JP2008104657A - Medical balloon catheter - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a medical balloon catheter with high reachability to a lesion and high certainty of expansion treatment by generalizing the entire structure. <P>SOLUTION: In an intermediate tube (b) and a distal end tube (c), a lumen for balloon expansion and a core wire inside the lumen exist. At the proximal section of the distal end tube (c), a guide wire port which is the proximal end side opening of a guide wire passing tube (d) exists. The guide wire passing tube (d) is provided with an inner layer tube, a reinforcing layer for which at least one metal tube is fixed to at least a part of the inner layer tube, and a resin outer layer covering the inner layer tube and the reinforcing layer. <P>COPYRIGHT: (C)2008,JPO&INPIT

Description

  The present invention relates to a medical balloon catheter used for medical purposes, and more specifically, percutaneous angioplasty (PTA: Percutaneous Transluminal Angioplasty, PTCA: Percutaneous Transluminal Coronary Angioplasty, etc.).

  Conventionally, percutaneous angioplasty using a medical balloon catheter is widely used for the purpose of expanding or treating stenosis or occlusion in the lumen of the blood vessel and restoring or improving blood flow in coronary arteries and peripheral blood vessels. It has been. A typical medical balloon catheter is formed by joining a balloon that can be inflated and deflated by adjusting the internal pressure to the distal end portion of a catheter shaft. Inside the catheter shaft, a lumen through which a guide wire is inserted ( A guide wire lumen) and a lumen for supplying a pressure fluid for adjusting the internal pressure of the balloon (balloon expansion lumen) are provided along the longitudinal direction of the catheter shaft.

  A general operation example of PTCA using such a medical balloon catheter is as follows. First, a guide catheter is inserted from a puncture site such as the femoral artery, brachial artery, and radial artery, and the distal end is placed at the entrance of the coronary artery via the aorta. Next, the guide wire inserted through the guide wire lumen is advanced beyond the stenotic site of the coronary artery, and a medical balloon catheter is inserted along the guide wire to match the balloon with the stenosis. Next, a pressure fluid is supplied to the balloon via a balloon dilatation lumen using an indeflator or the like, and the balloon is inflated to dilate the stenosis. After dilatation treatment of the stenosis, PTCA is terminated by retracting the balloon under reduced pressure and removing it from the body. In this operation example, the use example of the medical balloon catheter by PTCA in the coronary artery stenosis is described. However, the medical balloon catheter is widely applied to the expansion treatment in other blood vessel lumens and body cavities such as the periphery. Yes.

  In such a medical balloon catheter, as shown in FIG. 1 or FIG. 2, the balloon 2 is joined to the tip of the catheter shaft 1, and the hub 3 for supplying pressure fluid for adjusting the internal pressure of the balloon is joined to the catheter shaft 1. It has a structure and is roughly classified into two according to the structure of the catheter shaft 1.

  One is that the guide wire lumen 4 is provided from the proximal end side to the distal end side of the medical balloon catheter, that is, over the entire length of the medical balloon catheter, and the guide wire port 5 is provided in the hub 3. It is an over-the-wire type (OTW type) (FIG. 1). The other is a high-speed exchange type (RX type) in which the guide wire lumen is provided only on the distal end side of the medical balloon catheter and the guide wire port 5 is provided in the middle of the catheter shaft 1 (FIG. 2). .

  The performance required for medical balloon catheters varies widely, but the main performance is the crossability of the stenosis site, the trackability to the bent blood vessel, and the force when inserting the medical balloon catheter into the blood vessel. There are three main categories of pushability. Moreover, kink-resistance is also mentioned as a performance related to pushability.

  Crossability improves by reducing the catheter shaft profile (thickness), but pushability and kink-resistance tend to decrease. In addition, increasing the rigidity of the catheter shaft improves pushability and kink-resistance, but tends to decrease trackability. That is, the above performances are closely related to each other, and it is not easy to improve all the performances. Accordingly, various techniques for improving crossability, pushability, and trackability and improving kink-resistance are disclosed.

  In Patent Document 1, there is provided a medical tube having a flexible inner layer, a reinforcing layer attached to the outside of the inner layer, and a flexible outer layer attached to the outside of the reinforcing layer, The reinforcing layer is a coil layer, at least part of which is composed of a first coil and a second coil that is provided substantially coaxially with the first coil and is wound in a direction opposite to the first coil. Each of the first coil and the second coil is wound in close winding with a gap width between pitches of 0.02 mm or less, and the coil layer extends from the distal end to the proximal end. Adhesive or resin is not bonded to the inner layer and the outer layer for a predetermined length toward the gap between the pitches on the base side of the coil layer in a portion extending from the base end of the medical tube to the predetermined length. Medical treatment characterized by inflow of materials A tube is presented. In addition, a vasodilator catheter using the medical tube is also presented.

  However, this configuration provides pushability and kink-resistance, but the first coil constituting the reinforcing layer and the first coil are provided substantially on the same axis and wound in the opposite direction to the first coil. Since the first coil and the second coil are overlapped with each other, the tube layer can be obtained with only a large thickness. You can't get something expensive. The guide wire passage tube of the vasodilator catheter is required to have a large inner diameter and a small outer diameter, that is, a thin tube. In addition, although an adhesive or a resin material is allowed to flow into the gap between the pitches on the proximal end side of the coil layer, this process is technically cumbersome and difficult. In addition, winding the coil around a tightly wound coil with a gap between the pitches of 0.02 mm or less gives sufficient flexibility to the tip as a vasodilator catheter even if the coil material is selected. That is, it is difficult to obtain trackability.

  Patent Document 2 discloses a balloon catheter assembly including an elongated tubular member having a balloon portion located on the distal side and a shaft portion located on the proximal side, and extends through the balloon portion and the shaft portion. A balloon catheter assembly is presented that includes a central lumen and an alternating braid member extending from the shaft portion distal to the balloon portion.

  Even in this configuration, pushability and kink-resistance can be obtained, but the reinforcing layer is composed of alternately braided members, that is, braided. In this case, since the strands constituting the reinforcing material overlap, the thickness of the tube is reduced. Only thick ones can be obtained. For this reason, a product with high crossability cannot be obtained.

Furthermore, in this document, a so-called OTW type vascular dilatation catheter is presented, but the gap in the braided tubular member functions as a fluid passage from between the inner lumen of the catheter to the balloon itself, or just distal to the balloon. It is complicated as an OTW type vasodilator catheter, such as inflating the balloon by injecting fluid after the part of the valve fits with the valve seat in the lumen and cooperates with the valve seat seen on the core wire or guide wire A core wire or a guide wire having a configuration and a unique valve seat is required, and there is a possibility that a sufficient vasodilator effect cannot be obtained in terms of the complexity of the procedure and the certainty.
Japanese Patent No. 3659664 Japanese Patent No. 3170210

  The main object of the present invention is to provide a medical balloon tube having, as main performances, good passability of a stenosis site, followability to a bent blood vessel, transferability of force when inserting a medical balloon catheter into the blood vessel, and kink resistance Is to provide. In particular, the object of the present invention is to improve the drawbacks of the prior art, such that the guide wire passes but the balloon body is difficult to pass by adding a device to the guide wire passing tube while maintaining their performance. An object of the present invention is to provide a medical balloon tube having improved lesion passage ability. In addition, the present invention provides reachability to the lesioned part and dilatation treatment by giving a stiffness to the distal part of the balloon catheter by combining the entire structure, such as using a reinforcing material for the core wire or the guide wire passing tube. An object of the present invention is to provide a medical balloon tube with high reliability.

The present invention has one or more of the following features.
(1) One feature of the present invention is that the balloon portion is fixed to the proximal end tube (a), the intermediate tube (b), and the distal end constituting the lumen for balloon expansion from the proximal end side to the distal end side. And a guide wire passing tube having a tip opening at the tip, the balloon portion being fixed to the distal end, and covered with the tip tube (c) and the balloon portion. (D), wherein the intermediate tube (b) and the distal tube (c) have a balloon expansion lumen and a core wire inside the lumen; A guide wire port which is a proximal end side opening of the guide wire passing tube (d) is present at the proximal portion of the distal end tube (c), and the guide wire passing tube (d Is provided with an inner layer tube, a reinforcing layer in which at least one metal tube is fixed to at least a part of the inner layer tube, and a resin outer layer covering the inner layer tube and the reinforcing layer. A catheter.
(2) In a preferred embodiment, the inner layer tube of the guide wire passage tube (d) is made of a fluororesin.
(3) In a preferred embodiment, one or more metal tubes of the guide wire passage tube (d) are made of a radiopaque metal.
(4) In a preferred embodiment, the resin outer layer of the guide wire passage tube (d) is made of polyamide-based elastomer, nylon, polyester, polyester-based elastomer, polyurethane-based elastomer, polyolefin, polyimide, polyimideamide, and polyetherimide. It consists of 1 or more types of resin materials chosen from the group which consists of.

  The above-described and other features of the present invention and their effects will be clarified by the following embodiments and drawings.

  According to the present invention, the guide wire passing tube includes an inner layer tube, and a resin outer layer that fixes at least one metal tube as a reinforcing material to at least a part of the inner layer tube and covers the inner layer tube and the reinforcing layer. By using the composite tube characterized by the above, the distal end portion of the medical balloon catheter has a low profile due to the large inner diameter and the smaller outer diameter, and the narrowness is achieved by the cooperation of the reinforcing material and the elasticity of the core wire. A medical balloon catheter with particularly improved lesion passage is obtained.

  Furthermore, in a preferred embodiment of the present invention, by using a fluororesin for the inner layer tube of the guide wire passage tube, the guide wire passage property is improved, and the outer resin layer of the guide wire passage tube, the vasodilation balloon, However, since it is made of a material having high affinity such as a polyamide-based elastomer, the bonding or welding of both is good, and there is an effect that a medical balloon catheter that can perform a reliable procedure is obtained.

  Embodiments of a medical balloon catheter according to the present invention will be described below.

1. Overall Structure of Medical Balloon Catheter The medical balloon catheter as an embodiment is a high-speed exchange type (RX type) in which a guide wire passing tube 6 is disposed only at the distal end side of the medical balloon catheter as shown in FIG. It relates to a catheter. FIG. 3 shows the entire medical balloon catheter of the embodiment, but there are a hub 7, a strain relief 8, a proximal end tube 9, and a balloon 10.

  Further, FIG. 4 shows a detailed view from the distal portion of the medical balloon catheter, that is, from the balloon to a portion of the proximal tube. In the distal portion, there are a proximal end tube 9, an intermediate tube 11, a distal end tube 12, and a balloon 10 in order from the proximal portion. A guide wire passing tube 6 exists inside the distal end tube 12 and inside the balloon 10. These are bonded by thermal fusion or an adhesive.

  The proximal end tube 9 forms a balloon expansion lumen 18 as seen in the A-A ′ cross section (see FIG. 4), and the position marker 13 may be disposed.

  A core wire 14 is disposed in the intermediate tube 11 and the tip tube 12 for the purpose of increasing the rigidity of the distal side of the medical balloon catheter, and corresponds to a joint between the intermediate tube 11 and the tip tube 12. For example, the core wire fixing portion 15 is fixed by welding. B-B 'sectional view (refer to Drawing 4B) has balloon expansion lumen 18 by this core wire 14 and middle section tube 11. FIG.

  A guide wire passing tube 6 exists from the inside of the distal end tube 12 to the inside of the balloon 10. In the CC cross-sectional view (see FIG. 4C), there is a balloon expansion lumen 18 formed by the guide wire passing tube 6, the core wire 14, and the tip tube 12. A position marker 16 exists in the balloon 10. At the proximal portion of the distal end tube 12, there is a guide wire port 17 that is a proximal end side opening of the guide wire passing tube 6.

2. Balloon Balloon 10 is fixed to the distal end of tip tube 12 and the distal end of guide wire passing tube 6. A tip opening is provided at the tip of the guide wire passing tube 6.

  The balloon 10 can be inflated and deflated by adjusting the internal pressure. As a manufacturing method of the balloon 10, there are dipping molding, blow molding and the like, and an appropriate method can be selected according to the use application of the medical balloon catheter. In particular, in the case of a medical balloon catheter for the purpose of expanding and treating a stenosis of a blood vessel or a body cavity, blow molding is preferable in order to obtain sufficient pressure resistance. For example, a tubular parison having an arbitrary size is first formed by extrusion molding or the like.

  The tubular parison is placed in a mold having a mold that matches the balloon shape, and stretched in the axial direction and the radial direction by a biaxial stretching process, thereby forming a balloon having the same shape as the mold. In addition, the said biaxial stretching process may be performed on heating conditions, and may be performed in multiple times. Further, the stretching in the axial direction may be performed simultaneously with or before or after the stretching in the radial direction. Furthermore, in order to stabilize the shape and dimensions of the balloon, the balloon may be annealed.

  As shown in FIG. 1 or FIG. 2, the balloon 10 has a straight pipe portion 2a and a joining portion 2b for liquid-tight joining to the distal end side and the proximal end side thereof, and is tapered between the straight pipe portion and the joining portion. It has a part 2c. The dimensions of the balloon 2 are determined by the intended use of the medical balloon catheter. The outer diameter of the straight tube portion 2a when expanded by adjusting the internal pressure is 1.50 to 35.00 mm, preferably 1.50. And the length of the straight pipe portion 2a is 10.00 to 80.00 mm, preferably 10.00 to 60.00 mm.

3. Material The resin material of the tubular parison is not particularly limited. For example, polyolefin, polyolefin elastomer, polyester, polyester elastomer, polyamide, polyamide elastomer, polyurethane and polyurethane elastomer can be used. You may have the multilayer material by the blend material which mixed the seed | species or more, and the lamination | stacking of 2 or more types.

  The material of the base end tube 9, the intermediate tube 11, and the distal end tube 12 is not particularly limited. That is, polyolefin, polyolefin elastomer, polyester, polyester elastomer, polyamide, polyamide elastomer, polyurethane, polyurethane elastomer and the like can be used.

  The material of the core wire 14 is stainless steel, C—Mn—Si—PS—Cr—Mo—Ni—Fe—X (X = Au, Os, Pd, Re, Ta, Ir, Ru) alloy, C—Mn. -Si-PS-Cr-Mo-Ni-X (X = Au, Os, Pd, Re, Ta, Ir, Ru) alloy, copper, nickel, titanium, piano wire, Co-Cr alloy, Ni-Ti Various alloys such as alloys, Ni—Ti—Co alloys, Ni—Al alloys, Cu—Zn alloys, Cu—Zn—X alloys (for example, X = Be, Si, Sn, Al, Ga), amorphous alloys, etc. Metal wires are used, and among these materials, stainless steel is preferable because it has an appropriate rigidity and is not workable, economical, or toxic. The core wire is preferably tapered so that it gradually becomes thinner in the intermediate tube region and has a constant diameter in the distal tube region.

  As the material of the position marker 16, it is preferable to use a metal having high radiopacity such as platinum or gold.

4). Structure and Manufacturing Process of Guide Wire Passing Tube 6 One of the characteristic configurations of the present invention is that the guide wire passing tube 6 includes an inner layer tube and at least one metal in at least a part of the inner layer tube. A reinforcing layer that fixes the tube, and a resin outer layer that covers the inner layer tube and the reinforcing layer.

  Here, in order to show the structure of the guide wire passing tube 6 in more detail, the manufacturing process will be shown.

  First, a metal core wire 19 is prepared as shown in FIG. The metal core wire is wound around a reel 20, and the outer diameter thereof is substantially the same as the inner diameter of the guide wire passing tube to be manufactured. The material is preferably a metal-plated copper wire or a stainless steel wire.

  Subsequently, as shown in FIG. 6, the inner layer tube 21 is formed by extrusion coating on the metal core wire 19 by the extruder 22.

(Inner layer pipe)
Examples of the constituent material of the inner layer tube 21 include fluorine such as polytetrafluoroethylene, tetrafluoroethylene-perfluoroalkyl vinyl ether copolymer, tetrafluoroethylene-hexafluoropropylene copolymer, and ethylene-tetrafluoroethylene copolymer. Resin, polypropylene, polyethylene, polyolefin such as ethylene-vinyl acetate copolymer, polyamide, polyester such as polyethylene terephthalate, polybutylene terephthalate, polyurethane, polyvinyl chloride, polystyrene resin, polyimide resin, and mixtures thereof. It is done. From the standpoint that the finished product exhibits excellent slidability with respect to the guide wire and the like passing through the inner layer tube 21 and obtains position adjustment with guide wire followability, polytetrafluoroethylene or tetrafluoroethylene-perfluoroalkyl. It is preferable to comprise a vinyl ether copolymer. When polytetrafluoroethylene is used, it is fired after treatment such as drying of the additive.

  The inner tube 21 covered with the metal core wire preferably has a sufficient adherence to the metal core wire. Further, in the process of coating the outer tube, the chemical method (use of a defluorinating agent such as sodium naphthalene + dimethyl ether) and / or electricity such as plasma is used to increase the adhesion between the inner tube and the outer tube. Irregularities may be formed or the surface may be modified by a conventional method.

(Reinforcement layer)
The metal core wire covering the inner layer tube 21 is cut to an appropriate length, and one or more metal tubes are fixed to form a reinforcing layer.

  A reinforcing material layer made of a metal tube is formed by caulking and fixing on an inner layer tube covered with a metal core wire as shown in FIG.

  As the metal tube, a metal tube having a cut as shown in FIG. By making a cut in the pipe circumferential direction of the metal tube, the guide wire passing tube is secured with a suitable stiffness.

  Further, the metal tube may be disposed by winding a thin metal plate on the inner layer tube 21 as shown in FIG. At this time, an adhesive may be used, or the contact portion of the metal thin plate may be welded.

  The length of the metal tube is 0.5 to 10 mm, preferably about 0.7 to 5 mm. When arranging a plurality of metal tubes, as shown in FIG. 10, a metal tube that is short in the axial direction at the position corresponding to the tip of the guide wire passing tube and longer in the axial direction toward the base portion is arranged. May be. As described above, the metal tube at the tip is short and the metal tube at the base is long, so that the reachability to the bent lesion is good.

  The arrangement interval of the metal tubes can be 0.3 to 10 mm, more preferably 0.5 to 3 mm.

  The thickness of the metal tube is 1 to 500 μm, preferably 10 to 50 μm.

  The metal tube may use any stainless steel such as martensite, ferrite, two-phase, and austenite. Further, gold, platinum, aluminum, brass, copper, tin, zinc, silver, magnesium, and other metals rich in malleability or alloys thereof can be used as the material.

  One or more of the metal tubes used as the reinforcing material layer are preferably made of a radiopaque metal and act as a marker during the procedure. This radiopaque metal tube is preferably at the forefront of the plurality of metal tubes forming the reinforcing material layer.

As the radiopaque metal, tungsten metal, platinum metal, gold metal, or the like can be used. Tungsten metal is pure tungsten, W-45Mo alloy, W-5Mo-5Ni (Co, Fe) alloy, W-Re alloy, W-ThO ₂ alloy, and alloys of tungsten, copper, carbon, etc. Represents this. The platinum-based metal represents platinum or an alloy of platinum and tungsten, rhodium, iridium, osmium, palladium, ruthenium, or the like. The gold-based metal represents pure gold or an alloy of gold and copper, silver, rhodium, iridium, osmium, palladium, ruthenium, or the like.

  Subsequently, as shown in FIG. 11, the inner tube and the reinforcing layer are covered with the resin outer layer 23. The resin outer layer 23 is a resin tube having an inner diameter slightly larger than the outer diameter of the inner layer tube on which the reinforcing material layer is disposed and fixed.

  The medical balloon tube of the present invention with improved narrow lesion passing ability is integrated with the guide wire passing tube having the reinforcing material layer and the core wire, and the structure is integrated into the distal portion of the balloon catheter. By providing this, it is possible to obtain a medical balloon tube with high reachability to a lesioned part and high certainty of expansion treatment.

(Resin outer layer)
As the material of the resin tube forming the outer layer tube, polyamide elastomer, nylon, polyester, polyester elastomer, polyurethane elastomer, polyolefin, polyimide, polyimide amide, and polyether imide, or a combination of two or more of these Things can be used.

  Here, the polyamide elastomer is, for example, nylon 6, nylon 64, nylon 66, nylon 610, nylon 612, nylon 46, nylon 9, nylon 11, nylon 12, N-alkoxymethyl-modified nylon, hexamethylenediamine-isophthalate. Typical block copolymers include various aliphatic or aromatic polyamides such as acid polycondensation polymers and metaxyloxydiamine-adipic acid polycondensation polymers as hard segments, and polymers such as polyesters and polyethers as soft segments. In addition, polymer alloys (polymer blend, graft polymerization, random polymerization, etc.) of the polyamide and flexible resin, those obtained by softening the polyamide with a plasticizer, and a mixture thereof are also included. It is a concept.

  The polyester-based elastomer is typically a block copolymer of a saturated polyester such as polyethylene terephthalate or polybutylene terephthalate and a polyether or polyester. In addition, these polymer alloys or the saturated polyester may be used as a plasticizer or the like. It is a concept that includes a softened product and a mixture thereof.

  A material suitably used is preferably a polyamide-based elastomer from the viewpoint of processability and flexibility, and representative examples thereof include PEBAX manufactured by elf atochem. If the guide wire passing tube and the balloon are made of the same material, they can be strongly and liquid-tightly integrated when they are heat-sealed.

  The resin outer layer may have the same hardness throughout the entire axial direction of the guide wire passing tube, or the position corresponding to the distal portion of the guide wire passing tube may be more flexible.

  The whole covered with the resin outer layer is further covered with a shrink tube 24 having the property of reducing its diameter by heating as shown in FIG. The shrink tube 24 is preferably made of polytetrafluoroethylene or perfluoroethylene-propene copolymer.

  Thereafter, the shrink tube 24 is heated by a heater to a temperature at which the tube contracts, or is heated by applying high-frequency electromagnetic waves, and the inner tube, the reinforcing layer, and the resin outer layer are integrated. After that, the shrink tube is peeled off and the metal core wire is pulled out to obtain a guide wire passing tube.

5. Effect by the embodiment When the guide wire passing tube obtained in this way is used to construct a medical balloon catheter, when delivered to a narrow lesion, due to the effect of the reinforcing material to which the metal tube is fixed, The force that pushes the balloon catheter is transmitted without causing buckling or kinking easily, and the reachability to the lesioned part and the certainty of the expansion treatment are increased.

6). Hydrophilic coating The outer surface of the medical balloon catheter can be provided with a hydrophilic coating in order to facilitate insertion into a blood vessel or a guide catheter. That is, it is preferable to apply a hydrophilic coating that exhibits lubricity when in contact with blood, such as a base end tube, an intermediate tube, a distal end tube, and an outer surface of a balloon, in contact with blood. The kind of hydrophilic coating is not particularly limited, and hydrophilic polymers such as poly (2-hydroxyethyl methacrylate), polyacrylamide, and polyvinylpyrrolidone can be suitably used, and the coating method is not limited.

FIG. 1 is a schematic perspective view of an over-the-wire type of a general PTCA balloon catheter. FIG. 2 is a schematic perspective view of a high-speed exchange type among general PTCA balloon catheters. FIG. 3 shows an overall configuration diagram of an embodiment of the present invention. FIG. 4 shows a distal portion of a medical balloon catheter as an embodiment of the present invention. FIG. 5 shows a metal core wire wound around a reel. FIG. 6 shows a process of extrusion coating the inner layer tube on the metal core wire. FIG. 7 shows a step of forming a reinforcing material layer by caulking a metal tube. FIG. 8 shows the form of a cut metal tube. FIG. 9 shows a state in which a thin metal plate is wound around the inner layer tube. FIG. 10 shows a state in which a reinforcing material layer is formed by arranging and fixing metal tubes having different lengths. FIG. 11 shows a state in which the inner tube and the reinforcing material layer are covered with a resin outer layer. FIG. 12 shows a state in which the inner tube, the reinforcing material layer, and the resin outer layer are covered with a shrink tube.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Catheter shaft 2 Balloon 3 Hub 4 Guide wire lumen 5 Guide wire port 6 Guide wire passage tube 7 Hub 8 Strain relief 9 Base end tube 10 Balloon 11 Intermediate tube 12 End tube 13 Position marker 14 Core wire 15 Core wire Fixed portion 16 Position marker 17 Guide wire port 18 Balloon expansion lumen 19 Metal core wire 20 Reel 21 Inner layer tube 22 Extruder 23 Resin outer layer 24 Shrink tube

Claims (4)

From the base side to the tip side,
A proximal tube (a) constituting a lumen for balloon expansion,
Middle tube (b),
A tip tube (c) having a balloon portion fixed to the distal end; and
A medical balloon catheter having a tip opening at the tip, the balloon portion fixed at the distal end, and a guide wire passage tube (d) covered with the tip tube (c) and the balloon portion. Because
The intermediate tube (b) and the tip tube (c) have a balloon expansion lumen and a core wire inside the lumen,
In the proximal portion of the distal end tube (c), there is a guide wire port that is a proximal end side opening of the guide wire passing tube (d),
The guide wire passing tube (d) includes an inner layer tube, a reinforcing layer in which at least one metal tube is fixed to at least a part of the inner layer tube, and a resin outer layer covering the inner layer tube and the reinforcing layer. thing,
A medical balloon catheter.   The medical balloon catheter according to claim 1, wherein the inner layer tube of the guide wire passage tube (d) is made of a fluororesin.   The medical balloon tube according to claim 1 or 2, wherein at least one of the metal tubes of the guide wire passage tube (d) is made of a radiopaque metal.   The resin outer layer of the guide wire passage tube (d) is one selected from the group consisting of polyamide elastomer, nylon, polyester, polyester elastomer, polyurethane elastomer, polyolefin, polyimide, polyimide amide, and polyether imide The medical balloon catheter according to any one of claims 1 to 3, comprising the above resin material.

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