WO2011110092A1 - Blood vessel stent facilitating to be compressed and grasped - Google Patents
Blood vessel stent facilitating to be compressed and grasped Download PDFInfo
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- WO2011110092A1 WO2011110092A1 PCT/CN2011/071663 CN2011071663W WO2011110092A1 WO 2011110092 A1 WO2011110092 A1 WO 2011110092A1 CN 2011071663 W CN2011071663 W CN 2011071663W WO 2011110092 A1 WO2011110092 A1 WO 2011110092A1
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- blood vessel
- stent
- axial support
- support rods
- vessel stent
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheets or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheets or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
Definitions
- the present invention relates to a blood vessel stent in a medical device, and more particularly to a blood vessel stent that facilitates crimping.
- BACKGROUND OF THE INVENTION Minimally invasive implantation of vascular stents is widely used as an effective intervention technique for the treatment of vascular stenosis.
- the tubular hollow stent is surgically placed to the affected part to effectively support the blood vessels, thereby functioning to clear the narrow blood vessels. And the surgery will not cause major trauma to the patient.
- materials that can be used to make vascular stents can be divided into two major categories: metal and medical polymer materials.
- Metal materials used for vascular stent processing mainly include 316L stainless steel, L605 cobalt chromium (CoCr) alloy, and magnesium alloy.
- vascular stents After a long period of clinical testing, the production and application of metal stents have become increasingly mature, and it is currently the main product of vascular stents, which is generally accepted by the majority of surgical operators and patients.
- studies have shown that long-term retention of metal stents in blood vessels can cause chronic damage to blood vessels, which can lead to atrophy of the middle vascular layer, aneurysm formation and reactive intimal hyperplasia, which ultimately leads to the occurrence of vascular restenosis (Rab ST, KiHgsB, Roubin GS, et al.
- vascular stents based on medical polymer materials are gradually emerging. These stents can support the vascular mechanical support during the specific time of injury healing, and can be used in lesions. After being healed, it is gradually absorbed by the body, which avoids the negative effects of metal stents due to long-term retention in the body.
- the materials that can be used to make biodegradable vascular stents are mainly polylactic acid (PLA) and L-polylactic acid.
- polyLlactic acid, PLLA or LPLA polyglycolic acid/polylactic acid
- PGLA polyglycolic acid/polylactic acid
- PCL polycaprolactone
- PHBV polyhydroxylbutyratevalerate
- PAGA poly Olysyl glutamic acid
- POE polyorthoesters
- PEO/PBTP polyethylene oxide/polybutylene terephthalate
- the cut vascular stent must have good biocompatibility. Adequate radial support and good compliance to meet the basic safety needs of long-term or longer-term support of vascular lesions.
- the graphic design of the vascular stent is also one of the key factors determining the quality of the finished product. The performance of the stent obtained by cutting the same tube with different graphic design is very different.
- the object of the present invention is to provide a blood vessel stent suitable for pressure grip, which is suitable for laser cutting processing of vascular stents of various metal materials and medical polymer materials.
- the blood vessel bracket provided by the utility model provides sufficient space for the pressure grip of the stent, and the possibility that the support ribs are touched together during the pressure grip is greatly reduced, and the drug coating can be effectively protected; the shape of the blood vessel stent is still very good after release. Regularity, the stent has a low shrinkage rate, good support and flexibility, and the "dog bone” effect is low. It can be widely applied to laser cutting of vascular stents of most polymer materials such as 316L stainless steel, L605 cobalt-chromium alloy and other polylactic acid (PLLA). This and other objects of the present invention will be further embodied and elucidated by the following detailed description and description.
- the vascular stent for facilitating the crimping is laser-cut from a tubular material, and the sinusoidal main body ribs (1) are arranged in parallel in a plurality of rows and are arranged in parallel by the axial support rods (3) at the apex of the sine wave peaks and troughs. (2) Connected together.
- the number of sine wave main ribs (1) can be added or deleted to adjust the length of the bracket, and the length of the main rib (1) of the sine wave is changed to adjust the outer diameter of the bracket.
- the sinusoidal main body ribs are composed of vertices and bending ribs, which can be closed and extended with the apex as a fixed point, which is advantageous for obtaining smaller diameter and uniform deformation when the bracket is bundled on the conveying system.
- the bending rib (4) yields in the shape of the sine wave (1) in the surrounding of the upper and lower axial support rods (3), and the adjacent basic unit bends.
- the bending direction of the ribs (4) is kept the same, ensuring that the connecting ribs are not due to no yielding position. The touch occurs to protect the drug coating.
- the present invention can be used for, but not limited to, the cutting of the following vascular stent tubes: metal materials such as 316L stainless steel, L605 cobalt chrome, and polylactic acid (PLLA), and mixtures, derivatives thereof and the like.
- metal materials such as 316L stainless steel, L605 cobalt chrome, and polylactic acid (PLLA), and mixtures, derivatives thereof and the like.
- the number of sine waves (1) or the number of (or) arrays or (and) the number of apex axial support rods (3) can be added or deleted according to the specific characteristics of the material metal bracket and the polymer cutting tube to obtain a series of different graphics.
- the vascular stent design graphic balances the flexibility and support of the stent.
- the beneficial effect of the blood vessel support for the pressure grip of the utility model is that it can adapt to the cutting of the blood vessel stent of most materials at present, and provides sufficient space for the pressure grip of the stent, and the possibility that the support ribs touch together when pressed Reduced, can effectively protect the drug coating; the shape of the stent is still very regular after release, the stent has a short shortening rate, good support and flexibility, and the "dog bone” effect is low. It can be widely applied to laser cutting of vascular stents of most polymer materials such as 316L stainless steel, L605 cobalt chrome and other metal materials such as polylactic acid (PLLA).
- PLLA polylactic acid
- 1 is a planar development view of the vascular stent produced by the utility model ( 3 ⁇ 4).
- FIG 2 is produced according to the present invention (a partial vascular stent substantially plane development unit of FIG.
- Figure 3 is a schematic view of the basic unit of the blood vessel stent of the present invention ( a).
- Figure 4 is produced according to the present invention (3 ⁇ 4 interleaved plane after removing vascular stent support bar axially expanded FIG.
- FIG 5 is produced according to the present invention (3 ⁇ 4 o column after removal of the vascular stent unequal axial plane of the support rods to expand FIG.
- FIG 6 is produced according to the present invention (3 ⁇ 4 interlaced plane after removing vascular stent deployment FIG unequal axial support rods.
- FIG 7 is produced according to the present invention (3 ⁇ 4 interlaced plane after removing vascular stent support bar axially expanded FIG.
- FIG 8 is produced according to the present invention (3 ⁇ 4 interlaced every other column after removal of the vascular stent planar development view of an axial support rods.
- FIG 9 is produced according to the present invention (3 ⁇ 4 three compartments and blood vessel stent interleaved plane after removing the support rods axially expand FIG.
- FIG. 10 is the planar deployment of the vascular stent after the axial support rod is removed every two rows of the utility model.
- FIG. 11 is a plan view of the vascular stent after the product of the utility model is separated by two columns and the axial support rods are staggered.
- Figure 12 is a plan development view of the bracket of the axial support rod of the product of the present invention.
- Figs. 1 to 3 symbol 1 represents a sine wave arranged in parallel, symbol 2 represents a vertex of a sine wave, symbol 3 represents an axial support bar, and symbol 4 represents a bent rib of a sine wave other than the apex.
- PLLA polylactic acid
- the blood vessel support for the pressure grip of the present invention is laser cut from a polylactic acid (PLLA) tubular material, which is composed of a plurality of rows of parallel sinusoidal waves (1) through an axial support rod (3) in a sine wave The vertices (2) are connected together.
- Polylactic acid tubing outer diameter 1. 8mm-4. 5 wall thickness 0. 08mm_0.
- the cutting edge is clear, the shape is regular. After being processed by the stent and pressed together with the balloon, the shape of the stent is still very regular after the stent is released, and the stent is not touched by the stent.
- the stent shortening rate is less than 1%, the supporting force is greater than 1N, and the flexibility is good. After the release, the stent diameter is less than 2%, and the "dog bone" effect is low.
- the vascular stent for the pressure grip of the present invention is laser-cut from a L605 cobalt-chromium tubular material by a plurality of rows of parallel arranged sine waves (1) through the axial support rods (3) in the sine The vertices of the waves (2) are connected together.
- the sufficiency is better than 1. 5N, the flexibility is good, the support is greater than 1. 5N, the support is greater than 1. 5N, the flexibility is good.
- the stent diameter is less than 3%, and the "dog bone" effect is low. Referring to FIG. 1, FIG. 1, FIG.
- the blood vessel support for the pressure grip of the utility model is laser cut from a 316L stainless steel tubular material, and is laser-cut by a L605 cobalt-chromium tubular material to form a plurality of parallel arranged sine waves.
- (1) By connecting the axial support rods (3) at the apex (2) of the sine wave.
- the sufficiency is better than 1. 5N, the flexibility is good, the support is greater than 1. 5N, the support is greater than 1. 5N, the flexibility is good.
- Example 2 Interlacing the axial support rods, see Figure 4
- Example 3 Removing the unequal axial support rods in the adjacent column, see Figure 5
- Example 4 Interlacing the unequal axial support rods, see Figure 6
- Example 5 Interlacing the axial support rods, see Figure 7
- Example 6 Interlacing the spacers to remove the axial support rods, see Figure 8
- Example 7 Separate the three axial rows and stagger the axial support rods, see Figure 9
- Example 8 The axial support bars are removed once every two rows, see Figure 10.
- Example 9 The axial support bars are removed in two rows and staggered, see Figure 11.
- Example 10 The wave crests are staggered to connect the axial support rods, see Figure 12.
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- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Life Sciences & Earth Sciences (AREA)
- Cardiology (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Transplantation (AREA)
- Physics & Mathematics (AREA)
- Vascular Medicine (AREA)
- Optics & Photonics (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
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- Prostheses (AREA)
Abstract
Description
一种利于压握的血管支架 技术领域 本实用新型涉及医疗器械中的血管支架， 特别是一种利于压握的血管支架。 技术背景 血管支架微创植入做为一种行之有效的介入技术被广泛用于治疗血管狭窄， 将管状镂 空支架通过手术安放至患病部位对血管实行有效支撑， 起到疏通狭窄血管的作用， 而且手 术不会对病患造成大创伤。 目前， 能用于制作血管支架的材料可分为金属和医用高分子材料两大类。 用于血管支架加工的金属材料主要有 316L不锈钢、 L605 钴铬 （CoCr) 合金、 镁合金 等。 在经过较长时间临床检验后， 金属支架生产和应用已日趋成熟， 是目前血管支架的主 流产品， 普遍为广大手术操作者和患者所接受。 但是研究表明， 金属支架在血管内长期存 留可引起血管的慢性损伤，后期可造成血管中层的萎縮、动脉瘤形成及反应性的内膜增生， 最终导致血管再狭窄的发生 （Rab ST, KiHgsB, Roubin GS, et al. Coronary aneurysms after stent Placement: a suggestion of altered vessel wall healing in the Presence of anti-inflammatory agents. J Am CollCardiol 1991, 18:1524)。 近年来，随着医疗需求和发展，一类由医用高分子材料为基材的血管支架正逐渐兴起， 该类支架能在损伤愈合的特定时间内对血管起力学支撑的作用， 并能在病变愈合后被机体 逐步吸收， 避免了金属支架因长期存留体内而产生的负面影响。 可用于制作生物降解血管支架的材料主要有聚乳酸 (polylacticacid, PLA)、 L-聚乳酸 BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a blood vessel stent in a medical device, and more particularly to a blood vessel stent that facilitates crimping. BACKGROUND OF THE INVENTION Minimally invasive implantation of vascular stents is widely used as an effective intervention technique for the treatment of vascular stenosis. The tubular hollow stent is surgically placed to the affected part to effectively support the blood vessels, thereby functioning to clear the narrow blood vessels. And the surgery will not cause major trauma to the patient. At present, materials that can be used to make vascular stents can be divided into two major categories: metal and medical polymer materials. Metal materials used for vascular stent processing mainly include 316L stainless steel, L605 cobalt chromium (CoCr) alloy, and magnesium alloy. After a long period of clinical testing, the production and application of metal stents have become increasingly mature, and it is currently the main product of vascular stents, which is generally accepted by the majority of surgical operators and patients. However, studies have shown that long-term retention of metal stents in blood vessels can cause chronic damage to blood vessels, which can lead to atrophy of the middle vascular layer, aneurysm formation and reactive intimal hyperplasia, which ultimately leads to the occurrence of vascular restenosis (Rab ST, KiHgsB, Roubin GS, et al. Coronary aneurysms after stent Placement: a suggestion of altered vessel wall healing in the Presence of anti-inflammatory agents. J Am Coll Cardiol 1991, 18: 1524). In recent years, with the medical needs and development, a series of vascular stents based on medical polymer materials are gradually emerging. These stents can support the vascular mechanical support during the specific time of injury healing, and can be used in lesions. After being healed, it is gradually absorbed by the body, which avoids the negative effects of metal stents due to long-term retention in the body. The materials that can be used to make biodegradable vascular stents are mainly polylactic acid (PLA) and L-polylactic acid.
(polyLlactic acid, PLLA或 LPLA)、 聚羟基乙酸 /聚乳酸共聚物（polyglycolic acid/polylactic acid, PGLA) 、 聚 己 内 酯 （polycaprolactone,PCL) 、 聚 羟 基 丁 酸 戊 酯 (polyhydroxylbutyratevalerate, PHBV)、 聚乙酰谷氨酸 ( olyacetylglutamicacid, PAGA)、 聚 正酯（polyorthoesters, POE)和聚氧化乙烯 /聚丁烯共聚物（polyethylene oxide/polybutylene terephthalate, PEO/PBTP)等。 目前支架材料应用较多的为 PLA, PLLA及 PGLA。 在美国， PLLA和 PGLA已被食品与药物管理局 (FDA)批准为可应用于人体的生物工程材料。 （刁繁 荣吕安林李军杰生物可降解性冠状动脉支架的研究进展第四军医大学学报 2006， 27 (20)) 不管是采用哪类管材切割血管支架， 切割好的血管支架都必须具备良好的生物相容 性、 足够的径向支撑力、 良好的柔顺性， 以满足长期或较长期内支撑血管病变部位的基本 安全需要。 除了切割血管支架的材料对产品的影响外， 血管支架图形设计也是决定成品优劣的关 键因素之一， 相同的管材采用不同的图形设计切割所得到的支架的性能差别很大。 由于血 管支架置于病人体内， 要经常受到血管的交变压力， 以及弯曲、 扭曲等各种外力的左右， 需要保证支架在此过程中不会碎裂和损坏。 而支架加工过程中支架内也会产生应力应变， 如果支架结构设计不良， 导致局部应力过于集中， 就可能会发生破裂等疲劳破坏。 因此， 支架设计图形对血管支架植入前后的性能至关重要。 发明内容 本实用新型的目的是提供一种利于压握的血管支架，适用于各类金属材料和医用高分 子材料的血管支架激光切割加工。 本实用新型所提供的血管支架给支架压握提供了做够的 空间， 压握时各支撑筋碰触在一起的可能性大大降低， 能有效保护药物涂层； 该血管支架 释放后形状仍十分规整， 支架短縮率很低， 支撑力及柔顺性良好， "狗骨头"效应低。 可 广泛适用于 316L不锈钢、 L605钴铬合金等金属材料和聚乳酸（PLLA)等大多数聚合物材 料血管支架的激光切割。 本实用新型的这个以及其他目的将通过下列详细描述和说明来进一步体现和阐述。 所述的利于压握的血管支架由管状材料激光切割而成，由纵向多排平行均布排列的正 弦波主体肋条 （1 ) 通过轴向支撑杆 （3) 在正弦波的波峰与波谷的顶点 （2) 相连而成。 可以增删正弦波主体肋条 （1 ) 的个数来调整支架长度， 改变正弦波主体肋条 （1 ) 的长度 来调整支架外径。 正弦波主体肋条由顶点和弯折筋构成， 弯折筋可以以顶点为定点合拢和伸展， 有利于 在支架捆绑在输送系统上时获得更小的直径和均匀的变形。 管状血管支架在受垂直周向外 力压握时， 弯折筋 （4) 顺着正弦波 （1 ) 的形状屈服于上下两段轴向支撑杆 （3) 的包围 内， 相邻的基本单元弯折筋 （4) 的弯曲方向保持一致， 保证各连接筋不会因为无屈服位 置而发生碰触， 进而保护药物涂层。 更进一步地， 本实用新型可用于但不仅限于以下血管支架管材的切割： 316L不锈钢、 L605钴铬合金等金属材料和聚乳酸 （PLLA) 及其混合物、 衍生物等。 可以根据材质金属 支架和聚合物切割管材具体特性需要， 对正弦波 （1 ) 的个数或 （和） 排列数或 （和） 顶 点轴向支撑杆 （3 ) 的数量进行增删得到一系列不同图形的血管支架设计图形， 来平衡支 架的柔顺性和支撑力。 本实用新型的利于压握的血管支架的有益效果是可以适应目前大部分材质血管支架 的切割， 给支架压握提供了做够的空间， 压握时各支撑筋碰触在一起的可能性大大降低， 能有效保护药物涂层； 血管支架释放后形状仍十分规整， 支架短縮率很低， 支撑力及柔顺 性良好， "狗骨头"效应低。 可广泛适用于 316L不锈钢、 L605钴铬合金等金属材料和聚 乳酸 （PLLA) 等大多数聚合物材料血管支架的激光切割。 附图说明 (polyLlactic acid, PLLA or LPLA), polyglycolic acid/polylactic acid (PGLA), polycaprolactone (PCL), polyhydroxylbutyratevalerate (PHBV), poly Olysyl glutamic acid (PAGA), polyorthoesters (POE), and polyethylene oxide/polybutylene terephthalate (PEO/PBTP). At present, the most widely used scaffold materials are PLA, PLLA and PGLA. In the United States, PLLA and PGLA have been approved by the Food and Drug Administration (FDA) as bioengineerable materials that can be applied to humans. (刁繁 Rong Lu Anlin Li Junjie Research progress of biodegradable coronary stents. Journal of the Fourth Military Medical University, 2006, 27 (20)) Regardless of which type of tube is used to cut the vascular stent, the cut vascular stent must have good biocompatibility. Adequate radial support and good compliance to meet the basic safety needs of long-term or longer-term support of vascular lesions. In addition to the influence of the material of the vascular stent on the product, the graphic design of the vascular stent is also one of the key factors determining the quality of the finished product. The performance of the stent obtained by cutting the same tube with different graphic design is very different. Since the vascular stent is placed in the patient's body, it is often subject to alternating pressure of the blood vessel, as well as various external forces such as bending and twisting, and it is necessary to ensure that the stent does not break and damage during the process. Stress and strain are also generated in the stent during the processing of the stent. If the structural design of the stent is poor, the local stress is too concentrated, and fatigue damage such as cracking may occur. Therefore, the stent design pattern is critical to the performance of the vascular stent before and after implantation. SUMMARY OF THE INVENTION The object of the present invention is to provide a blood vessel stent suitable for pressure grip, which is suitable for laser cutting processing of vascular stents of various metal materials and medical polymer materials. The blood vessel bracket provided by the utility model provides sufficient space for the pressure grip of the stent, and the possibility that the support ribs are touched together during the pressure grip is greatly reduced, and the drug coating can be effectively protected; the shape of the blood vessel stent is still very good after release. Regularity, the stent has a low shrinkage rate, good support and flexibility, and the "dog bone" effect is low. It can be widely applied to laser cutting of vascular stents of most polymer materials such as 316L stainless steel, L605 cobalt-chromium alloy and other polylactic acid (PLLA). This and other objects of the present invention will be further embodied and elucidated by the following detailed description and description. The vascular stent for facilitating the crimping is laser-cut from a tubular material, and the sinusoidal main body ribs (1) are arranged in parallel in a plurality of rows and are arranged in parallel by the axial support rods (3) at the apex of the sine wave peaks and troughs. (2) Connected together. The number of sine wave main ribs (1) can be added or deleted to adjust the length of the bracket, and the length of the main rib (1) of the sine wave is changed to adjust the outer diameter of the bracket. The sinusoidal main body ribs are composed of vertices and bending ribs, which can be closed and extended with the apex as a fixed point, which is advantageous for obtaining smaller diameter and uniform deformation when the bracket is bundled on the conveying system. When the tubular vascular stent is pressed by the vertical circumference and outward force, the bending rib (4) yields in the shape of the sine wave (1) in the surrounding of the upper and lower axial support rods (3), and the adjacent basic unit bends. The bending direction of the ribs (4) is kept the same, ensuring that the connecting ribs are not due to no yielding position. The touch occurs to protect the drug coating. Furthermore, the present invention can be used for, but not limited to, the cutting of the following vascular stent tubes: metal materials such as 316L stainless steel, L605 cobalt chrome, and polylactic acid (PLLA), and mixtures, derivatives thereof and the like. The number of sine waves (1) or the number of (or) arrays or (and) the number of apex axial support rods (3) can be added or deleted according to the specific characteristics of the material metal bracket and the polymer cutting tube to obtain a series of different graphics. The vascular stent design graphic balances the flexibility and support of the stent. The beneficial effect of the blood vessel support for the pressure grip of the utility model is that it can adapt to the cutting of the blood vessel stent of most materials at present, and provides sufficient space for the pressure grip of the stent, and the possibility that the support ribs touch together when pressed Reduced, can effectively protect the drug coating; the shape of the stent is still very regular after release, the stent has a short shortening rate, good support and flexibility, and the "dog bone" effect is low. It can be widely applied to laser cutting of vascular stents of most polymer materials such as 316L stainless steel, L605 cobalt chrome and other metal materials such as polylactic acid (PLLA). DRAWINGS
1是本实用新型产( ¾的血管支架平面展开图。 1 is a planar development view of the vascular stent produced by the utility model ( 3⁄4).
图 2是本实用新型产( a的血管支架基本单元局部平面展开图。 FIG 2 is produced according to the present invention (a partial vascular stent substantially plane development unit of FIG.
图 3是本实用新型产( a的血管支架基本单元局部压握后示意图。 Figure 3 is a schematic view of the basic unit of the blood vessel stent of the present invention ( a).
图 4是本实用新型产( ¾交错去除轴向支撑杆后的血管支架平面展开图。 Figure 4 is produced according to the present invention (¾ interleaved plane after removing vascular stent support bar axially expanded FIG.
图 5是本实用新型产( ¾邻列去除不等轴向支撑杆后的血管支架平面展开图。 FIG 5 is produced according to the present invention (¾ o column after removal of the vascular stent unequal axial plane of the support rods to expand FIG.
图 6是本实用新型产( ¾隔行去除不等轴向支撑杆后的血管支架平面展开图。 FIG 6 is produced according to the present invention (¾ interlaced plane after removing vascular stent deployment FIG unequal axial support rods.
图 7是本实用新型产( ¾隔行去除轴向支撑杆后的血管支架平面展开图。 FIG 7 is produced according to the present invention (¾ interlaced plane after removing vascular stent support bar axially expanded FIG.
图 8是本实用新型产( ¾隔行隔列去除轴向支撑杆后的血管支架平面展开图。 FIG 8 is produced according to the present invention (¾ interlaced every other column after removal of the vascular stent planar development view of an axial support rods.
图 9是本实用新型产( ¾隔三列并交错去除轴向支撑杆后的血管支架平面展开图。 FIG 9 is produced according to the present invention (¾ three compartments and blood vessel stent interleaved plane after removing the support rods axially expand FIG.
10 是本实用新型产品每隔两行交错一次去除轴向支撑杆后的血管支架平面展开 图 11是本实用新型产品隔两列并交错去除轴向支撑杆后的血管支架平面展开图。 图 12是本实用新型产品波峰波谷交错连接轴向支撑杆的支架平面展开图。 10 is the planar deployment of the vascular stent after the axial support rod is removed every two rows of the utility model. FIG. 11 is a plan view of the vascular stent after the product of the utility model is separated by two columns and the axial support rods are staggered. Figure 12 is a plan development view of the bracket of the axial support rod of the product of the present invention.
在图 1至图 3中， 符号 1代表平行排列的正弦波， 符号 2代表正弦波的顶点， 符号 3 代表轴向支撑杆， 符号 4代表正弦波除顶点外的弯折筋。 具体实施方式 本实用新型的利于压握的血管支架， 由聚乳酸 （PLLA) 管状材料激光切割而成， 由多 排平行排列的正弦波 （1 ) 通过轴向支撑杆 （3 ) 在正弦波的顶点 （2 ) 相连而成。 聚乳酸 管材外径 1. 8mm-4. 5 壁厚 0. 08mm_0. 25 使用飞秒激光切割， 切割后边缘清晰， 形 状规则。 在通过支架加工后与球囊压握在一起， 血管支架释放后形状仍十分规整， 无支架 连接筋碰触现象， 支架短縮率小于 1%， 支撑力大于 1N， 柔顺性良好。 释放后支架直径不 匀率小于 2%， "狗骨头"效应低。 参考图 2、 图 3， 本实用新型的利于压握的血管支架， 由 L605钴铬合金管状材料激光 切割而成由多排平行排列的正弦波 （1 ) 通过轴向支撑杆 （3 ) 在正弦波的顶点 （2 ) 相连 而成。 L605合金管材外径 1. Omm-4. 0 壁厚 0. 06mm_0. 12 使用激光切割， 切割后边 缘清晰， 形状规则。 在通过支架加工后与球囊压握在一起， 血管支架释放后形状仍十分规 整， 无支架连接筋碰触现象， 支架短縮率小于 1. 5%， 支撑力大于 1. 5N, 柔顺性良好。 释 放后支架直径不匀率小于 3%， "狗骨头"效应低。 参考图 1、 图 2、 图 3， 本实用新型的利于压握的血管支架， 由 316L不锈钢管状材料 激光切割而成， 由 L605钴铬合金管状材料激光切割而成由多排平行排列的正弦波 （1 ) 通 过轴向支撑杆 （3 ) 在正弦波的顶点 （2 ) 相连而成。 316L不锈钢管材外径 1. 0mm-4. 0mm 壁厚 0. 08mm_0. 15mm， 使用激光切割， 切割后边缘清晰， 形状规则。 在通过支架加工后与 球囊压握在一起， 血管支架释放后形状仍十分规整， 无支架连接筋碰触现象， 支架短縮率 小于 1. 5%， 支撑力大于 1. 5N, 柔顺性良好。 释放后支架直径不匀率小于 2%， "狗骨头"效 应低。 举例 2: 交错去除轴向支撑杆， 见附图 4 举例 3: 邻列去除不等轴向支撑杆， 见附图 5 举例 4: 隔行去除不等轴向支撑杆， 见附图 6 举例 5: 隔行去除轴向支撑杆， 见附图 7 举例 6: 隔行隔列去除轴向支撑杆， 见附图 8 举例 7: 隔三列并交错去除轴向支撑杆， 见附图 9 举例 8: 每隔两行交错一次去除轴向支撑杆， 见附图 10。 举例 9: 隔两列并交错去除轴向支撑杆， 见附图 11。 举例 10: 波峰波谷交错连接轴向支撑杆， 见附图 12。 In Figs. 1 to 3, symbol 1 represents a sine wave arranged in parallel, symbol 2 represents a vertex of a sine wave, symbol 3 represents an axial support bar, and symbol 4 represents a bent rib of a sine wave other than the apex. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS The blood vessel support for the pressure grip of the present invention is laser cut from a polylactic acid (PLLA) tubular material, which is composed of a plurality of rows of parallel sinusoidal waves (1) through an axial support rod (3) in a sine wave The vertices (2) are connected together. Polylactic acid tubing outer diameter 1. 8mm-4. 5 wall thickness 0. 08mm_0. 25 Using femtosecond laser cutting, the cutting edge is clear, the shape is regular. After being processed by the stent and pressed together with the balloon, the shape of the stent is still very regular after the stent is released, and the stent is not touched by the stent. The stent shortening rate is less than 1%, the supporting force is greater than 1N, and the flexibility is good. After the release, the stent diameter is less than 2%, and the "dog bone" effect is low. Referring to Figures 2 and 3, the vascular stent for the pressure grip of the present invention is laser-cut from a L605 cobalt-chromium tubular material by a plurality of rows of parallel arranged sine waves (1) through the axial support rods (3) in the sine The vertices of the waves (2) are connected together. L605 alloy pipe outer diameter 1. Omm-4. 0 wall thickness 0. 06mm_0. 12 using laser cutting, the cutting edge is clear, the shape is regular. The sufficiency is better than 1. 5N, the flexibility is good, the support is greater than 1. 5N, the support is greater than 1. 5N, the flexibility is good. After the release, the stent diameter is less than 3%, and the "dog bone" effect is low. Referring to FIG. 1, FIG. 2 and FIG. 3, the blood vessel support for the pressure grip of the utility model is laser cut from a 316L stainless steel tubular material, and is laser-cut by a L605 cobalt-chromium tubular material to form a plurality of parallel arranged sine waves. (1) By connecting the axial support rods (3) at the apex (2) of the sine wave. 316L stainless steel pipe outer diameter 1. 0mm-4. 0mm wall thickness 0. 08mm_0. 15mm, using laser cutting, the cutting edge is clear, the shape is regular. The sufficiency is better than 1. 5N, the flexibility is good, the support is greater than 1. 5N, the support is greater than 1. 5N, the flexibility is good. After the release, the stent diameter is less than 2%, and the "dog bone" effect is low. Example 2: Interlacing the axial support rods, see Figure 4 Example 3: Removing the unequal axial support rods in the adjacent column, see Figure 5 Example 4: Interlacing the unequal axial support rods, see Figure 6 Example 5: Interlacing the axial support rods, see Figure 7 Example 6: Interlacing the spacers to remove the axial support rods, see Figure 8 Example 7: Separate the three axial rows and stagger the axial support rods, see Figure 9 Example 8: The axial support bars are removed once every two rows, see Figure 10. Example 9: The axial support bars are removed in two rows and staggered, see Figure 11. Example 10: The wave crests are staggered to connect the axial support rods, see Figure 12.
Claims
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201020126811.3 | 2010-03-10 | ||
| CN 201020126811 CN201840555U (en) | 2010-03-10 | 2010-03-10 | Vessel stent being beneficial to being pressed and held |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| WO2011110092A1 true WO2011110092A1 (en) | 2011-09-15 |
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| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| PCT/CN2011/071663 Ceased WO2011110092A1 (en) | 2010-03-10 | 2011-03-10 | Blood vessel stent facilitating to be compressed and grasped |
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| Country | Link |
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| CN (1) | CN201840555U (en) |
| WO (1) | WO2011110092A1 (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US10888414B2 (en) | 2019-03-20 | 2021-01-12 | inQB8 Medical Technologies, LLC | Aortic dissection implant |
Families Citing this family (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103417317A (en) * | 2013-08-16 | 2013-12-04 | 江苏大学 | Intravascular stent |
| CA2950726A1 (en) * | 2014-06-02 | 2015-12-10 | Amaranth Medical Pte. | Bioabsorbable stents |
| CN105902331A (en) * | 2016-04-08 | 2016-08-31 | 南京永明医疗器械有限公司 | Intravascular stent and preparation method thereof |
| CN109172070A (en) * | 2016-05-17 | 2019-01-11 | 李刚 | A kind of surgery manually bracket |
| CN105796217B (en) * | 2016-05-17 | 2018-10-26 | 常州市第二人民医院 | A kind of intravascular stent |
| CN106038010B (en) * | 2016-05-19 | 2018-01-09 | 刘歆 | A kind of cardiovascular arterial bracket |
| CN108125738A (en) * | 2017-12-21 | 2018-06-08 | 潍坊医学院 | A cardiovascular stent |
| CN109966015B (en) * | 2017-12-27 | 2023-04-18 | 先健科技(深圳)有限公司 | Covered stent |
| CN113876475B (en) * | 2020-06-16 | 2024-03-19 | 上海瑛泰医疗器械股份有限公司 | Degradable magnesium alloy bracket |
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| US20020123791A1 (en) * | 2000-12-28 | 2002-09-05 | Harrison William J. | Stent design with increased vessel coverage |
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| CN2710576Y (en) * | 2004-03-10 | 2005-07-20 | 杨大智 | Laser curved 'quasi sine' tube type nickel titanium alloy support |
| US20080275537A1 (en) * | 2007-05-04 | 2008-11-06 | Limon Timothy A | Stents with High Radial Strength and Methods of Manufacturing Same |
| US20090270972A1 (en) * | 2006-05-23 | 2009-10-29 | All-Vascular Pty Ltd. | Endovenous valve transfer stent |
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| CN2408836Y (en) * | 1999-12-24 | 2000-12-06 | 蒲忠杰 | Medical diameter changing supporter for dilating human canal |
| US20020123791A1 (en) * | 2000-12-28 | 2002-09-05 | Harrison William J. | Stent design with increased vessel coverage |
| US6899729B1 (en) * | 2002-12-18 | 2005-05-31 | Advanced Cardiovascular Systems, Inc. | Stent for treating vulnerable plaque |
| CN2710576Y (en) * | 2004-03-10 | 2005-07-20 | 杨大智 | Laser curved 'quasi sine' tube type nickel titanium alloy support |
| US20090270972A1 (en) * | 2006-05-23 | 2009-10-29 | All-Vascular Pty Ltd. | Endovenous valve transfer stent |
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| US10888414B2 (en) | 2019-03-20 | 2021-01-12 | inQB8 Medical Technologies, LLC | Aortic dissection implant |
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| CN201840555U (en) | 2011-05-25 |
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