JP2005177094A - Guidewire - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a guidewire with excellent flexibility and maneuverability of which the bonding strength between the first wire and the second wire is superior. <P>SOLUTION: The guidewire 1 is equipped with a main body of the wire 10 which is constituted with the linear first wire 2 disposed at a distal end side and the linear second wire 3 connected to a proximal end side of the first wire. A coil 4 with an X-ray imaging capacity is disposed at a periphery of the distal end section of the first wire 2. The first wire 2 and the second wire 3 are preferably connected by welding to form a stratified connection boundary section 14. The connection boundary section 14 has a curved surface and particularly forms a curved convex surface which becomes more convex toward the proximal end direction of the main body of the wire 10. Also, the curved surface of the connection boundary section 14 has a shape which is symmetric with respect to the central axis of the main body of the wire 10 (a shape of a body of rotation around the central axis of the main body of the wire 10). A covering layer 5 is formed at the periphery of the main body of the wire 10. <P>COPYRIGHT: (C)2005,JPO&NCIPI

Description

  The present invention relates to a guide wire, and particularly to a guide wire used when a catheter is introduced into a body cavity such as a blood vessel.

  The guide wire can be used for the treatment of a site where surgical operation is difficult, such as PTCA (Percutaneous Transluminal Coronary Angioplasty), or for the purpose of minimally invasive to the human body, Used to guide catheters used for examinations such as angiography. A guide wire used for PTCA surgery is inserted to the vicinity of the target vascular stenosis portion together with the balloon catheter with the tip of the guide wire protruding from the tip of the balloon catheter. Guide to near.

  The blood vessel is intricately curved, and the guide wire used to insert the balloon catheter into the blood vessel has flexibility and resilience to moderate bending, and pushability to transmit the operation at the proximal end to the distal side. In addition, torque transmission properties (collectively referred to as “operability”) and kink resistance (bending resistance) are required. Among these characteristics, as a structure for obtaining moderate flexibility, a structure having a metal coil having flexibility for bending around a thin tip core material of a guide wire, and for providing flexibility and resilience There is a guide wire using a super elastic wire such as Ni-Ti as a core material.

  In the conventional guide wire, the core material is substantially composed of one material, and a material having a relatively high elastic modulus is used in order to improve the operability of the guide wire. Tended to lose its flexibility. Further, if a material having a relatively low elastic modulus is used in order to obtain the flexibility of the distal end portion of the guide wire, the operability on the proximal end side of the guide wire is lost. Thus, it has been difficult to satisfy the required flexibility and operability with one kind of core material.

  In order to improve such a defect, for example, a Ni-Ti alloy wire is used as a core material, and heat treatment is performed on the distal end side and the proximal end side under different conditions to increase the flexibility of the distal end portion. A guide wire with increased rigidity has been proposed (see, for example, Patent Document 1).

  However, there is a limit to the control of flexibility by such heat treatment, and even if sufficient flexibility is obtained at the distal end portion, there is a case where satisfactory rigidity is not always obtained at the proximal end side.

  Further, a flexible first wire disposed on the distal end side, a second wire having high rigidity disposed on the proximal end side, a first wire and the second wire are connected to each other, and a groove and There has been proposed a guide wire that includes a tubular connecting member having a slit, and the connecting member is configured such that rigidity gradually increases from the distal end side toward the proximal end side (see, for example, Patent Document 2).

  In such a guide wire, wires having desired characteristics can be arranged on the distal end side and the proximal end side, respectively. However, since both wires are connected via a tubular connecting member, the bonding strength of both wires can be increased. There is a problem that the torque cannot be increased and the torque transmission cannot be sufficiently obtained. In addition, there is a manufacturing problem that it takes time to connect the wires.

Japanese Examined Patent Publication No. 4-60675 Japanese Patent Laid-Open No. 10-118055

  An object of the present invention is to provide a bonding strength between the first wire and the second wire while sufficiently securing flexibility and operability by bonding and using the first wire and the second wire having different physical characteristics. It is to provide a high guide wire.

Such an object is achieved by the present inventions (1) to (16) below.
(1) A linear first wire arranged on the distal end side and a linear second wire joined to the proximal end of the first wire and made of a material having a higher elastic modulus than the constituent material of the first wire. A wire body comprising a wire,
A guide wire characterized in that a joining boundary portion between the first wire and the second wire has a curved surface shape and is substantially symmetrical with respect to a central axis of the wire body.

  (2) The guide wire according to (1), wherein the joining boundary portion has a curved convex shape that is convex toward the proximal direction of the wire body.

  (3) The guide wire according to (1) or (2), wherein the first wire and the second wire are joined by welding.

  (4) The guide wire according to any one of (1) to (3), wherein the joint boundary portion is formed in a layer shape.

  (5) The guide wire according to (4), wherein a thickness of the layered boundary is 0.001 to 100 μm.

  (6) The guide wire according to any one of (1) to (5), wherein an outer diameter of the wire main body at the bonding boundary portion is larger than an outer diameter of a proximal end side and a distal end side portion of the bonding boundary portion. .

  (7) The guide wire according to any one of (1) to (6), further including a coating layer provided on an outer periphery of the wire body so as to cover at least the joining boundary portion.

  (8) The guide wire according to (7), wherein the coating layer is made of a material that can reduce friction.

  (9) The guide wire according to (7) or (8), wherein the coating layer is made of a thermoplastic elastomer, a silicone resin, or a fluorine resin.

  (10) The guide wire according to any one of (7) to (9), wherein the coating layer has an average thickness of 1 to 30 μm.

  (11) The guide wire according to any one of (1) to (10), wherein the wire body includes an outer diameter gradually decreasing portion whose outer diameter gradually decreases toward the distal end.

  (12) The guide wire according to any one of (1) to (11), wherein the guide wire includes a spiral coil that covers at least a portion on a distal end side of the first wire.

  (13) The guide wire according to any one of (1) to (12), wherein a common metal element is contained in each of the constituent materials of the first wire and the second wire.

  (14) The guide wire according to any one of (1) to (13), wherein the first wire is made of a superelastic alloy.

  (15) The guide wire according to any one of (1) to (14), wherein the second wire is made of stainless steel or a Co-based alloy.

  (16) The guide wire according to (15), wherein the Co-based alloy is a Co—Ni—Cr-based alloy.

  According to the guide wire of the present invention, it is possible to sufficiently ensure flexibility and operability by using the first wire and the second wire, which have different physical characteristics, in addition to the first wire and the second wire. Bonding strength with 2 wires is high.

  For this reason, even when a stress such as bending or tension acts on the guide wire, the joint between the first wire and the second wire is not detached, and the torsional torque or pushing force from the proximal end side to the distal end side does not occur. Can be transmitted reliably.

  Hereinafter, the guide wire of the present invention will be described in detail based on preferred embodiments shown in the accompanying drawings.

  FIG. 1 is a longitudinal sectional view showing an embodiment of a guide wire of the present invention, and FIG. 2 is an enlarged longitudinal sectional view showing the vicinity of a bonding boundary portion of a wire body in the guide wire of the present invention. For convenience of explanation, the right side in FIGS. 1 and 2 is referred to as “base end”, and the left side is referred to as “tip”. Further, in FIG. 1, for the sake of easy understanding, the length direction of the guide wire is shortened and the thickness direction of the guide wire is exaggerated and schematically illustrated. The ratio between the length direction and the thickness direction is actually shown. Is different.

  A guide wire 1 shown in FIG. 1 is a catheter guide wire used by being inserted into a catheter, and includes a first wire 2 disposed on the distal end side and a second wire disposed on the proximal end side of the first wire 2. A wire body 10 formed by joining (connecting) the wire 3 and a spiral coil 4 are provided. The total length of the guide wire 1 is not particularly limited, but is preferably about 200 to 5000 mm. Further, the outer diameter of the wire body 10 (the outer diameter of the portion having a constant outer diameter) is not particularly limited, but it is usually preferably about 0.2 to 1.4 mm.

  The 1st wire 2 is comprised with the wire which has elasticity. Although the length of the 1st wire 2 is not specifically limited, It is preferable that it is about 20-1000 mm.

  In the present embodiment, the first wire 2 has a portion having a constant outer diameter and a portion (outer diameter gradually decreasing portion) in which the outer diameter gradually decreases in the distal direction. The latter may be one place or two places or more. In the illustrated embodiment, the outer diameter gradually decreasing portions 15 and 16 are provided.

  By having such outer diameter gradually decreasing portions 15, 16, the rigidity (bending rigidity, torsional rigidity) of the first wire 2 can be gradually decreased toward the distal end direction. Good flexibility can be obtained at the distal end portion, the followability to blood vessels and safety can be improved, and bending and the like can also be prevented.

  In the illustrated configuration, the outer diameter gradually decreasing portions 15 and 16 are each formed in a part of the first wire 2 in the longitudinal direction, but the entire first wire 2 may constitute an outer diameter gradually decreasing portion. . Further, the taper angle (the reduction rate of the outer diameter) of the outer diameter gradually decreasing portions 15 and 16 may be constant along the longitudinal direction of the wire, or there may be a portion that varies along the longitudinal direction. For example, a portion where the taper angle (reduction rate of the outer diameter) is relatively large and a portion where the taper angle is relatively small may be alternately formed a plurality of times.

  Further, unlike the illustrated configuration, the proximal end of the outer diameter gradually decreasing portion 16 is located in the middle of the second wire 3, that is, the outer diameter gradually decreasing portion 16 is connected to the joining boundary portion (welding between the first wire 2 and the second wire 3 Part) 14 may be formed.

  The constituent material of the 1st wire 2 is not specifically limited, For example, various metal materials, such as stainless steel, can be used, Among them, the alloy (a superelastic alloy is included) which shows pseudoelasticity especially among these. preferable. More preferably, it is a superelastic alloy. Since the superelastic alloy is relatively flexible, has a resilience, and is difficult to bend, the guide wire 1 can be sufficiently formed at the tip side by configuring the first wire 2 with the superelastic alloy. Flexibility and bendability can be obtained, followability to a complicatedly bent / bent blood vessel can be improved, more excellent operability can be obtained, and even if the first wire 2 repeats bending / bending deformation, Since the bend crease is not attached due to the resilience provided in the first wire 2, it is possible to prevent a decrease in operability due to the bend crease attached to the first wire 2 during use of the guide wire 1.

  Pseudoelastic alloys include any shape of stress-strain curve due to tension, including those that can measure the transformation point of As, Af, Ms, Mf, etc., and those that cannot be measured. However, everything that returns to its original shape by removing stress is included.

  The preferred composition of the superelastic alloy is Ni-Ti alloy such as Ni-Ti alloy of 49-52 atomic% Ni, Cu-Zn alloy of 38.5-41.5 wt% Zn, 1-10 wt% X Cu-Zn-X alloy (X is at least one of Be, Si, Sn, Al, and Ga), 36-38 atomic% Al-Ni-Al alloy, and the like. Of these, the Ni-Ti alloy is particularly preferable. In addition, the superelastic alloy represented by the Ni-Ti type alloy is excellent also in the adhesiveness of the coating layer 5 mentioned later.

  The distal end of the second wire 3 is connected (coupled) to the proximal end of the first wire 2 by, for example, welding. The 2nd wire 3 is comprised with the wire which has elasticity. Although the length of the 2nd wire 3 is not specifically limited, It is preferable that it is about 20-4800 mm.

  The second wire 3 is usually made of a material having an elastic modulus (Young's modulus (longitudinal elastic modulus), rigidity (transverse elastic modulus), volume elastic modulus) different from that of the first wire 2. It is preferable to be made of a material having a larger elastic modulus than 1 wire 2. Thereby, moderate rigidity (bending rigidity, torsional rigidity) is obtained for the second wire 3, the guide wire 1 becomes so-called strong and the pushability and torque transmission performance are improved, and more excellent insertion operability. Is obtained.

  The constituent material (material) of the second wire 3 is not particularly limited, and is stainless steel (for example, SUS304, SUS303, SUS316, SUS316L, SUS316J1, SUS316J1L, SUS405, SUS430, SUS434, SUS444, SUS429, SUS430F, SUS302, etc. All types), various metal materials such as piano wire, cobalt-based alloy, and pseudoelastic alloy can be used.

  Among these, the cobalt-based alloy has a high elastic modulus when used as a wire and has an appropriate elastic limit. For this reason, the 2nd wire 3 comprised by the cobalt type alloy has the outstanding outstanding torque transmission, and it is hard to produce problems, such as buckling. Any cobalt-based alloy may be used as long as it contains Co as a constituent element, but it contains Co as a main component (Co-based alloy: Co content in the elements constituting the alloy) Is preferable, and a Co—Ni—Cr alloy is more preferably used. By using an alloy having such a composition as a constituent material of the second wire 3, the above-described effects become more remarkable. In addition, an alloy having such a composition has a high elastic modulus and can be cold-formed even as a high elastic limit, and by reducing the diameter while sufficiently preventing buckling from occurring due to the high elastic limit. And can have sufficient flexibility and rigidity to be inserted into a predetermined portion.

  Examples of the Co—Ni—Cr alloy include alloys having a composition of 28 to 50 wt% Co-10 to 30 wt% Ni-10 to 30 wt% Cr—remainder Fe, and a part of the other elements (substitution elements). Alloys substituted with are preferred. The inclusion of a substitution element exhibits a unique effect depending on the type. For example, the strength of the second wire 3 can be further improved by including at least one selected from Ti, Nb, Ta, Be, and Mo as the substitution element. In addition, when an element other than Co, Ni, and Cr is included, the content (of the entire substituted element) is preferably 30 wt% or less.

  Further, a part of Co, Ni, and Cr may be substituted with other elements. For example, a part of Ni may be substituted with Mn. Thereby, the further improvement of workability etc. can be aimed at, for example. Further, a part of Cr may be replaced with Mo and / or W. Thereby, the further improvement of an elastic limit, etc. can be aimed at. Among Co—Ni—Cr alloys, Co—Ni—Cr—Mo alloys containing Mo are particularly preferable.

  As a specific composition of the Co—Ni—Cr alloy, for example, [1] 40 wt% Co-22 wt% Ni-25 wt% Cr-2 wt% Mn—0.17 wt% C-0.03 wt% Be—balance Fe [2] 40 wt% Co-15 wt% Ni-20 wt% Cr-2 wt% Mn-7 wt% Mo-0.15 wt% C-0.03 wt% Be-balance Fe, [3] 42 wt% Co-13 wt% Ni- 20 wt% Cr-1.6 wt% Mn-2 wt% Mo-2.8 wt% W-0.2 wt% C-0.04 wt% Be-balance Fe, [4] 45 wt% Co-21 wt% Ni-18 wt% Cr- 1 wt% Mn-4 wt% Mo-1 wt% Ti-0.02 wt% C-0.3 wt% Be-balance Fe, [5] 34 wt% Co-21 wt% Ni-14 wt% Cr-0.5 wt% Mn-6w % Mo-2.5wt% Nb-0.5wt% Ta- balance being Fe, and the like. The Co—Ni—Cr alloy referred to in the present invention is a concept that includes these alloys.

  Moreover, when stainless steel is used as the constituent material of the second wire 3, the guide wire 1 can obtain better pushability and torque transmission.

  In the present invention, the first wire 2 and the second wire 3 are preferably made of different alloys, and the first wire 2 is made of a material having a smaller elastic modulus than the constituent material of the second wire 3. Is preferred. As a result, the guide wire 1 has excellent flexibility at the distal end portion and abundant rigidity (bending rigidity, torsional rigidity) at the proximal end portion. As a result, the guide wire 1 obtains excellent pushability and torque transmission and secures good operability, while obtaining good flexibility and restoration on the distal end side, followability to blood vessels, and safety. Will improve.

  As a specific combination of the first wire 2 and the second wire 3, the first wire 2 is made of a superelastic alloy (particularly Ni—Ti alloy), and the second wire 3 is made of a Co-based alloy ( In particular, it is particularly preferable to use a Co—Ni—Cr alloy) or stainless steel (Fe—Cr—Ni alloy). Thereby, the effect mentioned above becomes further remarkable. Another reason why such a combination is preferable is that a common metal element (for example, Ni) is contained in each of the constituent materials of the first wire 2 and the second wire 3. Thereby, the joint strength of the joint boundary part 14 of both becomes still higher.

  The outer diameter of the second wire 3 is generally constant, but the outer diameter gradually decreases in the vicinity of the distal end of the second wire 3 (near the proximal end side of the joining boundary portion 14). 18. Due to the presence of the outer diameter gradually decreasing portion 18, the physical characteristics from the second wire 3 to the first wire 2, particularly the elasticity, changes smoothly, and excellent pushability and torque transmission before and after the joint boundary portion 14 are exhibited. In addition, kink resistance is also improved.

  The coil 4 is a member formed by spirally winding a wire (thin wire), and is installed so as to cover a portion on the distal end side of the first wire 2. In the configuration shown in the drawing, the portion on the distal end side of the first wire 2 is inserted through a substantially central portion inside the coil 4. Further, the distal end portion of the first wire 2 is inserted in a non-contact manner with the inner surface of the coil 4. The joining boundary portion 14 is located closer to the base end side than the base end of the coil 4.

  In the configuration shown in the figure, the coil 4 has a slight gap between the spirally wound wires in a state where no external force is applied, but unlike the illustration, the coil 4 is spiraled in a state where no external force is applied. Wires wound in a shape may be densely arranged without a gap.

  The coil 4 is preferably made of a metal material. Examples of the metal material constituting the coil 4 include stainless steel, superelastic alloy, cobalt-based alloy, noble metals such as gold, platinum, tungsten, and alloys containing these (for example, platinum-iridium alloy). In particular, when the guide wire 1 is made of an X-ray opaque material such as a noble metal, X-ray contrast can be obtained in the guide wire 1, and the guide wire 1 can be inserted into the living body while confirming the position of the tip under X-ray fluoroscopy. It is possible and preferable. Further, the coil 4 may be composed of different materials on the distal end side and the proximal end side. For example, the distal end side may be constituted by a coil made of an X-ray opaque material, and the proximal end side may be constituted by a coil made of a material that relatively transmits X-rays (such as stainless steel). The total length of the coil 4 is not particularly limited, but is preferably about 5 to 500 mm.

  The proximal end portion and the distal end portion of the coil 4 are fixed to the first wire 2 by fixing materials 11 and 12, respectively. Further, an intermediate portion (position near the tip) of the coil 4 is fixed to the first wire 2 by a fixing material 13. The fixing materials 11, 12 and 13 are made of solder (brazing material). The fixing materials 11, 12 and 13 are not limited to solder, and may be adhesives. Moreover, the fixing method of the coil 4 is not limited to a fixing material, and for example, welding may be used. In order to prevent damage to the inner wall of the blood vessel, the distal end surface of the fixing material 12 is preferably rounded.

  In the present embodiment, since such a coil 4 is installed, the first wire 2 is covered with the coil 4 and has a small contact area, so that the sliding resistance can be reduced. The operability of 1 is further improved.

  In the case of the present embodiment, the coil 4 has a circular cross section of the wire. However, the present invention is not limited to this, and the cross section of the wire is, for example, elliptical or quadrangular (particularly rectangular). Also good.

  It is preferable that the 1st wire 2 and the 2nd wire 3 which comprise the guide wire main body 10 are connected and fixed by welding. Accordingly, a high bonding strength can be obtained at the bonding boundary portion (welded portion) 14 between the first wire 2 and the second wire 3 by a simple method, and thus the guide wire 1 is torsional torque from the second wire 3. The pushing force is reliably transmitted to the first wire 2.

  As shown in FIG. 2, such a joining boundary portion 14 has a layer shape (not only a visual layer shape but also a conceptual layer shape, including, for example, a significant change in the content of components). . The thickness of this layer is preferably about 0.001 to 100 μm, more preferably about 0.1 to 15 μm, and more preferably about 0.3 to 2 μm. The thickness of this layer may be partially thick, but is preferably substantially the same. By forming the joining boundary portion 14 in a layer shape having such a thickness, higher joining strength can be obtained.

  In FIG. 2, for easy understanding, the interface between the joining boundary portion 14 that forms a layer and the material of the first wire 2 and the material of the second wire 3 is clearly shown. None of them may have a clear boundary surface.

  The joining boundary portion 14 joined by welding has, in its layer, a component (metal element) in the metal material constituting the first wire 2 and a component (metal element) in the metal material constituting the second wire 3. Are mixed. In other words, the composition of the first wire 2, the bonding boundary portion 14, the second wire 3, and the material constituting the first wire 2, the bonding boundary portion 14, and the second wire 3 change gradually (continuously).

  For example, when the first wire 2 is made of a Ni—Ti alloy and the second wire 3 is made of stainless steel (Fe—Cr—Ni alloy), the second wire 3 side is formed in the joining boundary portion 14. Fe and Cr tend to decrease toward the first wire 2 side, and Ni and Ti tend to decrease from the first wire 2 side toward the second wire 3 side.

  As described above, by having a change in the composition (containing component) before and after the joining boundary portion 14, even higher joining strength can be obtained.

  Note that the content of the component (metal element) may change abruptly in the vicinity of the interface between the layered joint boundary 14 and the material of the first wire 2 and the material of the second wire 3.

  The method for welding the first wire 2 and the second wire 3 is not particularly limited, and examples thereof include friction welding, spot welding using a laser, butt resistance welding such as butt seam welding, and the like. Butt resistance welding is particularly preferred because high joint strength is obtained.

  Such a joining boundary portion 14 has a curved surface shape. In particular, it has a curved convex shape (dish shape) that is convex toward the proximal direction of the wire body 10. Further, the curved surface of the joining boundary portion 14 has a shape that is substantially symmetric with respect to the central axis of the wire body 10. That is, the curved surface of the joining boundary portion 14 has a rotating body shape centered on the central axis of the wire body 10. As a rotating body shape of the joining boundary part 14, other than a dish shape, for example, a spherical shape, a paraboloid shape, or a shape similar to these shapes can be cited.

  The following effects are acquired because the joining boundary part 14 is such a shape. That is, since the joining boundary portion 14 has a curved surface shape, the joining area becomes larger than that of the flat surface, and the effect of dispersing stress with respect to bending is produced, so that high joining strength can be obtained. Further, since the curved surface of the joining boundary portion 14 is symmetric with respect to the central axis of the wire body 10, the torque is evenly distributed from the second wire 3 to the first wire 2 when the wire body 10 is twisted. Can be transmitted (without bias). This contributes to improved operability.

  The outer diameter at the bonding boundary portion 14 of the wire main body 10 is larger than the outer diameters of the proximal end side and distal end side portions of the bonding boundary portion 14. That is, the predetermined region including the bonding boundary portion 14 of the wire body 10 has the protruding portion 17 that slightly protrudes (raises) in the outer peripheral direction. With such a configuration, the bonding area of the bonding boundary portion 14 can be increased, so that the bonding strength is improved, and the torsional torque and the pushing force from the second wire 3 are more reliably applied to the first wire 2. Can communicate.

  Moreover, by having the protrusion part 17, it becomes possible to visually recognize the location where the junction boundary part 14 exists more easily under X-ray fluoroscopy, for example. As a result, by confirming the X-ray fluoroscopic image, it is possible to easily and reliably grasp the progress of the guide wire 1 and the catheter in the blood vessel and the like, which contributes to shortening of the treatment time and improvement of safety.

  Although the height of the protrusion part 17 is not specifically limited, It is preferable that it is about 1 micrometer-0.4 mm, and it is more preferable that it is about 5-50 micrometers. If the height of the protruding portion 17 is less than the lower limit value, the effect of providing the protruding portion 17 may not be sufficiently exhibited depending on the constituent materials of the first wire 2 and the second wire 3. On the other hand, when the height of the protruding portion 17 exceeds the upper limit value, the inner diameter of the lumen to be inserted into the balloon catheter is determined, so that the outside of the second wire 3 on the proximal end side is compared with the height of the protruding portion 17. In some cases, the diameter of the second wire 3 must be reduced, and it may be difficult to fully exhibit the physical properties of the second wire 3.

Such a protrusion 17 is formed as follows, for example.
The first wire 2 and the second wire 3 are brought into pressure contact with the proximal end of the first wire 2 and the distal end of the second wire 3 while applying a predetermined voltage by, for example, a butt welder. As a result of this pressure contact, a molten layer is formed at the contact portion, and when the molten layer is cooled and solidified, a joining boundary portion 14 is formed, and the first wire 2 and the second wire 3 are firmly joined. During this welding, a raised portion having a large outer diameter is formed in a predetermined region including the joining boundary portion 14 (for example, a range of about 0.1 to 5 mm before and after the joining boundary portion 14). The protruding portion 17 is formed by appropriately removing (deleting) the raised portion to adjust the shape. The outer peripheral surface of the protrusion 17 can be a substantially smooth surface. Examples of the method for removing (shaping) the raised portion include chemical treatment such as grinding, polishing, and etching.

  As shown in FIG. 1, the wire body 10 has a coating layer 5 that covers all or part of the outer peripheral surface (outer surface) (not shown in FIG. 2). The covering layer 5 can be formed for various purposes. As an example, the coating layer 5 reduces the friction (sliding resistance) of the guide wire 1 and improves the slidability, thereby improving the operability of the guide wire 1. May improve.

  The covering layer 5 is preferably provided so as to cover at least the outer periphery of the bonding boundary portion 14. As described above, since there is a change (step) in the outer diameter of the wire body 10 in the vicinity of the bonding boundary portion 14, the outer diameter change is offset or mitigated by covering with the coating layer 5, and in the vicinity of the bonding boundary portion 14. The outer diameter of the guide wire 1 can be made substantially uniform. As a result, the operability of moving the guide wire 1 in the longitudinal direction can be improved.

  For the purpose as described above, the coating layer 5 is preferably made of a material capable of reducing friction. Thereby, the frictional resistance (sliding resistance) with the inner wall of the catheter used together with the guide wire 1 is reduced, the slidability is improved, and the operability of the guide wire 1 in the catheter becomes better. Further, since the sliding resistance of the guide wire 1 is lowered, when the guide wire 1 is moved and / or rotated in the catheter, the guide wire 1 is kinked (bent) or twisted, particularly in the vicinity of the joint boundary 14. And twist can be more reliably prevented.

  Examples of materials that can reduce such friction include polyolefins such as polyethylene and polypropylene, polyvinyl chloride, polyesters (PET, PBT, etc.), polyamides, polyimides, polyurethanes, polystyrenes, polycarbonates, silicone resins, fluorine resins ( PTFE, ETFE, etc.) or a composite material thereof.

  In particular, when a fluorine-based resin (or a composite material containing the same) is used, the frictional resistance (sliding resistance) between the guide wire 1 and the inner wall of the catheter is more effectively reduced, and slidability is achieved. And the operability of the guide wire 1 in the catheter becomes better. In addition, this makes it possible to more reliably prevent kinking (bending) and twisting of the guide wire 1, particularly kinking and twisting in the vicinity of the welded portion, when the guide wire 1 is moved and / or rotated in the catheter.

  Further, when a fluororesin (or a composite material containing the same) is used, the wire main body 10 is usually coated with the resin material heated by a method such as baking or spraying. Thereby, the adhesiveness between the wire body 10 and the coating layer 5 is particularly excellent.

  Further, when the coating layer 5 is made of a silicone resin (or a composite material containing the same), the wire body can be formed without heating when the coating layer 5 is formed (covered on the wire body 10). Thus, the coating layer 5 that is firmly and firmly adhered to the coating 10 can be formed. That is, when the coating layer 5 is made of a silicone resin (or a composite material containing the same), a reaction-curing material or the like can be used, so that the coating layer 5 can be formed at room temperature. it can. Thus, by forming the coating layer 5 at room temperature, the coating can be easily performed, and the guide wire is maintained in a state in which the bonding strength between the first wire 2 and the second wire 3 in the welded portion 14 is sufficiently maintained. Can be operated.

  Other preferable examples of the material that can reduce friction include a hydrophilic material or a hydrophobic material. Of these, hydrophilic materials are particularly preferable.

  Examples of the hydrophilic material include cellulose-based polymer materials, polyethylene oxide-based polymer materials, and maleic anhydride-based polymer materials (for example, maleic anhydride copolymers such as methyl vinyl ether-maleic anhydride copolymer). ), Acrylamide polymer materials (for example, polyacrylamide, block copolymer of polyglycidyl methacrylate-dimethylacrylamide (PGMA-DMAA)), water-soluble nylon, polyvinyl alcohol, polyvinylpyrrolidone and the like.

  In many cases, such a hydrophilic material exhibits lubricity by wetting (water absorption) and reduces frictional resistance (sliding resistance) with the inner wall of the catheter used together with the guide wire 1. Thereby, the slidability of the guide wire 1 is improved, and the operability of the guide wire 1 in the catheter becomes better.

  The covering layer 5 can also be provided for the purpose of improving safety when the guide wire 1 is inserted into a blood vessel. For this purpose, the covering layer 5 is preferably made of a material (soft material) rich in flexibility.

  Examples of such flexible materials include polyolefins such as polyethylene and polypropylene, polyvinyl chloride, polyester (PET, PBT, etc.), polyamide, polyimide, polyurethane, polystyrene, silicone resin, polyurethane elastomer, polyester elastomer, polyamide Examples thereof include thermoplastic elastomers such as elastomers, various rubber materials such as latex rubber and silicone rubber, or composite materials in which two or more thereof are combined.

  In particular, when the covering layer 5 is made of a thermoplastic elastomer such as polyurethane elastomer or various rubber materials, the flexibility of the distal end portion of the guide wire 1 is further improved. It is possible to more reliably prevent damage to the inner wall and the like, and the safety is extremely high.

  Such a coating layer 5 may be a laminate of two or more layers, and the composition of the material constituting the coating layer 5 may be different depending on the location where the wire body 10 is formed. For example, the constituent material of the coating layer 5 may be different between the portion covering the bonding boundary portion 14 and the other portion. Further, the tip portion of the guide wire 1 (for example, the portion on the tip side from the outer diameter gradually decreasing portion 16) is made of the above-described flexible material to improve safety, and other portions reduce the above-described friction. It is possible to improve operability by using a material that can be used.

  The thickness of the coating layer 5 is not particularly limited, and is appropriately determined in consideration of the purpose of forming the coating layer 5, the constituent material, the forming method, and the like. Usually, the thickness (average) is about 1 to 30 μm. And is more preferably about 2 to 15 μm. If the thickness of the coating layer 5 is too thin, the purpose of forming the coating layer 5 may not be sufficiently exhibited, the peeling of the coating layer 5 may occur, and the thickness of the coating layer 5 is too thick. Then, the physical characteristics of the wire body 10 may be affected, and the coating layer 5 may be peeled off.

  In the present invention, the outer peripheral surface (surface) of the wire body 10 can be subjected to a treatment (chemical treatment, heat treatment, etc.) for improving the adhesion of the coating layer 5 or the adhesion of the coating layer 5 can be improved. An intermediate layer can also be provided.

  FIG. 3 and FIG. 4 are diagrams each showing a use state when the guide wire 1 of the present invention is used in PTCA surgery.

  3 and 4, reference numeral 40 denotes an aortic arch, reference numeral 50 denotes a right coronary artery of the heart, reference numeral 60 denotes a right coronary artery opening, and reference numeral 70 denotes a vascular stenosis (lesion). Reference numeral 30 is a guiding catheter for reliably guiding the guide wire 1 from the femoral artery to the right coronary artery, and reference numeral 20 is a balloon catheter for constriction portion expansion having a balloon 201 that can be expanded and contracted at its distal end. . The following operations are performed under fluoroscopy.

  As shown in FIG. 3, the distal end of the guide wire 1 is projected from the distal end of the guiding catheter 30 and inserted into the right coronary artery 50 through the right coronary artery opening 60. Further, the guide wire 1 is advanced, inserted into the right coronary artery 50 from the distal end, and stopped at a position where the distal end exceeds the vascular stenosis 70. Thereby, the passage of the balloon catheter 20 is secured. At this time, the joining boundary portion 14 of the guide wire 1 is located on the descending aorta side (in vivo) of the aortic arch 40.

  Next, as shown in FIG. 4, the distal end of the balloon catheter 20 inserted from the proximal end side of the guide wire 1 is projected from the distal end of the guiding catheter 30 and further advanced along the guide wire 1 to open the right coronary artery opening. It is inserted into the right coronary artery 50 from the part 60 and stops when the balloon 201 reaches the position of the vascular stenosis part 70.

  Next, a balloon expansion fluid is injected from the proximal end side of the balloon catheter 20 to expand the balloon 201 and expand the vascular stenosis part 70. By doing so, deposits such as cholesterol deposited on the blood vessels of the blood vessel stenosis part 70 are physically spread and the blood flow inhibition can be eliminated.

  As mentioned above, although the guide wire of this invention was demonstrated based on embodiment of illustration, this invention is not limited to this, Each part which comprises a guide wire is arbitrary structures which can exhibit the same function. Can be substituted. Moreover, arbitrary components may be added.

  Moreover, the use of the guide wire of the present invention is not limited to the case where it is used in the PTCA operation described above.

It is a longitudinal cross-sectional view which shows embodiment of the guide wire of this invention. It is a longitudinal cross-sectional view which expands and shows the junction boundary part vicinity of the wire main body in the guide wire of this invention. It is a schematic diagram for demonstrating the usage example of the guide wire of this invention. It is a schematic diagram for demonstrating the usage example of the guide wire of this invention.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Guide wire 10 Wire main body 2 1st wire 3 2nd wire 4 Coil 5 Coating layer 11, 12, 13 Fixing material 14 Joining boundary part (welding part)
DESCRIPTION OF SYMBOLS 15 Outer diameter decreasing part 16 Outer diameter decreasing part 17 Protrusion part 18 Outer diameter decreasing part 20 Balloon catheter 201 Balloon 30 Guiding catheter 40 Aortic arch 50 Right coronary artery 60 Right coronary artery opening 70 Vascular constriction part

Claims (10)

A linear first wire disposed on the distal end side, and a linear second wire joined to a proximal end of the first wire and made of a material having a higher elastic modulus than the constituent material of the first wire A wire body with
A guide wire characterized in that a joining boundary portion between the first wire and the second wire has a curved surface shape and is substantially symmetrical with respect to a central axis of the wire body.   The guide wire according to claim 1, wherein the joining boundary portion has a curved convex shape that is convex toward the proximal direction of the wire body.   The guide wire according to claim 1 or 2, wherein the first wire and the second wire are joined by welding.   The guide wire according to any one of claims 1 to 3, wherein the joining boundary portion has a layer shape.   5. The guide wire according to claim 4, wherein a thickness of the layered joint boundary portion is 0.001 to 100 μm.   The guide wire according to any one of claims 1 to 5, wherein an outer diameter of the wire main body at the bonding boundary portion is larger than outer diameters of a proximal end side and a distal end side portion of the bonding boundary portion.   The guide wire according to any one of claims 1 to 6, further comprising a coating layer provided on an outer periphery of the wire body so as to cover at least the joining boundary portion.   The guide wire according to any one of claims 1 to 7, wherein the first wire is made of a superelastic alloy.   The guide wire according to any one of claims 1 to 8, wherein the second wire is made of stainless steel or a Co-based alloy.   The guide wire according to claim 9, wherein the Co-based alloy is a Co—Ni—Cr-based alloy.

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