one main section 317c1 and multiple branch sections 317c2. The branch sections 317c2 are spaced apart along the length direction of the main section 317c1. One end of the branch section 317c2 is a fixed end and is fixedly connected to the main section 317c1, while the other end of the branch section 317c2 is a free end. One end of the main segment 317c1 is fixed to the auxiliary support, while the other end of the main segment 317c1 is a free end. Of course, the other end of the main segment 317c1 can also be a fixed end. By setting multiple branch segments 317c2 on the main segment 317c1, the entire guide strip 317c is made easier to adhere to blood, thereby promoting the formation of a thrombus within the groove 120.

[0118] Eighteenth Embodiment

[0119] See Figure 36 The main difference between the auxiliary support 318 of the eighteenth embodiment and the auxiliary support 317 of the seventeenth embodiment is that the guide strip 318c is wrapped around the auxiliary support 318b.

[0120] Nineteenth Embodiment

[0121] See Figure 37 and Figure 38The main difference between this nineteenth embodiment and any of the above embodiments is that the lumen support 10 further includes a drainage piece 200, which is a sheet-like structure and is housed in the groove 120. When the auxiliary support 300 is engaged with the groove 120, the drainage piece 200 will also be located in the cavity of the auxiliary support 300, so that the auxiliary support 300 can cover the drainage piece 200, that is, the auxiliary support 300 covers the drainage piece 200 in the groove 120. By setting the drainage patch 200, for the stent 10 implanted in the aorta 20, blood will enter the branch vessel 31 through the window 124 and the groove 120. After the bridging stent 32 is implanted into the branch vessel 31, blood will no longer be able to enter the groove 120 through the window 124, resulting in residual blood in the groove 120. At the same time, blood in the lumen of the main stent 100 may also enter the groove 120 through the permeation of the covering 130, so a certain amount of blood will accumulate in the groove 120. Due to the setting of the drainage patch 200, under the swing and drainage action of the drainage patch 200, the hemodynamics of the blood accumulated in the groove 120 changes. For example, the blood will generate eddies, thereby accelerating the formation of a thrombus in a short time, causing the thrombus to quickly fill the groove 120, thus sealing the groove 120.

[0122] Therefore, the drainage patch 200 serves two purposes: firstly, it prevents small thrombi from becoming suspended in a large amount of blood due to slow thrombus formation, thus avoiding the possibility of small thrombi forming earlier entering the branch vessel 31 through gaps between the bridging stent 32 and the inner wall of the branch vessel 31, and preventing serious complications such as organ ischemia or limb necrosis caused by thrombi entering the branch vessel 31, thereby improving the safety of the luminal stent 10. Secondly, it also prevents blood in the groove 120 from flowing into the aneurysm 21 through gaps between the main stent 100 and the inner wall of the aorta 20, thereby improving the healing speed of the aneurysm 21 and the safety of the luminal stent 10.

[0123] The drainage plate 200 is fixedly connected to at least one of the main support 100 and the auxiliary support 300. For example, the drainage plate 200 is fixedly connected only to the main support 100, so that the drainage plate 200 is attached to the main support 100 but exists independently of the auxiliary support 300. When the auxiliary support 300 is not engaged with the groove 120, the drainage plate 200 is fixedly connected to the main support 100, and not fixed to the auxiliary support 300. Alternatively, the drainage plate 200 is fixed only to the auxiliary support 300, so that the drainage plate 200 is attached to the auxiliary support 300 but exists independently of the main support 100. When the auxiliary support 300 is not engaged with the groove 120, the drainage plate 200 is fixed to the auxiliary support 300, and not fixed to the main support 100. Yet another example is that the drainage plate 200 is fixedly connected to both the main support 100 and the auxiliary support 300.

[0124] See Figure 14 , Figure 37 and Figure 38 The drainage patch 200 has a through hole 210. Both the mesh 300a and the through hole 210 can be used to cooperate with the guide wire 40, which is used to implant the bridging stent 32. During the implantation of the bridging stent 32, the guide wire 40 first passes through the branch vessel 31 and then sequentially passes through the mesh 300a, the through hole 210, and the window 124 to extend into the lumen of the main stent 100. Then, the sheath containing the bridging stent 32 is inserted through the guide wire 40 to the designated position, and the bridging stent 32 is released from the sheath. This allows the bridging stent 32 implanted in the branch vessel 31 to cooperate with the window 124 and extend into the lumen of the main stent 100, so that blood in the aorta 20 can enter the branch vessel 31 through the bridging stent 32. Finally, the guide wire 40 is withdrawn. The guide wire channel formed by the through hole 210 and the mesh 300a can effectively constrain the guide wire 40 inserted therein, effectively preventing the guide wire 40 from coming out of the groove 120, improving the implantation efficiency and accuracy of the bridging stent 32, and ultimately improving the ease of use of the lumen stent 10.

[0125] See Figure 37 and Figure 38The drainage patch 200 is made of a biocompatible thin film material (e.g., PET, PTFE, etc.) and includes an elastic portion, which can be made of silicone, metal, or other elastic materials. A through hole 210 is formed in this elastic portion. This through hole 210 serves as a constraint hole. When the stent 10 is implanted into the target lumen or when the stent 10 is in its naturally extended state, the diameter of the maximum inner circle 220 of the through hole 210 is smaller than the outer diameter of the guidewire 40. Therefore, after the entire stent 10 is implanted, the guidewire 40 needs to overcome the elastic force of the elastic portion and pass through the through hole 210. This can be visualized as the through hole 210 forming an interference fit with the guidewire 40, allowing the drainage patch 200 to apply a clamping force to the guidewire 40 passing through the through hole 210. The clamping force of the drainage plate 200 on the guide wire 40 further enhances the positioning of the guide wire 40, effectively preventing the guide wire 40 from falling out of the groove 120, improving the implantation efficiency and accuracy of the bridging stent 32, and ultimately improving the ease of use of the lumen stent 10.

[0126] It is understandable that if the through hole 210 can be used as a constraint hole, the mesh 300a can be used as a constraint hole, that is, it is not necessary to satisfy the condition that "when the lumen stent 10 is implanted into the target lumen or when the lumen stent 10 is in a naturally deployed state, the diameter D1 of the maximum inner circle of the mesh 300a is less than the outer diameter D0 of the guide wire 40"; of course, both the through hole 210 and the mesh 300a can be used as constraint holes.

[0127] The technical features of the above embodiments can be combined in any way. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0128] The embodiments described above are merely illustrative of several implementations of the present invention, and while the descriptions are relatively specific and detailed, they should not be construed as limiting the scope of the invention patent. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of the present invention, and these all fall within the protection scope of the present invention. Therefore, the protection scope of this invention patent should be determined by the appended claims.

Claims

1. A luminal stent for implantation into a target lumen, characterized in that, The device includes a main support and an auxiliary support. The side of the main support is recessed towards its central axis to form a recessed section. The auxiliary support has an arcuate structure and at least a portion of it forms a space between itself and the outer surface of the recessed section in the radial direction. The recessed section includes a groove, and the auxiliary support is at least partially housed in the groove. The membrane of the main support forms a cavity structure with open ends and a groove in the middle. The groove includes a bottom wall and a first side wall and a second side wall surrounding the bottom wall. The two first side walls are spaced apart along the axial direction of the main support. A window is provided on the first side wall and / or the bottom wall, and the window communicates the groove and the cavity of the main support for cooperation with a bridging support. The auxiliary support includes a deformable constraint hole. When the cavity support is radially compressed to an outer diameter that is approximately equal to the inner diameter of the target cavity, the constraint hole allows the insertion of a guide wire, and the auxiliary support can apply a clamping force to the guide wire passing through the constraint hole. The ratio between the outer diameter of the lumen support in its naturally deployed state and the inner diameter of the target lumen is 1+C%, where C% is the support magnification ratio and the value of C% ranges from 5% to 20%. When the lumen support is radially compressed to the point where its outer diameter is approximately equal to the inner diameter of the target lumen, the maximum inner diameter D1 of the constraint hole is less than the outer diameter D0 of the guide wire.

2. The lumen stent according to claim 1, characterized in that, When the lumen support is in its naturally deployed state, the maximum inner diameter of the constraint hole is D2, D2 / D0≤1+C%, where C% is the support magnification; and / or, when the lumen support is in its naturally deployed state, D2 / D0≤1.

3. The lumen stent according to claim 1, characterized in that, The auxiliary support is a circumferentially closed tubular structure; or, the auxiliary support is a circumferentially non-closed structure with a notch, wherein the length occupied by the notch in the axial direction of the auxiliary support is less than or equal to the total length of the auxiliary support, and the notch is located in the groove.

4. The lumen stent according to claim 1, characterized in that, The auxiliary support includes a mesh structure, which includes multiple intersecting first braided wires and second braided wires, as well as deformable mesh holes woven from the first braided wires and second braided wires. The same first braided wire is located on the same side of the second braided wire at the intersection, or alternately located on opposite sides of the second braided wire. One or more mesh holes can serve as constraint holes.

5. The lumen stent according to claim 1, characterized in that, The constraint hole is circumferentially closed; or, the constraint hole is circumferentially open and has an opening, the width of which is smaller than the outer diameter of the guidewire when the lumen support is radially compressed to an outer diameter substantially equal to the inner diameter of the target lumen, or when the lumen support is in a naturally unfolded state.

6. The lumen stent according to claim 5, characterized in that, The auxiliary support includes an auxiliary support body and a barrier strip. The constraint hole is provided on the auxiliary support body and has an opening. The barrier strip can elastically expand and contract along its own length direction. The barrier strip is located in the opening and both ends are fixed to the auxiliary support body.

7. The lumen stent according to claim 1, characterized in that, The auxiliary support includes multiple auxiliary support bodies stacked in layers. The outermost auxiliary support body has an external through hole, and the other auxiliary support bodies have internal through holes. At least one of the external through holes and the internal through holes serves as a constraint hole.

8. The lumen stent according to claim 7, characterized in that, The inner perforation is a constraint hole. When the auxiliary support is in a naturally unfolded state, the maximum inner diameter of the outer perforation is greater than the maximum inner diameter of the inner perforation.

9. The lumen stent according to claim 7, characterized in that, The central axis of the largest inner circle of the outer perforation and the central axis of the largest inner circle of the inner perforation are coincident, parallel, and opposite to each other.

10. The lumen stent according to claim 7, characterized in that, The spacing between two adjacent auxiliary support layers is less than the outer diameter of the guide wire.

11. The lumen stent according to claim 1, characterized in that, The auxiliary support includes a three-dimensional mesh structure, in which a guide wire channel is provided that passes through the constraint hole.

12. The lumen stent according to claim 11, characterized in that, The auxiliary support also includes a guide tube, which is inserted into the guide wire channel, and the lumen of the guide tube is used to pass through the guide wire.

13. The lumen stent according to claim 7, characterized in that, The auxiliary support also includes an elastic filler strip, which is disposed in the gap between adjacent auxiliary support layers.

14. The lumen stent according to claim 1, characterized in that, The auxiliary support includes an auxiliary support body and a cover body connected to each other. The auxiliary support body is provided with mesh holes, and the cover body is elastic and covers a portion of the mesh holes to form a constraint hole. The auxiliary support body and the cover body are used together to apply a clamping force to the guide wire.

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