JP4067225B2 - Angioplasty vessel stent - Google Patents

Description

[0001]
[Technical field to which the invention belongs]
  The present invention relates to an aneurysm or other aneurysm shape.CompletionAneurysm shape used to treat blood vesselsCompletionThe present invention relates to a vascular stent.
[0002]
[Prior art]
  The aorta is more likely to have an aneurysm than the peripheral artery. This aneurysm gradually expands, and eventually the aneurysm wall cannot resist the blood pressure and ruptures. When ruptured, it is a very malignant disease with a very high mortality rate of 75-80% in the abdomen and 70% or more in the chest. Conventionally, this aneurysm treatment has been performed by removing a lesion site and embedding a prosthesis (artificial blood vessel) or wrapping around the lesion site with a graft. However, since these methods are surgically laparotomized, the invasion of the patient is large, the amount of bleeding is large, and the hospitalization period is also long. For this reason, there has been a problem that it cannot be applied to elderly patients who have no physical strength or elderly people with chronic illness. In order to solve these problems, a treatment method has been carried out in which a stent with a cover (stent graft) is placed percutaneously and the aneurysm is blocked to form a thrombus. This method of treatment is less invasive and less bleed, so that patients who could not be treated surgically until now can be treated.
[0003]
  However, in each of these stent grafts, a phenomenon (leak) in which blood flows into the aneurysm from the gap between the end portions of the stent graft that fixes the stent graft to the host blood vessel occurs after placement in the blood vessel. The main causes of the leak include poor adhesion between the stent graft and the host blood vessel and poor fixation. Once this leak occurs, blood is sent into the aneurysm even after stent graft placement, the aneurysm does not thrombolate, the internal pressure of the aneurysm increases, the aneurysm expands, and the aneurysm may rupture is there. For this reason, in cases where the leak does not heal after placement, additional stents have been added to the leak site and a shift to artificial blood vessel transplantation by surgical operation has been performed.
[0004]
  The object of the present invention has been made in view of such a problem, and has the shape of an aneurysm.CompletionAfter placement of the stent in the blood vessel, thrombus formation in the gap between the host blood vessel and the stent is fast, preventing blood from flowing into the aneurysm and fixing the stent and host blood vesselsexAneurysm shape that can improveCompletionIt is to provide a vascular stent.
[0005]
[Means for Solving the Problems]
  To achieve the above purpose,It is as follows.
(1)A tube-shaped structure that is deformable into a first outer diameter and a second outer diameter that is larger than the first outer diameter, and encloses a side surface of the structure.TubularAn aneurysm having a membraneCompletionA vascular stent comprising:Provided at both ends of the stentIt has a thrombus formation promoting partThe thrombus formation promoting part is formed by wrapping a mall-shaped fiber assembly in which the free ends of innumerable yarns are exposed, and the thrombus formation promoting part contains a blood coagulation factor adhesion improving substance. AttachedAneurysm shapeCompletionVascular stent.
[0006]
(2) The aneurysm-forming blood vessel stent according to (1), wherein the blood component adhesion improving substance is at least one of albumin, collagen, gelatin, and globulin.
[0007]
(3) The stent according to (1), wherein the stent includes a thrombus formation promoting portion provided on a side surface near the center of the stent.
[0008]
(4) The structure includes a maintaining means for maintaining the outer diameter of the structure at the second outer diameter, and the maintaining means includes a telescopic guide tube and an outer diameter smaller than the inner diameter of the guide tube. A rod having a diameter and inserted into the guide tube, wherein the structure has the first outer diameter when the guide tube is in an extended state, and the guide tube contracts when the rod is pulled. Thus, the aneurysm-forming blood vessel stent according to (1) or (2), wherein the structure has a diameter that becomes the second outer diameter.
(5) The aneurysm-forming blood vessel stent according to (4), wherein the guide tube is configured by a coil made of an elastic material.
[0009]
DETAILED DESCRIPTION OF THE INVENTION
  Hereinafter, the aneurysm shape of the present inventionCompletionA vascular stent will be described in detail based on a preferred embodiment shown in the accompanying drawings.
  FIG. 1 shows an aneurysm shape of the present invention.CompletionAneurysm with vascular stentCompletionFIG. 2 is an external view of an embodiment when applied to a vascular stent (stent graft), and FIG. 2 is a partially enlarged view of the stent of the embodiment of FIG. 3 and 4 are perspective views showing the structure of the maintenance means in the stent shown in FIG. 1, FIGS. 5 to 8 are partial sectional side views showing the operation of the maintenance means and the outer diameter expanding means, and FIG. It is a perspective view which shows the structure of the one end part of a diameter expansion means. 1 to 9, the upper side is described as “upper” or “upper end”, and the lower side is described as “lower” or “lower end”.
[0010]
  Aneurysm shape of the present inventionCompletionThe blood vessel stent 1 is a tube-shaped structure, which can be deformed into a first outer diameter and a second outer diameter larger than the first outer diameter. An aneurysm having a membrane 4 enclosing the sideCompletionThis is a vascular stent. The stent 1 includes thrombosis promoting portions (in other words, blood clotting factor good adhesion portions) 11 and 12.
[0011]
  A stent (stent graft, in-vessel indwelling object) 1 of the embodiment shown in FIG. 1 is inserted and placed (transplanted) in an aneurysm formation site in the aorta, and its outline is formed in a tube shape. (Three-dimensional structure) 2 and a film 4 enclosing the structure 2 are provided. The structure 2 is formed in a tube shape as shown in FIGS. Note that the structure may have a structure including a main body tube and two branch tubes that are bifurcated from the main body tube.
[0012]
  The structure 2 is mainly composed of a plurality of struts (linear bodies) 27 wound in a spiral shape. The structure 2 of this embodiment includes a plurality of struts 27a spirally wound in the same direction (winded so as to be substantially parallel), and a plurality of struts 27a wound in the opposite direction to the plurality of struts 27a. A strut 27b is provided. For this reason, a large number of intersections where the struts 27 a and the struts 27 b intersect are formed in the structure 2. The skeleton of the structure 2 is formed by these struts 27 (27a, 27b). In addition, the shape and form of the strut 27 are not limited to a spiral shape, but may be, for example, a ring shape (particularly, a shape in which a plurality of rings are connected) or a net shape.
[0013]
  The outer diameter of the structure 2 is changed by the action of an external force. That is, in a natural state (a state in which no external force is applied), it is the first outer diameter (hereinafter, this state is referred to as a “reduced diameter state”).5dIs operated, the second outer diameter becomes larger than the first outer diameter (hereinafter, this state is referred to as “expanded diameter state”).
  In this case, the first outer diameter is such that the stent graft 1 can move within the aorta, and the second outer diameter is such that the stent graft 1 can sufficiently adhere to the inner wall of the aorta.
[0014]
  Further, the structure 2 is provided with rod-like maintenance means 3a to 3d extending along the longitudinal direction thereof. The maintaining means has a function of maintaining the outer diameter of the structure 2 at the second outer diameter, and a plurality of the maintaining means are preferably arranged along the circumferential direction of the structure 2. In the stent graft 1 of this embodiment, four maintenance means 3a to 3d are installed at substantially equal intervals along the tube circumferential direction.
[0015]
  Examples of the constituent material of the strut 27 and the maintaining means 3a to 3d include various metals such as stainless steel, Ni—Ti alloy, Cu—Zn alloy, Ni—Al alloy, tungsten, tungsten alloy, titanium, titanium alloy, and tantalum. , Polyamides, polyimides, ultrahigh molecular weight polyethylene, polypropylene, fluorine-based resins and other relatively high-rigidity polymer materials, or combinations of these appropriately, among which stainless steel or stainless steel A core material is preferred. Moreover, the wire diameter of the strut 27 is not particularly limited, but can preferably be about 0.03 to 2 mm. More preferably, it can be about 0.1-1 mm.
[0016]
  The ends of the struts 27 are fixed to the upper and lower ends of the maintaining means 3a to 3d. Moreover, the site | part which cross | intersects the strut 27 in the middle of the maintenance means 3a-3d is being fixed, and it is preferable that the cross site | part of struts 27 is also fixed similarly. The fixing is performed by, for example, bonding with an adhesive, brazing such as soldering, welding, ligation or the like. In addition, the fixing of the struts 27 to the intermediate portions of the maintaining means 3a to 3d and the fixing of the crossing portions of the struts 27 are preferably loose fixing in which the crossing angle is variable. Thereby, expansion and contraction of the stent graft 1 can be performed more smoothly. The strut 27 is fixed to a guide tube 31 that is a member constituting the maintaining means 3a to 3d (see FIGS. 3 and 4).
  As described above, the maintaining means 3 a to 3 d form a part of the skeleton of the structure 2 together with the strut 27. In particular, the maintaining means 3 a to 3 d serve as pillars extending in the longitudinal direction of the structure 2. Thereby, necessary and sufficient strength and elasticity, particularly uniform strength and elasticity can be ensured without complicating the structure of the structure 2.
[0017]
  As shown in FIGS. 1 and 2, the film 4 is coated on the inner surface, outer surface, or both surfaces (in this embodiment, the outer surface) of the structure 2. Thereby, since the stent graft 1 and the inner surface of the lumen are in close contact with each other, it is possible to prevent positional deviation and angular deviation from the axis of the blood vessel after placement. The membrane 4 is preferably one that expands and contracts with a change in the outer diameter of the structure 2 or one that expands from a folded state. The membrane 4 may be, for example, a fibrous porous membrane such as a woven fabric, a knitted fabric, a non-woven fabric, or a paper material, a non-fibrous porous membrane, or a dense membrane such as a polymer sheet.
[0018]
  When a fiber material is used as the membrane 4, for example, natural fibers such as cellulose fiber, cotton, linter, kapok, flax, cannabis, ramie, silk, wool, nylon (polyamide), fluororesin fiber, rayon, cupra A chemical fiber such as acetate, vinyl resin fiber, acrylic, polyethylene terephthalate (polyester), polypropylene, or a combination of two or more of the above natural and chemical fibers (such as blended fibers) can be used.
[0019]
  Further, when a polymer sheet is used as the film 4, examples of the material include polyesters such as polyethylene, polypropylene, polyurethane, polyethylene terephthalate, and polybutylene terephthalate, polyvinyl chloride, polytetrafluoroethylene, natural rubber, and isoprene. Various rubbers such as rubber, silicone rubber, styrene-butadiene rubber and latex rubber, and various thermoplastic elastomers such as polyamide, polyester and polyurethane can be used.
  The film 4 may be a laminate of two or more layers made of the same or different materials.
[0020]
  The installation location of the membrane 4 with respect to the structure 2 may be the whole structure 2 or a part thereof, but preferably covers the central portion in the longitudinal direction of the structure 2, more preferably substantially the entire inner surface or outer surface of the structure 2. It is preferable. Thereby, when the structural body 2 expands to have the second outer diameter, the close contact portion between the inner wall of the lumen and the stent 1 becomes large, and the positional deviation of the indwelling stent 1 can be prevented.
  In the embodiment shown in FIGS. 1 and 2, the outer periphery of the structure 2 is covered with a tubular film 4 over almost the entire length, and only the both ends are exposed.
[0021]
  And as shown in FIG.1 and FIG.2, the thrombus formation promotion parts 11 and 12 are formed in the both ends of the structure 2. As shown in FIG. The thrombus formation promoting portions 11 and 12 of this embodiment are made of a fiber assembly in which one end is fixed to the outer surface of the stent and the other end is a free end. Specifically, the fiber assembly is wound around both ends of the structure 2. Numerous free ends of yarn are exposed on the surface of the fiber assembly, which is a so-called molding. For this reason, the contact area with the blood component (blood coagulation factor) is wide and the adhesion is high, and the formation of thrombus in this portion is fast. Thus, the thrombus formation promoting portions 11 and 12 are preferably formed at the end of the structure 2, but may be provided on the outer surface near the center of the membrane 4 in the axial direction. In this case, a thrombus formation promoting part having a certain width is desirable. In addition, the thrombus formation promoting portion is not limited to the above, and for example, a stretchable fiber assembly in which fibers are bundled is wound around the end portion (preferably both ends) of the structure 2. It may be.
[0022]
  The fiber used for the blood clot formation promoting portions 11 and 12 may be any fiber as long as it can adhere to blood components (coagulation factors). Polyethylene terephthalate, polytetrafluoroethylene, polypropylene, polyethylene, polyamide Synthetic fibers formed from polyurethane, polybutylene terephthalate, etc., natural fibers such as cellulose fibers, cotton, linter, kapok, flax, cannabis, ramie, silk, wool and the like are suitable.
[0023]
  Furthermore, it is preferable that a blood component adhesion improving substance (blood coagulation factor adhesion improving substance, for example, a protein) is attached to the thrombus formation promoting portions 11 and 12 formed of fibers as described above. The protein is preferably derived from a living body, and albumin, gelatin, collagen, globulin and the like are used.
[0024]
  Further, as described above, the thrombus formation promoting portions 11 and 12 are not limited to those using fibers, apart from the film forming material. For example, the thrombus formation promoting portion is provided on the membrane 4. Also good. For example, as shown in FIG. 10, the blood component (blood coagulation factor) adhesion improving substance (for example, protein) 14 as described above is attached to one end or both ends of the membrane 4 to thereby promote the thrombus formation promoting portion. 13a and 13b can be formed. In addition, as shown in FIG. 11, the membrane 4 has a predetermined width (a length in the axial direction, preferably about 10 to 150 mm) at the central portion in the axial direction, and blood components ( The blood clot formation promoting part 13 may be formed by attaching a blood coagulation factor) adhesion improving substance (for example, protein) 14. In these cases, it is preferable that the portion 4a of the membrane 4 serving as a thrombus formation promoting portion is slightly thicker than the other portions, and that the protein adheres well. Moreover, the above-described protein may be attached to the entire outer surface of the membrane 4 to form a thrombus formation promoting portion.
[0025]
  Next, the structures of the maintaining means 3a to 3d and the outer diameter expanding means will be described.
  Corresponding outer diameter expanding means are detachably connected (linked) to the lower end portions of the maintaining means 3a to 3d, respectively. The outer diameter expansion means is a structure 2 in a reduced diameter state.Diameter expansionWhile maintaining the state, the corresponding maintaining means 3a to 3d are operated.
  Since each of the maintaining means 3a to 3d and each of the outer diameter expanding means has substantially the same configuration, the maintaining means 3c and the outer diameter expanding means 5c connected thereto will be described below with reference to FIGS. Will be described representatively.
[0026]
  The maintaining means 3 c is configured by a telescopic guide tube 31 and a rod 32 having an outer diameter smaller than the inner diameter of the guide tube 31, and the rod 32 is inserted into the guide tube 31.
  The guide tube 31 is composed of a coil (coil spring) made of an elastic material. The guide tube 31 extends in a natural state, but can be contracted by a pulling operation of the rod 32.
[0027]
  As described above, the strut 27 is fixed to the guide tube 31. As shown in FIG. 3, when the guide tube 31 is in the extended state, the strut 27 fixed to the guide tube 31 is also extended in the axial direction, and the structure 2 is in a reduced diameter state. Also, as shown in FIG. 4, when the guide tube 31 contracts by pulling the rod 32, the axial distance between the fixed points of the strut 27 with respect to the guide tube 31 decreases, and the strut 27 expands in the radial direction. 2 becomes a diameter-expanded state.
[0028]
  Note that the contraction rate of the guide tube 31 may be the same over the entire length of the guide tube 31, but the guide tube 31 may have portions having different contraction rates in the longitudinal direction. In this case, the position of the fixed point of the strut 27 with respect to the guide tube 31 and the distance between the fixed points are selected, and the diameter expansion rate (= second outer diameter / first outer diameter) of the structure 2 is partially set. Can be changed. As a result, the shape of the structure 2 in the expanded state can be arbitrarily set, and the followability and adaptability to the placement site of the lumen can be further improved.
[0029]
  As a method of giving different shrinkage rates to the guide tube 31, for example, a method in which a plurality of unit guide tubes having different mechanical characteristics (spring elastic modulus and the like) are connected in the longitudinal direction to form one guide tube 31, For example, a method of changing the elastic modulus by changing coil winding conditions (density (number of turns), coil outer diameter, etc.) with respect to the guide tube.
[0030]
  The rod 32 is made of a wire, and a hook (stopper) 321 that engages with the upper end of the guide tube 31 is formed at the upper end thereof. The hook 321 may be fixed to the upper end portion of the guide tube 31 by the same method as described above.
  Further, the lower end portion of the rod 32 has an engaging portion 322 formed by bending the rod 32 into a loop shape. The engaging portion 322 engages with the lower end of the guide tube 31 and thereby maintains the contracted state of the guide tube 31 (see FIG. 7).
  A ring 33 is engaged (connected) or fixed to the lower end of the rod 32, that is, the loop portion of the engaging portion 322. The ring 33 is a connecting member that connects the rod 32 and the pulling wire 52. The ring 33 may be a separate body or an integrated body with respect to the rod 32.
[0031]
  Examples of the coil material forming the guide tube 31 include the same materials as those described as the constituent material of the strut 27. In addition, the outer diameter of the guide tube 31 is not particularly limited and depends on the outer diameter of the stent 1, but usually 0.2 to 2 in consideration of the burden and strength of the patient when inserted into the body cavity. About 0.5 mm is preferable, and about 0.4 to 1.2 mm is more preferable. The cross-sectional shape of the coil of the guide tube 31 is not limited to a circle, and may be any shape such as an ellipse or a quadrangle (flat shape).
[0032]
  Examples of the constituent material of the rod 32 include the same materials as those described as the constituent material of the strut 27. Moreover, although the wire diameter of the rod 32 is not specifically limited, Usually, about 0.05-1.5 mm is preferable and about 0.1-0.8 mm is more preferable.
[0033]
  Examples of the constituent material of the ring 33 include the same materials as those described as the constituent material of the strut 27. In addition, the wire diameter of the ring 33 is not particularly limited, but in the case of the ring 33 as a separate body, a relatively thin one is preferable in order to obtain sufficient flexibility, and specifically, about 0.03 to 0.3 mm. Is preferable, and about 0.08 to 0.15 mm is more preferable.
[0034]
  The outer diameter expanding means 5c is installed at the upper end of the outer tube 51, the pulling wire 52 inserted into the outer tube 51, and the outer tube 51, and is a connecting member (spacer) that constitutes a connecting portion with the maintaining means 3c. 53. The outer diameter expanding means 5c is detachably connected (linked) to the maintaining means 3c.
  The outer tube 51 has moderate rigidity, that is, when the guide tube 31 is contracted by pulling the rod 32, the outer tube 51 resists the compressive force generated in the axial direction, does not cause bending, and has moderate flexibility. (Flexibility), for example, a resin tube or a closely wound coil made of the same coil material as that of the guide tube 31 may be used.
[0035]
  The puller wire 52 has an outer diameter smaller than the inner diameter of the outer tube 51 and can slide smoothly in the outer tube 51. A hook 521 is provided at the upper end portion of the pulling wire 52. The hook 521 is engaged with the ring 33. Further, the lower end side of the pulling wire 52 protrudes from the lower end opening of the outer tube 51 by a predetermined length, and a pulling operation unit (not shown) is formed at the lower end portion. The traction operation unit is operated to pull the traction wire 52 downward.
[0036]
  When the pulling wire 52 is pulled downward while the hook 521 is engaged with the ring 33, the rod 32 is pulled downward via the ring 33, the guide tube 31 contracts, and the structure 2 is expanded in diameter. It becomes a state. Markers 522 and 523 are attached to predetermined positions on the lower end side of the pulling wire 52 as display means for indicating the moving amount (pulling amount) of the pulling wire 52. In this embodiment, at least two markers 522 and 523 that can be distinguished by different colors or shapes are attached. These markers 522 and 523 are used for various purposes. For example, as shown in FIG. 5, the engaging portion 322 is in the guide tube 31 and is not yet engaged with the lower end of the guide tube 31, and the guide tube 31 can be freely expanded and contracted. As shown in FIG. 6, it can be known that the engaging portion 322 is engaged with the lower end of the guide tube 31 or is in a state immediately before the engagement. The markers 522 and 523 are attached to positions corresponding to these states, respectively, and the state can be recognized by distinguishing the markers 522 and 523 that appear and disappear from the lower end opening of the outer tube 51.
  As another example of the display means, a scale corresponding to the amount of movement of the pulling wire 52 is attached to the pulling wire 52 or its pulling means (take-up reel or the like).
[0037]
  As shown in FIG. 9, the connection member 53 is configured by a flat box-shaped member, and a pair of opposing protrusions 531 are formed to protrude upward at the center of the upper end thereof. . The lower end of the guide tube 31 is in contact with or fitted into the protrusion 531.
  Inside the connection member 53, an internal space 530 that allows the engagement portion 322 to pass in a connected state of the maintaining means 3c and the outer diameter expanding means 5c is formed. Further, notches 532 are formed on both sides of the upper end portion of the connection member 53.
[0038]
  With the maintaining means 3c and the outer diameter expanding means 5c connected, the engaging portion 322 enters the internal space 530, and its end 323 passes through the notch 532 and protrudes outward from the guide tube 31, The guide tube 31 can be engaged with the lower end. That is, the connection member 53 allows the maintenance means 3c to start the operation of maintaining the expanded diameter of the structure while the maintaining means 3c and the outer diameter expanding means 5c are connected. Therefore, the operability of the operation for expanding the diameter of the structure 2 and maintaining the expanded state is improved. In the illustrated configuration, the planar shape of the connection member 53 is a rectangle, but is not limited thereto, and may be an ellipse, for example.
  The connection member 53 may be fixed to the outer tube 51 simply by being fitted thereto, or may be fixed by bonding with an adhesive, fusion bonding, brazing, welding, or the like.
[0039]
  A bundling member 54 is installed at the lower end of the outer tube 51. The bundling member 54 bundles the two outer tubes 51 of the outer diameter expanding means 5c and 5d into one. The bundle member 54 has a diameter larger than that of the two outer tubes 51. Therefore, the bundling member 54 constitutes a gripping part that is gripped by a gripping instrument in a blood vessel (aorta), as will be described later.
[0040]
  Specific examples of the bundling member 54 include a rubber band (O-ring), a string (thread), a band tube, a metal or resin clip (clamping member), and the like. Note that such a bundling member 54 may or may not be attached to each outer tube 51 of the outer diameter expanding means 5a and 5b.
  The outer diameter of the outer tube 51 is not particularly limited, and depends on the outer diameter of the stent 1, but is generally 0.2 to 2.5 mm in consideration of the burden and strength of the patient when inserted into the body cavity. The degree is preferable, and about 0.4 to 1.2 mm is more preferable.
  Examples of the constituent material of the pulling wire 52 include the same materials as those described as the constituent material of the strut 27. The wire diameter of the pulling wire 52 is not particularly limited, but is usually preferably about 0.1 to 1.5 mm, and more preferably about 0.2 to 0.8 mm.
[0041]
  Examples of the connecting member 53 include a metal tube deformed into a desired shape, a resin molded body, and the like. Examples of the metal material constituting the connection member 53 include iron or an iron-based alloy (such as stainless steel), copper or a copper-based alloy, aluminum or an aluminum alloy, titanium or a titanium alloy. Examples of the resin material constituting the connection member 53 include ultra high molecular weight polyethylene, polypropylene, polyamide, polyimide, polystyrene, polycarbonate, polymethyl methacrylate, ABS resin, polyethylene terephthalate, polybutylene terephthalate, and other polyesters, polysulfone, and polyethersulfur. Hong, polyphenylene sulfide, polyacetal, polyether ether ketone, polytetrafluoroethylene and the like can be mentioned.
[0042]
  Since the maintaining means 3c and the outer diameter expanding means 5c are structured as described above, the operability is excellent, and the diameter can be reduced while sufficiently functioning as the maintaining means and the outer diameter expanding means. . This contributes to reducing the burden on the patient during insertion into the lumen. Further, by reducing the diameter, it becomes possible even for sites that have been difficult to insert conventionally, and the range of application to various parts of the living body can be expanded.
[0043]
  Next, operations (actions) of the maintaining means 3c and the outer diameter expanding means 5c will be described with reference to FIGS.
  As shown in FIG. 5, first, in a state where no external force is applied to the maintaining means 3c, the guide tube 31 of the maintaining means 3c is in an extended state, whereby the structure 2 is in a reduced diameter state. At this time, the engaging portion 322 is accommodated in the guide tube 31. Further, the rod 32 and the pulling wire 52 are connected by a ring 33 so that tension can be transmitted.
[0044]
  Next, when the pulling wire 52 is pulled downward while holding the outer tube 51 as shown in FIG.531Contacts or fits to the lower end of the guide tube 31. When the pulling wire 52 is further pulled downward, the rod 32 is pulled, the guide tube 31 contracts, and the structure 2 is in an expanded state. Further, when the guide tube 31 contracts, the engaging portion 322 is exposed from the lower end opening of the guide tube 31 and enters the internal space 530 of the connection member 53. At this time, the end portion 323 of the engaging portion 322 passes through the notch 532 and protrudes outward from the guide tube 31.
[0045]
  Next, when the tension of the pulling wire 52 is weakened and the pulling wire 52 is returned slightly upward, the end portion 323 of the engaging portion 322 is engaged with the lower end of the guide tube 31 as shown in FIG. Thereby, the contraction state of the guide tube 31, that is, the diameter expansion state of the structure 2 is maintained.
  In addition, the operator can grasp | ascertain the operation | movement until it changes from the diameter-reduced state of the said structure 2 to a diameter-expanded state, and it is maintained, by visually recognizing the positions of the markers 522, 523 grade | etc.,.
[0046]
  Next, as shown in FIGS. 7 to 8, the hook wire 521 is removed from the ring 33 by performing operations such as upward movement and rotation of the pull wire 52, and then the pull wire 52 is moved downward again to hook. 521 is accommodated in the internal space 530 of the connection member 53. Thereby, the outer diameter expanding means 5c is separated from the maintaining means 3c.
  The operation as described above is performed in the same manner for the maintaining means and the outer diameter expanding means other than the maintaining means 3c and the outer diameter expanding means 5c. The surgeon can perform such an operation easily and smoothly in a short time.
[0047]
  The structure 2 is not limited to the structure and mechanism described above, and may be a so-called balloon expandable stent or self-expandable stent.
  The balloon expandable stent has no expansion function in the stent itself. After inserting the stent into the target site, the balloon is positioned in the stent to expand the balloon, and the stent is expanded (plastic deformation) by the expansion force of the balloon. It is of the type that is fixed in close contact with the inner surface of the lumen. For this reason, the stent is formed in a substantially tubular body, has a diameter for insertion into a living body, and is extensible when a force is applied that extends radially outward from the inside of the tubular body. .
[0048]
  Such a balloon expandable stent includes, for example, a ring-shaped ring formed by thin wavy elements and arranged in a plurality in the axial direction of the stent, and a connecting portion that connects the ring-shaped rings in the axial direction. Yes. As a material for forming the balloon expandable stent, a material having a certain degree of biocompatibility is preferable. For example, stainless steel, tantalum or a tantalum alloy, platinum or a platinum alloy, gold or a gold alloy, a cobalt base alloy, or the like can be considered. Moreover, after producing the stent shape, precious metal plating (gold, platinum) may be performed. As stainless steel, SUS316L having the most corrosion resistance is suitable.
[0049]
  Further, the self-expandable stent has a contraction and expansion function. In order to place the stent in the target site, the stress applied to maintain the contracted state is removed after the stent is inserted into the target site in the contracted state. For example, the stent is contracted and stored in a sheath having an outer diameter smaller than the inner diameter of the target site, and after the distal end of the sheath reaches the target site, the stent is pushed out of the sheath. The extruded stent is released from the sheath to release the stress load, and restores and expands to the shape before contraction. Thereby, it adheres and fixes to the inner surface of the target part.
[0050]
  Self-expandable stents include a cylindrical frame body, an opening partitioned by the frame constituting the cylindrical frame body, and a notch section partitioned by the frame, a coiled one, a cylinder Shape, roll shape, irregular shaped tube shape, higher order coil shape, leaf spring coil shape, basket or mesh shape.
  A metal is used as a material for forming the self-expandable stent. As the metal, for example, stainless steel, tantalum, nickel titanium alloy, super elastic metal and the like are preferable.
[0051]
  In all types of stents described above, the size of the stent varies depending on the indwelling blood vessel site, the patient's physique, etc., but generally the total length is preferably 30 mm to 400 mm, and particularly preferably 50 mm to 250 mm. The inner diameter is preferably 2 to 50 mm, particularly preferably 3 to 40 mm. The outer diameter is preferably 3 mm to 55 mm, particularly preferably 5 mm to 45 mm.
[0052]
  Next, the aneurysm shape of the present inventionCompletionA blood vessel treatment instrument will be described with reference to the drawings.
  Aneurysm shape of the present inventionCompletionVascular treatment instrument 60, 70, 80 is a tube-shaped structure that can be deformed into a first outer diameter and a second outer diameter that is larger than the first outer diameter; An aneurysm having a membrane encapsulating the side of the structureCompletionVascular stent 61 and aneurysm shapeCompletionIntravascular insertion tools 62, 72, and 82 that can be inserted into the stent after being placed in the blood vessel and have a heating mechanism for heating the blood vessel in the stent placement portion.
[0053]
  Aneurysm shape shown in FIG.CompletionThe blood vessel treatment device 60 has an aneurysm shape.CompletionIt consists of a blood vessel stent 61 and an intravascular insertion tool 62. The intravascular insertion tool 62 has an aneurysm shape.CompletionA balloon 65 that can come into contact with the inner surface of the stent 61 after being placed in the blood vessel during expansion, a flow path (lumen) 68 for supplying a liquid into the balloon, and a heating means 66 for heating the liquid in the balloon. It has.
  Aneurysm shapeCompletionAs the blood vessel stent 61, the above-described various stents can be used.
[0054]
  The intravascular insertion tool 62 includes a tube main body 63 and a connector 64 fixed to the rear end thereof. A balloon 65 that can be inflated and deflated is fixed to the distal end of the tube body 63 in a liquid-tight manner. A heating module 66 and a temperature sensor 67 are fixed at a position on the outer surface of the tube body 63 and in the balloon 65. The tube main body 63 includes two lumens 68 and 69 inside, and the lumens 68 and 69 are sealed by a tip member 91 fixed to the tip of the tube main body 63. Further, on the outer surface of the tube main body 63, a side hole 92 that communicates the inside of the balloon 65 and the lumen 68, a side hole 95 for inserting the lead wire 93 of the heating module 66, and a lead wire 94 of the temperature sensor 67 are inserted. Side holes 96 are provided. Further, the side hole 95 is sealed by the heating module 66, and the side hole 96 is sealed by the temperature sensor 66, and the balloon 65 does not communicate with the lumen 69.
[0055]
  The connector 64 is electrically connected to the fluid port 64a communicating with the balloon expansion lumen 68 and the lead wire 93 of the heating module 66, and is connected to a heating device (not shown). And a connection part 97 for being electrically connected to the lead wire 94 of the temperature sensor 67 and being connected to a temperature detection device (not shown).
[0056]
  As the tube main body 63, one having a certain degree of flexibility is preferable. For example, polyolefin (for example, polyethylene, polypropylene, ethylene-propylene copolymer, ethylene-vinyl acetate copolymer, etc.), polyvinyl chloride, polyimide, A thermoplastic resin such as polyurethane, polyamide elastomer, silicon rubber, latex rubber and the like can be used, preferably the above-mentioned thermoplastic resin, and more preferably polyurethane.
  The length of the tube body 63 is 200 to 600 mm, more preferably 450 to 550 mm, the outer diameter is 1.0 to 5.0 mm, more preferably 1.15 to 4.0 mm, and the wall thickness is It is 0.1-0.4 mm, More preferably, it is 0.15-0.25 mm.
[0057]
  The balloon 65 can be inflated and deflated, and is configured to be in close contact with or folded on the outer periphery of the tube body when deflated. The material of the balloon 65 is preferably a material having a certain degree of plasticity and a hardness that can suppress significant volume fluctuations due to driving fluid pressure and blood pressure. For example, polyolefin such as polyethylene, polypropylene, ethylene-propylene copolymer, polyethylene terephthalate, etc. Polyester such as, polyvinyl chloride, ethylene-vinyl acetate copolymer, cross-linked ethylene-vinyl acetate copolymer, thermoplastic resin such as polyurethane, polyamide elastomer, silicone rubber, latex rubber and the like can be used.
[0058]
  Each end of the balloon 65 is fixed to the outer peripheral surface of the tube main body by, for example, adhesion (for example, heat fusion). Also, the size of the balloon needs to be able to contact the inner surface of the stent during expansion. Specifically, the size of the balloon 65 differs depending on the intended blood vessel site, but when used for the aorta, the outer diameter during expansion is 3 to 52 mm, preferably 4 to 42 mm. The length is preferably about 10 to 70 mm.
[0059]
  As the heating module 66, it is desirable that the liquid injected into the balloon can be heated to 40 ° C. to 100 ° C., and it is particularly preferable that the liquid can be heated to 40 ° C. to 80 ° C. As the heating module 66, a high frequency heater (heating wire) or the like can be used. The temperature sensor 67 is preferably a thermistor.
[0060]
  Aneurysm shape of this exampleCompletionThe operation of the blood vessel treatment instrument 60 will be described with reference to FIG.
  A stent 61 is placed on a blood vessel (aorta) 99 in which an aneurysm (aneurysm) 99a is formed using a normal method. Then, the intravascular insertion tool 62 is inserted from the femoral artery, and is arranged so that the substantially center of the balloon 65 is located near the distal end portion of the stent 61. This state is the state shown in FIG. Then, liquid is pressed into the lumen 68 from the liquid port 64 a of the connector 64, the balloon 65 is inflated, and the balloon 65 is brought into close contact with the distal end portion of the stent 61. Thereby, the adhesiveness of the front-end | tip part of the stent 61 and the blood vessel inner wall improves. Subsequently, a heating device (not shown) is operated to cause the heating module (heat generation module) to generate heat, thereby heating the liquid injected into the balloon. The temperature of the liquid is detected by the temperature sensor 67, and using this detection result, the heating is adjusted so that the liquid is not overheated. When the liquid is heated, the vicinity 99b of the upstream end portion of the aneurysm 99a is also heated through the stent 61, and is located on the outer surface of the distal end portion of the stent 61 and the inner surface (particularly 99c portion) of the blood vessel 99. When the blood is heated, coagulation occurs and it becomes thrombotic and hardened. Thereby, the so-called leak that blood passes between the outer surface of the stent 61 and the inner surface of the blood vessel and flows into the aneurysm forming portion can be prevented. Then, if necessary, the above heating operation may be performed on the downstream end of the stent 61 as well.
[0061]
  Next, the aneurysm shape shown in FIG.CompletionThe blood vessel treatment instrument 70 will be described.
  Aneurysm shapeCompletionThe blood vessel treatment instrument 70 is an aneurysm-shaped device.CompletionIt consists of a blood vessel stent 61 and an intravascular insertion tool 72. The intravascular insertion tool 72 includes an inflatable balloon 65, a flow path 68 for supplying liquid into the balloon 65, and a heating element that can be expanded in diameter by the balloon 65 and that heats the stent 61.71It has. Aneurysm shapeCompletionAs the blood vessel stent 61, the above-described various stents can be used.
[0062]
  The intravascular insertion tool 72 includes a tube main body 73 and a connector 64 fixed to the rear end thereof. A balloon 65 that can be inflated and deflated is fixed to the distal end of the tube body 73 in a liquid-tight manner. The outer surface of the balloon 65 is provided with a heating module 71 that is a coiled heating element that can be expanded by the balloon 65 and a temperature sensor 74 that is provided so as to come into contact with the heating module 71. The tube main body 73 includes two lumens 68 and 69 inside, and the lumens 68 and 69 are sealed by a tip member 91 fixed to the tip of the tube main body 73. Further, the outer surface of the tube main body 73 is provided with a side hole 92 for communicating the inside of the balloon 65 and the lumen 68, a side hole 75 for inserting the lead wire 93 of the heating module 71 and the lead wire 94 of the temperature sensor 74. Yes.
[0063]
  The connector 64 is electrically connected to the fluid port 64a communicating with the balloon expansion lumen 68 and the lead wire 93 of the heating module 71 and is connected to a heating device (not shown). And a connection part 97 for being electrically connected to the lead wire 94 of the temperature sensor 74 and being connected to a temperature detection device (not shown).
[0064]
  As the tube main body 73, what was demonstrated in the tube main body 63 mentioned above can be used conveniently. The length of the tube body 73 is 200 to 600 mm, more preferably 450 to 550 mm, the outer diameter is 1.0 to 5.0 mm, more preferably 1.15 to 4.0 mm, and the wall thickness is It is 0.1-0.4 mm, More preferably, it is 0.15-0.25 mm.
[0065]
  The balloon 65 can be inflated and deflated, and is configured to be in close contact with or folded on the outer periphery of the tube body when deflated. The material of the balloon 65 is preferably a material having a certain degree of plasticity and a hardness that can suppress significant volume fluctuations due to driving fluid pressure and blood pressure. For example, polyolefin such as polyethylene, polypropylene, ethylene-propylene copolymer, polyethylene terephthalate, etc. Polyester such as, polyvinyl chloride, ethylene-vinyl acetate copolymer, cross-linked ethylene-vinyl acetate copolymer, thermoplastic resin such as polyurethane, polyamide elastomer, silicone rubber, latex rubber and the like can be used.
[0066]
  Each end of the balloon 65 is fixed to the outer peripheral surface of the tube main body by, for example, adhesion (for example, heat fusion). Also, the size of the balloon needs to be able to contact the inner surface of the stent during expansion. Specifically, the size of the balloon 65 differs depending on the intended blood vessel site, but when used for the aorta, the outer diameter during expansion is 3 to 52 mm, preferably 4 to 42 mm. The length is preferably about 10 to 70 mm.
[0067]
  The coiled heating module 71 needs to have a shape or form that can be expanded by a balloon. In this embodiment, since it has a coil shape, the diameter is expanded by a balloon. The heating module 71 is preferably capable of generating heat at 40 ° C. to 100 ° C., and particularly preferably capable of generating heat at 40 ° C. to 80 ° C. As the heating module 71, a coiled heater (heating wire) or the like can be used. The temperature sensor 74 is preferably a thermistor, and the temperature sensor 74 is preferably in contact with the heating module.
[0068]
  Aneurysm shape of this exampleCompletionThe operation of the blood vessel treatment instrument 70 will be described with reference to FIG.
  A stent 61 is placed on a blood vessel (aorta) 99 in which an aneurysm (aneurysm) 99a is formed using a normal method. Then, the intravascular insertion tool 72 is inserted from the femoral artery, and is arranged so that the substantially center of the balloon 65 is located near the distal end of the stent. This state is shown in FIG. Then, liquid is pressed into the lumen 68 from the liquid port 64 a of the connector 64, the balloon 65 is expanded, the diameter of the heating module 71 is expanded, and the heating module 71 is brought into close contact with the distal end portion of the stent 61. Thereby, the adhesiveness of the front-end | tip part of the stent 61 and the blood vessel inner wall improves. Subsequently, a heating device (not shown) is operated to cause the heating module (heat generating module) to generate heat. The temperature of the heating module is detected by the temperature sensor 74, and the detection result is used to adjust the heating so that the heating module does not generate excessive heat. When the heating module generates heat, the vicinity of the upstream end portion of the aneurysm 99a is also heated through the stent 61, and the blood located on the outer surface of the distal end portion of the stent 61 and the inner surface of the blood vessel 99 (particularly 99c portion). When heated, it becomes coagulated and clots and hardens. Thereby, the so-called leak that blood passes between the outer surface of the stent 61 and the inner surface of the blood vessel and flows into the aneurysm forming portion can be prevented. Then, if necessary, the above heating operation may be performed on the downstream end of the stent 61 as well.
[0069]
  Next, the aneurysm shape shown in FIG.CompletionThe blood vessel treatment instrument 80 will be described.
Aneurysm shapeCompletionThe blood vessel treatment instrument 80 is an aneurysm-shaped device.CompletionIt consists of a blood vessel stent 61 and an intravascular insertion tool 82. The intravascular insertion tool 82 includes a first inflatable balloon 84, a flow path 85 for supplying liquid into the first balloon 84, and a first distance provided at a predetermined distance from the first balloon 84. Two balloons 86, a flow path 87 for supplying liquid into the second balloon 86, and laser irradiation means 102 including a heating laser irradiation unit 101 between the first balloon 84 and the second balloon 86, A blood removal passage 88 that opens between the first balloon 84 and the second balloon 86 is provided. Aneurysm shapeCompletionAs the blood vessel stent 61, the above-described various stents can be used.
[0070]
  The intravascular insertion tool 82 includes a tube main body 83 having a double tube structure except for the distal end portion, and a shaft 102 with a laser irradiation function that is rotatably accommodated in the tube main body 83.
  The tube main body 83 includes an inner tube portion 83b extending to the tip and an outer tube 83a that covers the inner tube portion except for the tip portion. The first balloon 84 is fixed in a liquid-tight manner to the distal end portion of the inner tube portion 83b, and the balloon 84 is formed on the flow path 85 formed in the inner tube portion 83b and the side surface of the distal end portion of the inner tube portion 83b. The side holes 85a communicate with each other. The second balloon 86 is fixed in a liquid-tight manner at a position slightly proximal to the distal end of the outer tube portion 83a. The balloon 86 has a flow path 87 formed in the outer tube portion 83a and the outer tube portion 83b. The side holes 87a are formed on the side surface of the tip of each other. The distance between the first balloon 84 and the second balloon 86 is preferably about 30 to 200 mm, and particularly preferably 50 to 150 mm. The tube main body 83 includes a blood removal passage 88 that opens between the first balloon 84 and the second balloon 86. In this embodiment, the blood removal passage 88 is provided.88Is provided with a side hole 88 a that opens at a position slightly distal to the second balloon 86.
[0071]
  And the shaft 102 with a laser irradiation function is rotatably accommodated in the cylindrical space 89 formed between the outer tube part 83a and the inner tube part 83b. Two laser irradiation units 101 are fixed to the tip of the shaft 102. Further, the outer tube portion at a position corresponding to the laser irradiation portion 101 is a window portion 105 formed of a material having laser transparency and laser durability. As such a material, a material excellent in laser light transmittance, such as polyolefin, polyester, polyamide, latex, and cellulose, is preferable.
[0072]
  As the tube main body 83, what was demonstrated in the tube main body 63 mentioned above can be used conveniently. The length of the tube body 83 is 200 to 600 mm, more preferably 450 to 550 mm, the outer diameter is 1.0 to 5.0 mm, more preferably 1.15 to 4.0 mm, and the wall thickness is It is 0.1-0.4 mm, More preferably, it is 0.15-0.25 mm.
[0073]
  The balloons 84 and 86 can be inflated and deflated, and are configured to be in close contact with or folded on the outer periphery of the tube body when deflated. The material of the balloons 84 and 86 is preferably a material having a certain degree of plasticity and a hardness that can suppress significant volume fluctuations due to driving fluid pressure or blood pressure. For example, polyolefins such as polyethylene, polypropylene, ethylene-propylene copolymer, Polyester such as polyethylene terephthalate, polyvinyl chloride, ethylene-vinyl acetate copolymer, cross-linked ethylene-vinyl acetate copolymer, thermoplastic resin such as polyurethane, polyamide elastomer, silicone rubber, latex rubber and the like can be used.
[0074]
  Both ends of the balloons 84 and 86 are fixed to the outer peripheral surface of the tube main body by, for example, adhesion (for example, heat fusion). In addition, the size of the balloons 84 and 86 needs to be able to contact the inner surface of the stent during expansion. Specifically, the sizes of the balloons 84 and 86 differ depending on the target blood vessel site, but when used for the aorta, the outer diameter upon expansion is 3 to 52 mm, preferably 4 to 42 mm. is there. The length is preferably about 10 to 70 mm.
[0075]
  As the laser irradiation unit 101, one capable of heating a blood vessel is used. As for the heating temperature of the blood vessel, the laser irradiation part is preferably capable of heating the blood vessel to 40 ° C. to 100 ° C., and particularly preferably capable of heating to 40 ° C. to 80 ° C. As the laser irradiation unit 101, an Nd: YAG laser, a holonium: YAG laser, or the like can be used.
[0076]
  Aneurysm shape of this exampleCompletionThe operation of the blood vessel treatment instrument 80 will be described with reference to FIG.
  A stent 61 is placed on a blood vessel (aorta) 99 in which an aneurysm (aneurysm) 99a is formed using a normal method. Then, the intravascular insertion tool 82 is inserted from the femoral artery, the first balloon 84 is on the upstream side of the aneurysm 99a, the second balloon 86 is on the downstream side of the aneurysm 99a, and the laser irradiation unit 101 is It arrange | positions so that it may become vicinity of the front-end | tip part of the stent 61. FIG. Then, liquid is injected from the flow path 85 and the flow path 87, the balloons 84 and 86 are inflated, and the balloons 84 and 86 are brought into close contact with the inner wall of the blood vessel. Subsequently, a suction means (for example, a syringe) (not shown) is connected to the blood removal flow path 88, and the blood located at the closed portion is removed by the first balloon 84 and the second balloon 86. This state is the figure14It is the state shown in.
[0077]
  Then, a laser irradiation apparatus (not shown) is operated to irradiate the laser near the distal end portion of the stent 61 from the laser irradiation unit 101. Thereby, the blood vessel inner wall of the laser irradiation site is heated, denatured and cured. Then, by rotating the shaft 102, a blood vessel portion denatured and cured in an annular shape by laser heating is formed. Then, if necessary, the above heating operation may be performed on the downstream end of the stent 61 as well.
[0078]
【The invention's effect】
  Aneurysm shape of the present inventionCompletionThe blood vessel stent is a tube-shaped structure, which is deformable into a first outer diameter and a second outer diameter larger than the first outer diameter, and a side surface of the structure. An aneurysm having a membrane encapsulatingCompletionA stent for blood vessels, the stent including a thrombus formation promoting portion.
[0079]
  Since this stent has a thrombus formation promoting part, thrombus formation in the gap between the host blood vessel and the stent is quick after placement of the stent, preventing blood from flowing into the aneurysm and fixing the stent and host blood vessel Can be improved.
[0080]
  In addition, the aneurysm shape of the present inventionCompletionThe blood vessel treatment device is a tube-shaped structure that is deformable into a first outer diameter and a second outer diameter that is larger than the first outer diameter. An aneurysm having a membrane encapsulating the sideCompletionVascular stent and aneurysm shapeCompletionAn intravascular insertion tool that can be inserted into the stent after being placed in a blood vessel and that has a heating mechanism for heating the blood vessel in the stent placement portion.
[0081]
  This aneurysm shapeCompletionSince the blood vessel treatment device includes a heating mechanism for heating the blood vessel of the stent placement portion,CompletionAfter placing the stent in the blood vessel, thrombus formation in the gap between the host blood vessel and the stent can be accelerated, blood can be prevented from flowing into the aneurysm, and the fixation between the stent and the host blood vessel can be improved. .
[Brief description of the drawings]
FIG. 1 shows an aneurysm shape of the present inventionCompletionIt is a whole perspective view which shows the Example of the stent for blood vessels.
FIG. 2 is a partially enlarged view of the stent shown in FIG.
FIG. 3 is a perspective view showing the configuration of the maintenance means (the structure is in a reduced diameter state) in the stent shown in FIG. 1;
4 is a perspective view showing a configuration (a structure is in a diameter-enlarged state) of a maintaining unit in the stent shown in FIG. 1. FIG.
FIG. 5 is a partial cross-sectional side view showing the operation of the maintaining means and the outer diameter expanding means in one embodiment of the stent of the present invention.
FIG. 6 is a partial cross-sectional side view showing the operation of the maintaining means and the outer diameter expanding means in one embodiment of the stent of the present invention.
FIG. 7 is a partial cross-sectional side view showing the operation of the maintaining means and the outer diameter expanding means in one embodiment of the stent of the present invention.
FIG. 8 is a partial cross-sectional side view showing the operation of the maintaining means and the outer diameter expanding means in one embodiment of the stent of the present invention.
FIG. 9 is a perspective view showing the configuration of one end of the outer diameter expanding means.
FIG. 10 shows an aneurysm shape of the present invention.CompletionIt is a whole perspective view which shows other Examples of the stent for blood vessels.
FIG. 11 shows an aneurysm shape of the present invention.CompletionIt is a whole perspective view which shows other Examples of the stent for blood vessels.
FIG. 12 shows an aneurysm shape of the present invention.CompletionIt is explanatory drawing for demonstrating the Example of the blood vessel treatment instrument.
FIG. 13 shows an aneurysm shape of the present invention.CompletionIt is explanatory drawing for demonstrating the other Example of the blood vessel treatment instrument.
FIG. 14 shows an aneurysm shape of the present invention.CompletionIt is explanatory drawing for demonstrating the other Example of the blood vessel treatment instrument.
[Explanation of symbols]
1 Aneurysm shapeCompletionVascular stent
60 AneurysmCompletionVascular treatment instrument
70 AneurysmCompletionVascular treatment instrument
80 AneurysmCompletionVascular treatment instrument

Claims (5)

A tube-shaped structure that is deformable into a first outer diameter and a second outer diameter that is larger than the first outer diameter, and a cylinder that encloses the side surface of the structure a blood vessel dilation type forming a vascular stent having a Jo film, the stent comprises a prothrombotic portions provided at both ends of the stent, blood plugging promotion section, the free ends of the myriad of yarn is formed by winding a braid type of fiber aggregate is exposed, and, in the prothrombotic unit for blood vessel dilation shaped formation vessel, characterized in that the blood coagulation factor adhesion enhancing substance is deposited Stent. Wherein the blood component adhesion enhancing substance is albumin, collagen, gelatin, globulin is at least one of the blood vessel dilation type formed vascular stent according to claim 1. The stent, blood vessel dilation type formed vascular stent of claim 1, further comprising a disposed et the prothrombotic portion on the side surface near the center of the stent. The structure has a maintaining means for maintaining the outer diameter of the structure at the second outer diameter, and the maintaining means has a telescopic guide tube and an outer diameter smaller than the inner diameter of the guide tube. A rod inserted into the guide tube, and the structure has the first outer diameter when the guide tube is in an extended state, and the guide tube contracts by pulling the rod, The aneurysm-forming blood vessel stent according to claim 1 or 2, wherein the structure has a diameter that becomes the second outer diameter. The aneurysm-forming blood vessel stent according to claim 4, wherein the guide tube is formed of a coil made of an elastic material.

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