CN205515056U - Support - Google Patents
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- CN205515056U CN205515056U CN201620198527.4U CN201620198527U CN205515056U CN 205515056 U CN205515056 U CN 205515056U CN 201620198527 U CN201620198527 U CN 201620198527U CN 205515056 U CN205515056 U CN 205515056U
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- stent
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- proximal end
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- 238000009941 weaving Methods 0.000 claims abstract description 27
- 230000004323 axial length Effects 0.000 claims description 18
- 229910052751 metal Inorganic materials 0.000 claims description 18
- 239000002184 metal Substances 0.000 claims description 18
- 239000002131 composite material Substances 0.000 claims description 8
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 claims description 4
- 229910001080 W alloy Inorganic materials 0.000 claims description 3
- WAIPAZQMEIHHTJ-UHFFFAOYSA-N [Cr].[Co] Chemical class [Cr].[Co] WAIPAZQMEIHHTJ-UHFFFAOYSA-N 0.000 claims description 3
- 238000011161 development Methods 0.000 claims description 3
- 230000018109 developmental process Effects 0.000 claims description 3
- ZONODCCBXBRQEZ-UHFFFAOYSA-N platinum tungsten Chemical compound [W].[Pt] ZONODCCBXBRQEZ-UHFFFAOYSA-N 0.000 claims description 3
- 229910001220 stainless steel Inorganic materials 0.000 claims description 3
- RVTZCBVAJQQJTK-UHFFFAOYSA-N oxygen(2-);zirconium(4+) Chemical compound [O-2].[O-2].[Zr+4] RVTZCBVAJQQJTK-UHFFFAOYSA-N 0.000 claims 1
- 206010002329 Aneurysm Diseases 0.000 abstract description 31
- 230000017531 blood circulation Effects 0.000 abstract description 12
- 210000001367 artery Anatomy 0.000 abstract description 5
- 230000008859 change Effects 0.000 abstract description 3
- 230000015572 biosynthetic process Effects 0.000 abstract description 2
- 230000001174 ascending effect Effects 0.000 abstract 1
- 238000009940 knitting Methods 0.000 description 22
- 210000004204 blood vessel Anatomy 0.000 description 13
- 239000000463 material Substances 0.000 description 5
- 238000013461 design Methods 0.000 description 4
- 238000000034 method Methods 0.000 description 4
- 230000002490 cerebral effect Effects 0.000 description 3
- 201000010099 disease Diseases 0.000 description 3
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 3
- 230000000004 hemodynamic effect Effects 0.000 description 3
- 230000003902 lesion Effects 0.000 description 3
- 238000012986 modification Methods 0.000 description 3
- 230000004048 modification Effects 0.000 description 3
- 230000002792 vascular Effects 0.000 description 3
- 201000008450 Intracranial aneurysm Diseases 0.000 description 2
- 230000010102 embolization Effects 0.000 description 2
- 210000002889 endothelial cell Anatomy 0.000 description 2
- 238000002513 implantation Methods 0.000 description 2
- 229910001000 nickel titanium Inorganic materials 0.000 description 2
- 238000012856 packing Methods 0.000 description 2
- 238000001356 surgical procedure Methods 0.000 description 2
- 238000002560 therapeutic procedure Methods 0.000 description 2
- 206010060965 Arterial stenosis Diseases 0.000 description 1
- 206010020772 Hypertension Diseases 0.000 description 1
- 206010028980 Neoplasm Diseases 0.000 description 1
- 229910000566 Platinum-iridium alloy Inorganic materials 0.000 description 1
- 208000002223 abdominal aortic aneurysm Diseases 0.000 description 1
- 210000003484 anatomy Anatomy 0.000 description 1
- 238000013459 approach Methods 0.000 description 1
- 230000000740 bleeding effect Effects 0.000 description 1
- 210000001627 cerebral artery Anatomy 0.000 description 1
- 238000007428 craniotomy Methods 0.000 description 1
- 230000003073 embolic effect Effects 0.000 description 1
- 230000035876 healing Effects 0.000 description 1
- 208000014674 injury Diseases 0.000 description 1
- 239000007788 liquid Substances 0.000 description 1
- 238000004519 manufacturing process Methods 0.000 description 1
- 229910052697 platinum Inorganic materials 0.000 description 1
- HWLDNSXPUQTBOD-UHFFFAOYSA-N platinum-iridium alloy Chemical class [Ir].[Pt] HWLDNSXPUQTBOD-UHFFFAOYSA-N 0.000 description 1
- 229920000642 polymer Polymers 0.000 description 1
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Abstract
The utility model discloses a support, support include the first portion and formed at the second portion of the at least one end of first portion, two contained angles of weaving silk formation in the axial that interlock each other in the first portion are greater than weave the contained angles that the silk formed in the second portion for two that interlock each other in the axial, weave the silk and be lighter than at the contained angle that forms that makes progress in week for two that interlock each other in the first portion weave the contained angle that the silk upwards formed in week in the second portion for two that interlock each other. Weave the silk at the mechanical properties of each section of axial and all ascending contained angles adjustment support through what first portion and second portion were woven in the change, the blood flow flow direction in improving the aneurysm when realizing that the blood flow direction is rebuild, satisfies support to the demand of compliance and keep unobstructed by normal branch artery that support covered.
Description
Technical Field
The utility model relates to the technical field of medical equipment manufacture, especially, relate to a support.
Background
At present, the common diseases of blood vessels mainly include arterial stenosis, aneurysm and the like, and if the diseases are not treated in time, the blood vessels can be blocked, the tumor body can be ruptured, and the life safety of a patient can be seriously damaged.
Aneurysms are due to lesions or lesions of the arterial wall, manifested by localized or diffuse dilatation or bulging of the arterial vessel wall. Aneurysms grow continuously under the impact of blood flow, and when they rupture due to increased blood pressure or other factors, rapid bleeding occurs, with a very high mortality rate. Aneurysms can occur in different parts of the body, most commonly cerebral aneurysms and abdominal aortic aneurysms.
Aneurysms are commonly formed at the branch, bifurcation or bend of a blood vessel due to: based on the hemodynamic factors of the several parts, namely, the impact of axial blood flow on the far end of the blood vessel forms shear stress, the elastic layer of the blood vessel is damaged, the saccular protrusion is formed, and meanwhile, the shear stress stimulates and promotes the division and growth of damaged endothelial cells of the blood vessel, so that the endothelial cells grow into aneurysm, and therefore, the shear stress is the basic reason for the formation of the aneurysm.
The goal of treating aneurysms is to reduce the risk of aneurysm rupture, the most fundamental approach being to achieve healing of the parent artery to allow reconstruction of the arterial wall anatomy. Methods for treating aneurysms include the following:
1. Clamping aneurysm in surgical operation, and clamping the neck of the aneurysm with a metal clamp in craniotomy;
2. endovascular interventions, embolization of aneurysms with detachable coils (or micro-wire coils or other embolizing materials such as detachable balloons, curable liquids, etc.);
3. endovascular interventional therapy stent implantation.
The methods are mainly divided into surgical treatment and vascular intervention treatment, and because of the traumatic property, high risk and high complication of the surgical treatment, the intravascular intervention treatment gradually becomes a main method for treating the aneurysm, which is mainly benefited by the advantages that the intravascular intervention treatment has small trauma, few complications, high safety, little pain of patients, easy acceptance, short hospitalization time, high annual disease severity and tolerance and the like.
The removable spring coil embolization cavity is a percutaneous vascular puncture, and is introduced into a blood vessel through a microcatheter, and the metal spring coil is placed in the aneurysm to fill the aneurysm, so that the blood flow is prevented from flowing into the aneurysm. The design of the coil embolic material and microcatheter can reach aneurysmal lesions of tortuous complex cerebral arteries and stop the impact of blood flow by the packing of the aneurysm cavity, however such packing presents the risk of causing further enlargement and rupture of the aneurysm cavity.
Endovascular interventional therapy stenting is the implantation of vascular stents to treat and reconstruct the parent:
1) the stent can be compressed and loaded into the inner cavity of the micro-conveyor, and the compressed stent is soft enough to be conveyed to a target through tortuous, slender and complex cerebral vessels;
2) the stent has enough compliance after being implanted and conforms to tortuous cerebral vessels;
3) stents significantly affect the hemodynamics within the aneurysm while maintaining patency of the normal branch artery with the parent covered by the stent.
However, for the above-mentioned requirements, the existing stents still cannot fully satisfy, for example, the treatment of cerebral aneurysm, the requirement for softness of the stent is relatively high due to complicated anatomical shape tortuosity of cerebral vessels, and in order to satisfy the requirement for softness, a small amount of metal covering and open type meshes are adopted in stent design, but the mesh density of the stent is relatively low, and the neck of the aneurysm cannot be well covered, so that the stent cannot effectively change the hemodynamics in the aneurysm, and the stent has the problems of poor adherence, rupture in the lumen and the like at the position of a curved blood vessel. In view of the above-mentioned drawbacks of stents, there is a need to design more desirable stents.
SUMMERY OF THE UTILITY MODEL
An object of the utility model is to provide a support to solve in order to satisfy support compliance's demand, it is low for mesh density and metal coverage with the support design, can't cover aneurysm neck betterly, lead to the support can not fine realization blood flow direction problem of rebuilding.
In order to solve the technical problem, the utility model provides a support, the support includes:
a first portion; and
a second portion formed at least one end of the first portion;
the included angle formed by the two mutually staggered weaving wires in the first part in the axial direction is larger than the included angle formed by the two mutually staggered weaving wires in the second part in the axial direction, and the included angle formed by the two mutually staggered weaving wires in the first part in the circumferential direction is smaller than the included angle formed by the two mutually staggered weaving wires in the second part in the circumferential direction.
Optionally, in the stent, two interlaced knitting yarns in the first portion form included angles in the axial direction and the circumferential direction of 110 to 130 degrees and 50 to 70 degrees, respectively; the included angles formed by the two mutually staggered weaving yarns in the second part in the axial direction and the circumferential direction are respectively 60-90 degrees and 90-120 degrees.
Optionally, in the stent, the second portion is formed at a distal end of the first portion, and the stent further includes:
a third portion formed at a distal end of the second portion and/or a proximal end of the first portion.
Optionally, in the stent, the second portion is formed at a proximal end of the first portion, and the stent further includes:
a third portion formed at a proximal end of the second portion and/or a distal end of the first portion.
Optionally, in the stent, the second portion includes a first section and a second section, the first section is formed at a distal end of the first portion, the second section is formed at a proximal end of the first portion, and the stent further includes:
a third portion formed at a distal end of the first segment and/or a proximal end of the second segment.
Optionally, in the stent, the stent further includes a closed end formed at least one end of the plurality of interwoven braided wires.
Optionally, in the bracket, the axial length of the closed head end is 0.3mm to 1 mm.
Optionally, in the stent, the first portion and the second portion are both in a mesh tube shape, and are coaxial and have the same diameter.
Optionally, in the stent, the axial length of the first portion is greater than the axial length of the second portion.
Optionally, in the stent, the axial length of the second portion is 0.3mm to 1mm, and the axial length of the first portion is 2mm to 60 mm.
Optionally, in the stent, the third portion is in a shape of a mesh tube or a horn.
Optionally, in the stent, two interlaced knitting yarns in the third portion form included angles in the axial direction and the circumferential direction of 120 ° to 140 ° and 40 ° to 60 °, respectively.
Optionally, in the stent, the axial length of the third portion is 1mm to 5 mm.
Optionally, in the stent, the braided wire is a metal wire and/or a composite wire.
Optionally, in the stent, the metal wire is one or more of a nickel-titanium alloy wire, a platinum-tungsten alloy wire, a cobalt-chromium alloy wire, a platinum wire or a stainless steel wire.
Optionally, in the bracket, the composite wire includes a developing layer and a metal layer disposed outside the developing layer.
In the bracket provided by the utility model, the bracket comprises a first part and a second part formed at least one end of the first part, the included angle formed by the two interlaced knitting yarns in the first part in the axial direction is larger than the included angle formed by the two interlaced knitting yarns in the second part in the axial direction, the included angle formed by the two weaving wires which are staggered with each other in the first part in the circumferential direction is smaller than the included angle formed by the two weaving wires which are staggered with each other in the second part in the circumferential direction, so when the length of the diagonal line of the mesh holes of the stent in the circumferential direction is fixed, namely, when the diameter of the bracket is fixed and the number of the meshes on the circumference is fixed, if the angle of the corresponding axial direction in the meshes is larger, the smaller the mesh area, the greater the radial support of the stent, but the less compliant, and at the same time, the higher the density of the mesh and thus the higher the metal coverage. The angle of the axial direction in the meshes of the first part is larger than the corresponding angle in the meshes of the second part, so that the area of the meshes of the first part is smaller, the radial supporting force of the stent is larger, and meanwhile, the density of the meshes of the first part is higher than that of the meshes of the second part, so that the metal coverage rate of the first part is higher than that of the second part, the aneurysm neck is covered by the first part with higher density of the meshes, and the requirement of the stent on compliance is met by the second part with lower density of the meshes, and the smoothness of a normal branch artery covered by the stent is maintained. Therefore, the structure based on the stent provided by the application can remarkably improve the blood flow direction in the aneurysm, thereby realizing blood flow guiding reconstruction.
Drawings
Fig. 1a-1c are front views of a bracket according to an embodiment of the present invention, which is formed by a first part and a second part;
FIGS. 2a-2f are front views of the frame after forming a third portion and closing the head end based on the structure shown in FIG. 1 a;
FIGS. 3a-3f are front views of the frame after forming a third portion and closing the head end based on the structure shown in FIG. 1 b;
FIGS. 4a-4f are front views of the frame after forming a third portion and closing the head end based on the structure shown in FIG. 1 c;
fig. 5a is a front view of the stent after forming a third portion in a mesh tube shape based on the structure shown in fig. 1 c.
In the figure: a first portion 101; a second portion 102; a second partial first segment 102 a; a second partial second segment 102 b; a third portion 103; a closed head end 104; a distal end 30 of the first portion; the proximal end 40 of the first portion.
Detailed Description
The support proposed by the present invention will be described in further detail with reference to the accompanying drawings and specific embodiments. The advantages and features of the present invention will become more fully apparent from the following description and appended claims. It should be noted that the drawings are in simplified form and are not to precise scale, and are provided for convenience and clarity in order to facilitate the description of the embodiments of the present invention.
The core of the application lies in: the stent is divided into a first portion for covering the neck of the aneurysm and a second portion for supporting the blood vessel. Aiming at the different functions of the two parts, based on the principle that when the diagonal length of meshes of the stent in the circumferential direction is fixed (namely the stent has a certain diameter and the number of meshes in the circumferential direction is fixed), the larger the angle in the corresponding axial direction is, the smaller the mesh area is, the higher the density is, the higher the metal coverage rate is, the larger the radial supporting force is, and the poorer the flexibility is, the difference between the first part and the second part is designed in that an included angle formed by two weaving wires which are staggered with each other in the axial direction and an included angle formed by the two weaving wires which are staggered with each other in the circumferential direction are different during weaving, so that the first part can better cover the neck of the aneurysm, and the blood flow direction in the aneurysm is improved; the stiffness of the second portion is reduced to meet the compliance requirements of the stent.
As shown in fig. 1a-1c, the stent of the present invention is formed by interweaving a plurality of braided filaments, and mainly comprises a first portion 101 and a second portion 102 formed at the distal end 30 of the first portion 101 and/or the proximal end 40 of the first portion 101 (i.e. the second portion 102 is formed at least one end of the first portion 101); an included angle formed by the two mutually staggered knitting yarns in the first portion 101 in the axial direction is larger than an included angle formed by the two mutually staggered knitting yarns in the second portion 102 in the axial direction, and an included angle formed by the two mutually staggered knitting yarns in the first portion 101 in the circumferential direction is smaller than an included angle formed by the two mutually staggered knitting yarns in the second portion 102 in the circumferential direction. In this embodiment, the second portion 102 is formed by continuously knitting non-knitted yarns that form the rear edge of the first portion 101 with knitted yarns.
The first part 101 and the second part 102 are both in a net pipe shape, and are coaxial and have the same diameter, the axial length of the first part 101 is larger than that of the second part 102, and the axial length of the second part 102 is at least 1 mesh hole in the axial direction. Preferably, the axial length of the second part 102 is 0.3 mm-1 mm, the axial length of the first part 101 is 2 mm-60 mm, and the diameters of the first part 101 and the second part 102 are both 0.1-20 mm; the included angles formed by the two interlaced knitting yarns in the first part 101 in the axial direction and the circumferential direction are respectively 110-130 degrees and 50-70 degrees; the included angles formed by the two interlaced knitting yarns in the second part 102 in the axial direction and the circumferential direction are respectively 60 degrees to 90 degrees and 90 degrees to 120 degrees.
Specifically, the first portion 101 includes two ends, namely a proximal end 40 and a distal end 30 (the proximal end refers to an end close to the operator, and the distal end refers to an end far from the operator in this document), and different structures of the stent can be formed based on the second portion 102 disposed at different positions of the first portion 101, specifically as follows:
1A) as shown in fig. 1a, the second portion 102 is formed at the distal end 30 of the first portion 101, the second portion 102 is formed by adjusting nodes of a plurality of meshes formed by interweaving a plurality of knitting wires of the distal end 30 of the first portion 101 to vary in the axial direction and the circumferential direction, and the nodes of the plurality of meshes formed by interweaving a plurality of knitting wires to vary in the axial direction and the circumferential direction, so as to adjust the size of an included angle formed by two knitting wires which are interwoven in the axial direction and the circumferential direction, change the supporting force of the stent in the axial direction and the radial direction, and improve the flexibility and the metal coverage rate of the stent, so as to meet the requirements of actual conditions.
2A) As shown in fig. 1b, the second portion 102 is formed at the proximal end 40 of the first portion 101, and the second portion 102 is formed by adjusting the node of the plurality of meshes formed by the plurality of braided filaments of the proximal end 40 of the first portion 101 being alternately braided with each other in the axial and circumferential directions.
3A) As shown in fig. 1c, the second portion 102 includes a second portion first section 102a formed at the distal end 30 of the first portion 101 and a second portion second section 102b formed at the proximal end 40 of the first portion 101, that is, the first portion 101 is located between the second portion first section 102a and the second portion second section 102b, wherein the second portion first section 102a is formed by varying nodes of a plurality of meshes formed by interweaving a plurality of braided wires of the distal end 30 of the first portion 101 in the axial direction and the circumferential direction, and the second portion second section 102b is formed by varying nodes of a plurality of meshes formed by interweaving a plurality of braided wires of the proximal end 40 of the first portion 101 in the axial direction and the circumferential direction.
Referring to fig. 2a, in order to further improve the flexibility of the stent, the stent further comprises a third portion 103, wherein the mesh density of the third portion 103 is lower than that of the second portion 102, so as to improve the flexibility of the stent, and the stent can keep the lumen passage of the blood vessel following the circuitous blood vessel.
Preferably, the third portion 103 is in the shape of a mesh tube (as shown in fig. 5 a) or a trumpet (as shown in fig. 2a-2 c). Wherein the axial length of the third portion 103 is 1mm to 5 mm. When the third portion 103 is in the shape of a mesh tube, the third portion 103 is coaxial and co-axial (same diameter) with the first portion. The included angles formed by the two interlaced knitting yarns in the third part 103 in the axial direction and the circumferential direction are respectively 120-140 degrees and 40-60 degrees.
With reference to fig. 2b, in order to better fix the position of the stent during application, in the embodiment, the third portion 103 is designed to be in a horn shape, and assuming that the outer diameter of the straight portion of the first portion 101 is d, the difference between the minimum outer diameter and the maximum outer diameter of the horn shape is 1.5 d-2 d, so as to anchor the position of the stent in the blood vessel, so that the first portion 101 better fits the blood vessel wall.
For the position where the third portion 103 is formed to be woven based on the three stent structures formed by the first portion 101 and the second portion 102, there are several structures:
1B) based on case 1A above: referring to fig. 2a-2c, the third portion 103 may be formed by adjusting nodes of a plurality of meshes formed by interweaving a plurality of knitting filaments at the distal end of the second portion 102 and/or the proximal end 40 of the first portion 101, so as to vary in the axial direction and the circumferential direction, and preferably, two knitting filaments interweaved with each other in the third portion form included angles in the axial direction and the circumferential direction of 120 ° to 140 ° and 40 ° to 60 °, respectively.
2B) Based on the above case 2A: referring to fig. 3a-3c, the third portion 103 is formed by varying the nodes of the plurality of mesh openings formed by the interweaving of the plurality of braided filaments at the proximal end of the second portion 102 and/or the distal end 30 of the first portion 101 in the axial and circumferential directions.
3B) Based on the above case 3A: referring to fig. 4a-4c, the third portion 103 is formed by adjusting the node of the plurality of meshes formed by the interweaving of the plurality of braided filaments at the distal end of the second portion first section 102a and/or the proximal end of the second portion second section 102b to vary in the axial and circumferential directions.
In order to avoid this problem, the stent in this embodiment further includes a closed end formed at least one end of the plurality of braided wires that are woven in a staggered manner.
As shown in fig. 2d, the closed head end 104 is petal-shaped, the length of the closed head end 104 is at least 1 mesh opening in the axial direction, and preferably, the axial length of the closed head end 104 is 0.3mm to 1 mm.
For the specific weaving location of the closed end 104, based on the structure of the above-mentioned stent formed based on the first portion 101, the second portion 102 and the third portion 103, there are several structures:
1C) based on the above case 1B:
the closed head end is formed by interweaving a plurality of braided wires at a distal end of the second portion and/or a proximal end of the third portion with one another (not shown);
the closed head end is formed by interweaving a plurality of braided wires from a proximal end of the first portion and/or a distal end of the third portion with one another (not shown); or,
referring to fig. 2d-2f, the closed head end 104 is formed by interweaving a plurality of braided filaments formed at a distal end of the third portion 103 at a distal end of the second portion 102 and/or formed at a proximal end of the third portion 103 at a proximal end of the first portion 101.
2C) Based on the above case 2B:
the closed head end is formed by interweaving a plurality of braided wires from a proximal end of the second portion and/or a distal end of the third portion with one another (not shown);
the closed head end is formed by interweaving a plurality of braided filaments at a distal end of the first portion and/or a proximal end of the third portion with one another (not shown); or,
Referring to fig. 3d-3f, the closed head end 104 is formed by interweaving a plurality of braided filaments formed at a distal end of the third portion 103 at a distal end of the first portion 101 and/or formed at a proximal end of the third portion 103 at a proximal end of the second portion 102.
3C) Based on the above case 3B:
the closed head end is formed by interweaving a plurality of braided filaments at a distal end of the first segment of the second portion and/or at a proximal end of the third portion with one another (not shown);
the closed head end is formed by interweaving a plurality of braided filaments at a proximal end of the second section of the second portion and/or a distal end of the third portion (not shown); or,
referring to fig. 3d-3f, the closed head end 104 is formed by interweaving a plurality of braided filaments formed at a distal end of the third portion 103 at a distal end of the first segment 102a of the second portion and/or formed at a proximal end of the third portion 103 at a proximal end of the second segment 102b of the second portion.
Further, the number of the weaving wires is 8-108, preferably 24-96, and more preferably 32-72. The cross section of the knitting silk is rectangular, circular, trapezoidal or oval and the like. When the cross section of the weaving wire is circular, the diameter of the weaving wire is 0.01-0.2 mm, preferably 0.025-0.1 mm, and more preferably 0.03-0.08 mm. When the cross section of the weaving silk is rectangle, the length and width of the rectangle is 0.01-0.2 mm, preferably 0.025-0.1 mm, more preferably 0.03-0.08 mm, and the length-width ratio of the rectangle is 1: 1-4: 1.
In this embodiment, the woven wire is a metal wire and/or a composite wire. The material of the braided wire is selected from biocompatible metal and/or polymer. When the weaving wires are metal wires, specifically one or more of nickel-titanium alloy wires, platinum-tungsten alloy wires, cobalt-chromium alloy wires, platinum wires or stainless steel wires, in order to enable the stent to meet the requirement of development, developing wire materials are correspondingly woven in the process of weaving the stent, and the preferable developing wire materials are platinum-iridium alloy developing wires. When the weaving wire is a composite wire, the composite wire comprises a developing layer and a metal layer arranged on the outer side of the developing layer, and the bracket prepared by adopting the composite wire meets the requirement of the rigidity of the weaving wire of the bracket and also meets the requirement of developing.
In summary, in the stent provided by the present invention, the stent includes a first portion and a second portion formed at least one end of the first portion, an included angle formed by two knitting yarns interlaced with each other in the axial direction in the first portion is larger than an included angle formed by two knitting yarns interlaced with each other in the axial direction in the second portion, an included angle formed by two knitting yarns interlaced with each other in the circumferential direction in the first portion is smaller than an included angle formed by two knitting yarns interlaced with each other in the circumferential direction in the second portion, so that when a length of a diagonal line of a mesh of the stent in the circumferential direction is flexible, that is, when a diameter of the stent is constant and a number of meshes in the circumferential direction is constant, if an angle in the axial direction corresponding to each mesh in the mesh is larger, an area of the mesh is smaller, a radial supporting force of the stent is larger, but the radial supporting force is larger, but the mesh density is worse, and the mesh density is higher, and thus the higher the metal coverage. The angle of the axial direction in the meshes of the first part is larger than the corresponding angle in the meshes of the second part, so that the area of the meshes of the first part is smaller, the radial supporting force of the stent is larger, and meanwhile, the density of the meshes of the first part is higher than that of the meshes of the second part, so that the metal coverage rate of the first part is higher than that of the second part, the aneurysm neck is covered by the first part with higher density of the meshes, and the requirement of the stent on compliance is met by the second part with lower density of the meshes, and the smoothness of a normal branch artery covered by the stent is maintained. Therefore, the structure based on the stent provided by the application can remarkably improve the blood flow direction in the aneurysm, thereby realizing blood flow guiding reconstruction.
It will be apparent to those skilled in the art that various changes and modifications may be made to the present invention without departing from the spirit and scope of the invention. Thus, if such modifications and variations of the present invention fall within the scope of the claims and their equivalents, the present invention is also intended to include such modifications and variations.
Claims (16)
1. A stent is formed by interweaving and weaving a plurality of weaving wires, and is characterized by comprising:
a first portion; and
a second portion formed at least one end of the first portion;
the included angle formed by the two mutually staggered weaving wires in the first part in the axial direction is larger than the included angle formed by the two mutually staggered weaving wires in the second part in the axial direction, and the included angle formed by the two mutually staggered weaving wires in the first part in the circumferential direction is smaller than the included angle formed by the two mutually staggered weaving wires in the second part in the circumferential direction.
2. The stent of claim 1, wherein two interlaced braided filaments in the first portion form included angles in the axial and circumferential directions ranging from 110 ° to 130 ° and 50 ° to 70 °, respectively; the included angles formed by the two mutually staggered weaving yarns in the second part in the axial direction and the circumferential direction are respectively 60-90 degrees and 90-120 degrees.
3. The stent of claim 1, wherein the second portion is formed at a distal end of the first portion, the stent further comprising:
a third portion formed at a distal end of the second portion and/or a proximal end of the first portion.
4. The stent of claim 1, wherein the second portion is formed at a proximal end of the first portion, the stent further comprising:
a third portion formed at a proximal end of the second portion and/or a distal end of the first portion.
5. The stent of claim 1, wherein the second portion comprises a first section formed at a distal end of the first portion and a second section formed at a proximal end of the first portion, the stent further comprising:
a third portion formed at a distal end of the first segment and/or a proximal end of the second segment.
6. The stent of any one of claims 1-5, wherein the stent further comprises a closed head end formed at least one end of the plurality of interwoven braided wires.
7. The stent of claim 6, wherein the closed head end has an axial length of 0.3mm to 1 mm.
8. The stent of any one of claims 1-5, wherein the first portion and the second portion are both mesh-tubular shaped and coaxial and of the same diameter.
9. The stent of any one of claims 1-5, wherein an axial length of the first portion is greater than an axial length of the second portion.
10. The stent of claim 9, wherein the second portion has an axial length of 0.3mm to 1mm and the first portion has an axial length of 2mm to 60 mm.
11. The stent of any one of claims 3-5, wherein the third portion is in the shape of a mesh tube or a trumpet.
12. A stent according to any one of claims 3 to 5, wherein the two interlaced filaments in the third portion form angles in the axial and circumferential directions in the range of 120 ° to 140 ° and 40 ° to 60 °, respectively.
13. The stent of claim 11, wherein the third portion has an axial length of 1mm to 5 mm.
14. The stent of claim 1, wherein the braided wire is a metallic wire and/or a composite wire.
15. The stent of claim 14, wherein the wire is one or more of nitinol wire, platinum-tungsten alloy wire, cobalt-chromium alloy wire, platinum wire, or stainless steel wire.
16. The stent of claim 14, wherein the composite wire comprises a development layer and a metal layer disposed outside the development layer.
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| CN106491174A (en) * | 2016-12-20 | 2017-03-15 | 北京久事神康医疗科技有限公司 | A kind of callable blood flow guider |
| CN110236734A (en) * | 2019-07-17 | 2019-09-17 | 珠海通桥医疗科技有限公司 | The braided support that can be recycled completely |
| CN111134920A (en) * | 2020-01-22 | 2020-05-12 | 北京弘海微创科技有限公司 | Close net support |
| CN111249046A (en) * | 2020-01-22 | 2020-06-09 | 北京立德微创科技有限公司 | Close net support of lumen |
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| CN106491174A (en) * | 2016-12-20 | 2017-03-15 | 北京久事神康医疗科技有限公司 | A kind of callable blood flow guider |
| CN110236734A (en) * | 2019-07-17 | 2019-09-17 | 珠海通桥医疗科技有限公司 | The braided support that can be recycled completely |
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| CN111249046A (en) * | 2020-01-22 | 2020-06-09 | 北京立德微创科技有限公司 | Close net support of lumen |
| CN111249046B (en) * | 2020-01-22 | 2023-08-08 | 北京立德微创科技有限公司 | Lumen dense net support |
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| WO2022156095A1 (en) * | 2021-01-22 | 2022-07-28 | 广州易介医疗科技有限公司 | Novel pipeline embolization device |
| CN112914800A (en) * | 2021-01-22 | 2021-06-08 | 广州易介医疗科技有限公司 | Novel dense net support |
| CN113288535A (en) * | 2021-05-28 | 2021-08-24 | 成都百瑞恒通医疗科技有限公司 | Intracranial vascular stent |
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