JP2012024491A - Catheter - Google Patents

Abstract

The present invention provides a catheter capable of suppressing a sudden change in bending rigidity while reducing the diameter of the sheath, improving the operability of the sheath and suppressing the bending during the operation.
SOLUTION: A long sheath body portion 21 in which first lumens 27 and 28 are formed, and a second lumen 26B is formed on a side portion of the distal end portion in the insertion direction of the sheath body portion 21. An intermediate tube 29, wherein the sheath body 21 is disposed outside the outer tube 5 made of polyetheretherketone (PEEK) and on the inner side of the outer tube 5 than the outer tube 5. An inner tube 7 made of polyetheretherketone extending to the tip side, and a tip outer tube 6 made of a material lower in rigidity than polyetheretherketone provided on the tip side of the outer tube 5 and outside the inner tube 7; Have.
[Selection] Figure 3

Description

  The present invention relates to a catheter that is inserted into a living body such as a blood vessel and a blood vessel.

  Conventionally, an image diagnosis is performed by inserting an ultrasonic catheter having an imaging function into a blood vessel such as a coronary artery of the heart or a blood vessel such as a bile duct.

  Examples of the image diagnostic apparatus include an intravascular ultrasonic diagnostic apparatus (IVUS: Intra Vessel Ultra Sound). In general, an intravascular ultrasonic diagnostic apparatus performs a radial scan of a probe containing an ultrasonic transducer in a blood vessel, and receives a reflected wave (ultrasonic echo) reflected by a living tissue in a body cavity by the same ultrasonic transducer. Thereafter, processing such as amplification and detection is performed, and a cross-sectional image of the blood vessel is drawn based on the intensity of the generated ultrasonic echo.

  In addition, an optical coherence tomography (OCT: Optical Coherence Tomography) has come to be used as an image diagnostic apparatus. The optical coherence tomography diagnosis apparatus inserts a probe containing an optical fiber having a probe containing an optical lens and an optical mirror at the tip into a blood vessel, and performs a radial scan of the optical mirror disposed on the tip side of the optical fiber. The blood vessel is irradiated with light, and a cross-sectional image of the blood vessel is drawn based on the reflected light from the living tissue. Furthermore, recently, an image diagnostic apparatus using an optical frequency domain imaging method (OFDI), which is called next-generation OCT, has also been proposed.

  Patent Document 1 describes a catheter which is an intravascular ultrasonic diagnostic apparatus. In this catheter, a metal tube is used as a sheath to be inserted into a living body, and a resin layer is provided on the outside of the metal tube. The metal tube is provided up to the proximal end side of the portion of the sheath through which the ultrasonic waves are transmitted.

JP 2004-97286 A

  However, when a metal tube is used for the sheath, the bending rigidity of the sheath greatly changes when the tip of the metal tube is switched to the resin-only layer. In particular, when reducing the diameter of the sheath, the resin layer that overlaps the metal tube also becomes thinner, so the bending rigidity of the sheath will change more greatly, resulting in lower operability of the sheath and bending during operation. (Kink) etc. may occur.

  The present invention has been made to solve the above-described problems, and suppresses a rapid change in bending rigidity while reducing the diameter of the sheath, thereby improving the operability of the sheath and suppressing the bending during the operation. An object is to provide a possible catheter.

  The catheter of the present invention that achieves the above-mentioned object is provided with a long sheath body portion in which a first lumen is formed, and a second lumen formed on a side portion of the distal end portion in the insertion direction of the sheath body portion. A tube body, wherein the sheath main body is an outer tube made of polyetheretherketone (PEEK) and a poly-polyethylene disposed inside the outer tube and extending to the distal end side of the outer tube. An inner tube made of ether ether ketone, and a tip outer tube made of a material lower in rigidity than polyether ether ketone, provided on the distal side of the outer tube and outside the inner tube.

  In the catheter of the present invention configured as described above, since the outer tube and the inner tube constituting the sheath main body have a double structure of polyether ether ketone having high strength, a metal tube is applied. High strength can be realized without reducing the outer diameter. Furthermore, a distal outer tube made of a material having lower rigidity than polyether ether ketone is provided on the distal end side of the outer tube, and since the inner tube extends to the distal end side from the outer tube, the bending rigidity of the sheath is increased. It is decreased stepwise as it goes toward the tip direction, so that the operability is improved and bending during operation can be suppressed.

  If the inner tube extends to the distal end side rather than the proximal end portion of the tube body, the rigidity of the proximal end portion of the distal tube, whose rigidity changes, is improved by the inner tube, and bent during operation. Can be suppressed.

  A distal inner tube extending from the proximal end side to the distal end side of the distal outer tube from the proximal end side to the distal end side of the distal outer tube between the inner tube and the distal outer tube; Then, the layer structure constituted by the inner tube, the distal outer tube, and the distal inner tube changes in a step-wise manner from the triple structure toward the distal end side and changes. For this reason, the bending rigidity of the sheath is gradually reduced as it goes in the distal direction, so that the operability is improved and the bending during the operation can be suppressed.

  If at least one of the distal end side of the inner tube and the inner tube at the distal end has a rigidity decreasing portion in which the bending rigidity decreases in the direction of the distal end, the bending rigidity of the sheath is inclined toward the distal direction. Therefore, the operability is improved and bending during operation can be suppressed.

  If a reinforcing tube whose bending rigidity decreases in an inclined manner toward the distal end is provided between the outer tube and the inner tube, the operability can be further improved and bending during operation can be suppressed.

It is a top view which shows the ultrasonic catheter which concerns on 1st Embodiment. It is a longitudinal direction sectional view showing the tip part of the ultrasonic catheter concerning a 1st embodiment. It is a longitudinal section showing the vicinity of the base end part of the 2nd guidewire lumen of the ultrasonic catheter concerning a 1st embodiment. It is a longitudinal direction sectional view showing the vicinity of the base end portion of the second guide wire lumen of the ultrasonic catheter according to the second embodiment. It is longitudinal direction sectional drawing which shows the base end part vicinity of the 2nd lumen for guide wires of the ultrasonic catheter which concerns on 3rd Embodiment.

Embodiments of the present invention will be described below with reference to the drawings. In addition, the dimension ratio of drawing is exaggerated on account of description, and may differ from an actual ratio.
<First Embodiment>
The catheter according to the first embodiment of the present invention is an ultrasonic catheter 1 that transmits and receives ultrasonic waves in a blood vessel using a built-in ultrasonic transducer and renders a cross-sectional image of the blood vessel. The ultrasonic catheter 1 transmits and receives ultrasonic waves to and from a sheath 2 that is inserted into a living body such as a body cavity, and a hub 3 that is not inserted into the body cavity and is placed on the user's hand side for operation by the user. And an imaging core 4 for the purpose.

  As shown in FIGS. 1 and 2, the sheath 2 is connected to the sheath body 21 connected to the hub 3 and the distal end side of the sheath body 21, and a first guide wire lumen 26 </ b> A (second lumen) is provided. A distal tube 22 (tube body) to be formed, and an intermediate tube 29 (second lumen) 26B (second lumen) that is connected to the sheath main body 21 on the proximal side of the distal tube 22 and formed with a second guide wire lumen 26B (second lumen). Tube body). The sheath body 21 includes a sheath base end portion 23 connected to the hub 3, a sheath distal end portion 24 having an outer diameter smaller than that of the sheath base end portion 23, and a distal end tube 22 connected to the distal end side. And an intermediate tube 29 that is fused or bonded to the outer surface of the distal end portion 24. The distal tube 22 and the intermediate tube 29 are fused or bonded to the outer surface of the sheath distal portion 24. Alternatively, the tip tube 22 and the intermediate tube 29 may be formed integrally with the sheath tip portion 24.

  The guide wire 25 is inserted in advance to the vicinity of the affected part in the living body before the ultrasonic catheter 1 is inserted into the living body, and is used to guide the ultrasonic catheter 1 to the affected part. The ultrasonic catheter 1 is guided to the affected area while passing the guide wire lumens 26A and 26B through the guide wire 25.

  The sheath distal end portion 24 and the sheath base end portion 23 are provided with observation portion lumens 27 and 28 (first lumen) communicating with each other. The observation portion lumens 27 and 28 are hollow passages formed in the sheath 2, and are formed from the sheath base end portion 23 to the sheath distal end portion 24.

  The imaging core 4 is disposed in the observation unit lumens 27 and 28. The imaging core 4 includes a transducer unit (observation unit, ultrasonic detector) 41 for transmitting and receiving ultrasonic waves toward the tissue in the body cavity, and a drive that attaches the transducer unit 41 to the tip and transmits rotational power. A shaft 42.

  As shown in FIG. 2, the transducer unit 41 includes an ultrasonic transducer 411 that transmits and receives ultrasonic waves, and an ultrasonic transducer housing 412 that houses the ultrasonic transducer 411.

  The ultrasonic transducer 411 generates an ultrasonic wave toward the inside of the body and receives an ultrasonic wave reflected and returned, thereby enabling formation of an ultrasonic tomographic image of the affected part. The ultrasonic transducer housing 412 is formed in a concave shape, holds the ultrasonic transducer 411 in the concave concave portion, and protects the ultrasonic transducer 411.

  The drive shaft 42 is flexible and has a characteristic capable of transmitting the rotational power generated in the hub 3 to the vibrator unit 41. For example, a multi-layer coil such as a three-layer coil in which the right and left and the winding directions are alternated The outer diameter of the tube is constant. When the driving shaft 42 transmits the rotational power, the vibrator unit 41 rotates about the extending direction of the observation unit lumen 27 as an axis, so that the affected part in the body cavity such as a blood vessel and a vessel can be observed 360 degrees. it can. The drive shaft 42 has a signal line for transmitting a signal detected by the vibrator unit 41 to the hub 3.

  In addition, the observation unit lumens 27 and 28 not only contain the imaging core 4, but also serve as a path for the ultrasonic transmission liquid injected from the port 31 of the hub 3. The ultrasonic transmission liquid supplied from the port 31 flows and fills through the observation portion lumens 27 and 28 to the distal end of the sheath distal end portion 24, that is, from the proximal end side to the distal end side of the sheath 2. During the injection of the ultrasonic transmission liquid, the internal air is discharged from the discharge port 30 provided in the sheath distal end portion 24.

  By filling the sheath 2 with the ultrasound transmission liquid and then inserting the sheath 2 into a body cavity or the like, the ultrasound transmission liquid is disposed between the ultrasonic transducer 411 and the inner surface of the sheath 2, and the ultrasonic wave is transmitted. It is transmitted to the affected part (blood vessel wall) via the ultrasonic transmission liquid and blood, and can be reflected back from the affected part. Due to the presence of the ultrasonic transmission liquid, the transducer unit 41 can acquire a video signal by ultrasonic waves. Since the ultrasonic transmission liquid can be circulated in the blood vessel via the discharge port 30 provided in the sheath distal end portion 24, a physiological saline or the like that does not affect the human body is used as the ultrasonic transmission liquid.

  Note that an X-ray contrast marker may be provided on the distal tube 22 or the sheath distal end 24 so that the distal end position of the ultrasonic catheter can be confirmed under fluoroscopy when inserted into the living body.

  The first guidewire lumen 26A and the second guidewire lumen 26B are not connected to each other, but are arranged so that the guidewire passages formed with each other are substantially straight. Therefore, the guide wire 25 can pass through the guide wire lumens 26A and 26B in a straight line without bending.

  The first guidewire lumen 26A is provided closer to the distal end side of the ultrasound catheter 1 in the in-vivo insertion direction than the transducer unit 41 of the imaging core 4, and the second guidewire lumen 26B is provided closer to the rear end side. ing. Therefore, since the guide wire lumen does not exist on the outer peripheral surface of the sheath distal end portion 24 serving as an ultrasonic path, transmission / reception of ultrasonic waves by the transducer unit 41 is not hindered by the guide wire lumens 26A and 26B.

  In addition, by operating the hub 3, the living body can be observed in a wide range by moving the transducer unit 41 back and forth within the observation unit lumen 23 via the drive shaft 42. In this case, transmission / reception of ultrasonic waves is not hindered if the first guidewire lumen 26A and the second guidewire lumen 26B are separated from each other by the range in which the transducer unit 41 moves back and forth.

  Since the guide wire lumens 26A and 26B extend not only to the distal end portion but also to the proximal end side of the ultrasonic catheter 1, the guide wire 25 and the ultrasonic catheter 1 stably cooperate with each other. When the sheath 2 is inserted into the living body along the axis, the force for inserting the sheath 2 is easily transmitted to the distal end of the sheath 2 in the insertion direction, and the operability of the ultrasonic catheter 1 is improved. Further, when the observation of the affected area is completed and the ultrasonic catheter 1 is extracted from the living body, the guide wire 25 and the sheath 2 are long and parallel to each other, so that the guide is provided behind the first guide wire lumen 26A. The wire 25 is not bent, and thus the living body is not damaged. Further, by providing the second guide wire lumen 26B, the length of the first guide wire lumen 26A can be shortened, and the transducer unit 41 of the imaging core 4 can be brought close to the most distal portion of the sheath 2 to Observation can be made appropriate.

  Next, a specific structure of the vicinity of the proximal end side of the second guide wire lumen 26B of the sheath 2 to which the present invention is applied will be described with reference to FIG.

  The sheath body 21 includes an outer tube 5 connected to the hub 3, a distal outer tube 6 coupled to the distal end side of the outer tube 5, an inner tube 7 disposed inside the outer tube 5, and an inner tube 7. And a distal end inner tube 8 disposed on the distal end side.

  The outer tube 5 is a tube body extending from the hub 3 to the vicinity of the proximal end side of the second guide wire lumen 26B, and is made of polyetheretherketone (PEEK). Polyetheretherketone is a thermoplastic resin excellent in mechanical strength, chemical resistance and heat resistance.

  The inner tube 7 is a tube body that extends from the hub 3 to the tip side of the outer tube 5 inside the outer tube 5, and is made of polyetheretherketone (PEEK) like the outer tube 5. A first stiffness reducing portion 71 is formed at the distal end portion of the inner tube 7 so that the bending stiffness decreases in an inclined manner by reducing the diameter in the distal direction. The insides of the inner tube 7 and the distal end inner tube 8 constitute the observation portion lumens 27 and 28, and the imaging core 4 is disposed.

  The outer tube 5 and the inner tube 7 are not limited to polyether ether ketone as long as the material is highly rigid. For example, polyolefin resin such as polyethylene, polypropylene, polybutene, vinyl chloride, ethylene-vinyl acetate copolymer or the like Polyolefin elastomer, fluororesin or fluoroelastomer, methacrylic resin, polyphenylene oxide, modified polyphenylene ether, polyethylene terephthalate, polybutylene terephthalate, polyamideimide, polyetherimide, polyethersulfone, cyclic polyolefin, polyurethane elastomer, polyester Elastomer, polyamide or polyamide elastomer, polycarbonate, polyacetal, styrene resin or styrene Elastomer, a thermoplastic polyimide and the like can be used. Moreover, the outer tube 5 and the inner tube 7 may be formed of different materials.

  The distal outer tube 6 is a tubular body connected to the distal end portion of the outer tube 5 on the proximal end side with respect to the second guide wire lumen 26B, and reaches the middle of the portion where the intermediate tube 29 is provided. The side surface of the proximal end side of the intermediate tube 29 is fused or bonded to the outer surface (see FIG. 1). The distal outer tube 6 is made of polyethylene having a lower rigidity than the material of the outer tube 5 and the inner tube 7. The distal outer tube 6 and the outer tube 5 are bonded with an adhesive. The adhesive is, for example, an adhesive mainly composed of epoxy, urethane, acrylic, or a mixture thereof, but is not particularly limited as long as it can be bonded.

  The distal inner tube 8 is a tubular body that is disposed inside the distal outer tube 6 and extends from the distal end side to the forefront where the discharge port 30 is formed (see FIGS. 1 and 2). The outer tube 5 and the inner tube 7 are made of polyethylene having a rigidity lower than that of the material. The distal end inner tube 8 has a proximal end located between the inner tube 7 and the distal outer tube 6 on the proximal end side of the most distal end of the inner tube 7, and the distal end is located on the distal end side. The distal end tube 22 is fused to the outer peripheral surface of the sheath distal end portion 24. The distal inner tube 8 is inserted from the proximal end side to the middle of the portion where the intermediate tube 29 is provided, but is inserted into the distal outer tube 6. Therefore, the outermost layer is formed and the outer surface is fused to the intermediate tube 29 (see FIGS. 1 and 2). The distal inner tube 8 is fused to the inner peripheral surface of the distal outer tube 6. In addition, you may adhere | attach with an adhesive agent, without fuse | melting. The adhesive is, for example, an adhesive mainly composed of epoxy, urethane, acrylic, or a mixture thereof, but is not particularly limited as long as it can be bonded. Note that the proximal end side end of the distal inner tube 8 is located on the distal end side relative to the distal end side end of the outer tube 5, but is closer to the proximal end side than the distal end side end of the outer tube 5. May be located.

  The base end portion of the distal end inner tube 8 is formed with a second stiffness reducing portion 81 in which the bending stiffness decreases in an inclined manner by reducing the diameter toward the distal direction.

  The material of the tip outer tube 6 and the tip inner tube 8 is not limited to polyethylene as long as the material is lower in rigidity than the outer tube 5 and the inner tube 7. For example, polypropylene, polyisoprene, chlorinated polyethylene, polychlorinated Vinyl, polybutadiene, polystyrene, high impact polystyrene, acrylonitrile-styrene resin (AS resin), acrylonitrile-butadiene-styrene resin (ABS resin), methyl methacrylate-butadiene-styrene resin (MBS resin), methyl methacrylate-acrylonitrile-butadiene- Styrene resin (MABS resin), acrylonitrile-acrylic rubber-styrene resin (AAS resin), acrylic resin, polyester (polyethylene terephthalate, polybutylene terephthalate, polyethylene naphthalate, etc.), poly -Bonate, polyphenylene ether, modified polyphenylene ether, aliphatic polyamide, aromatic polyamide, polyphenylene sulfide, polyimide, polyether ether ketone, polysulfone, polyarylate, polyether ketone, polyether nitrile, polythioether sulfone, polyether sulfone, polybenz Imidazole, polyamideimide, polyetherimide, polyacetal, liquid crystal polymer, thermoplastic polyurethane and the like can be applied. Moreover, although it fixes with the adhesive agent between the front-end | tip outer tube | pipe 6 and the outer tube | pipe 5, according to material, you may fuse | melt as long as it can fuse | melt. Further, the distal end portion of the inner tube 7 is abutted in the middle of the distal inner tube 8. In addition, the internal diameter of the site | part which the inner tube 7 of the front-end | tip inner tube 8 contacts can be expanded locally, and it can also be set as the structure which the front-end | tip of the inner tube 7 strikes against the site | part with which the internal diameter expanded.

  The distal tube 22 and the intermediate tube 29 are tubular bodies made of polyethylene, but the material is not particularly limited. For example, polypropylene, polyisoprene, chlorinated polyethylene, polyvinyl chloride, polybutadiene, polystyrene, impact polystyrene, Acrylonitrile-styrene resin (AS resin), acrylonitrile-butadiene-styrene resin (ABS resin), methyl methacrylate-butadiene-styrene resin (MBS resin), methyl methacrylate-acrylonitrile-butadiene-styrene resin (MABS resin), acrylonitrile-acrylic rubber -Styrene resin (AAS resin), acrylic resin, polyester (polyethylene terephthalate, polybutylene terephthalate, polyethylene naphthalate, etc.), polycarbonate , Polyphenylene ether, modified polyphenylene ether, aliphatic polyamide, aromatic polyamide, polyphenylene sulfide, polyimide, polyether ether ketone, polysulfone, polyarylate, polyether ketone, polyether nitrile, polythioether sulfone, polyether sulfone, polybenzimidazole Polyamideimide, polyetherimide, polyacetal, liquid crystal polymer, thermoplastic polyurethane and the like can be applied.

  As described above, according to the ultrasonic catheter 1 according to the present embodiment, the outer tube 5 and the inner tube 7 constituting the sheath body 21 have a double structure of polyether ether ketone having high strength. High strength can be realized and the outer diameter can be reduced without applying a tubular body. In addition, when a metal tube is applied to the sheath, the rigidity of the sheath abruptly changes at a portion where the metal tube is switched to the resin tube, but in this embodiment, the sheath main body 21 is made of metal. Since the pipes made of polyetheretherketone are stacked without using the pipe body, the rigidity of the sheath does not change abruptly, and bending can be suppressed. In particular, since the force to bend the sheath 2 by the guide wire 25 is likely to act on the proximal end side of the second guide wire lumen 26B, the rigidity is inclined on the proximal end side of the second guide wire lumen 26B. The reduction is effective in suppressing the bending.

  Further, a distal end outer tube 6 made of a material having lower rigidity than polyether ether ketone is provided on the distal end side of the outer tube 5, and the inner tube 7 extends to the distal end side from the outer tube 5. The bending rigidity is gradually reduced as it goes in the tip direction, so that operability is improved and bending during operation can be suppressed.

  Further, a distal inner tube 8 extending between the inner tube 7 and the distal outer tube 6 from the proximal end side to the distal end side of the distal outer tube 6 from the proximal end side to the distal end side of the distal outer tube 6. Therefore, the layer structure constituted by the inner tube 7, the distal outer tube 6 and the distal inner tube 8 is gradually changed from a triple structure to a single structure through a two-layer structure from the proximal end side to the distal end side. Change. For this reason, the bending rigidity of the sheath is gradually reduced as it goes in the distal direction, so that the operability is improved and the bending during the operation can be suppressed.

In addition, since the first stiffness reducing portion 71 is formed at the distal end portion of the inner tube 7 and the second stiffness reducing portion 81 is formed at the distal inner tube 8, the bending stiffness of the sheath is inclined as it goes in the distal direction. Therefore, operability is improved and bending during operation can be suppressed.
<Second Embodiment>
The ultrasonic catheter 100 according to the second embodiment is different from the ultrasonic catheter 1 according to the first embodiment only in the position of the intermediate tube 129. In addition, about the site | part which has the same function as 1st Embodiment, the same code | symbol is attached | subjected and description is abbreviate | omitted in order to avoid duplication.

  As shown in FIG. 4, in the ultrasonic catheter 100, the proximal end of the intermediate tube 129 having the second guide wire lumen 26B is formed from the distal end of the inner tube 7 made of polyetheretherketone. Is also located on the proximal side.

According to the ultrasonic catheter 100 according to the second embodiment, the inner tube 7 made of polyetheretherketone extends to the distal end side from the proximal end portion of the intermediate tube 129, so that the rigidity is high. The rigidity of the base end portion of the intermediate tube 129 that greatly changes can be improved by the inner tube 7 and bending during operation can be suppressed.
<Third Embodiment>
The ultrasonic catheter 110 according to the second embodiment is different from the ultrasonic catheter 1 according to the first embodiment only in that a reinforcing tube 111 is provided. In addition, about the site | part which has the same function as 1st Embodiment, the same code | symbol is attached | subjected and description is abbreviate | omitted in order to avoid duplication.

  As shown in FIG. 5, the ultrasonic catheter 110 is provided between the outer tube 5 and the inner tube 7 with a reinforcing tube 111 whose bending rigidity decreases in an inclined manner as the thickness decreases toward the distal end. . The reinforcing tube 111 has a distal end portion located near the distal end of the outer tube 5 from the proximal end portion of the distal outer tube 6, and a proximal end portion located at the proximal end portion of the outer tube 5. It should be noted that the installation position of the reinforcing tube 111 can be changed as appropriate in accordance with the portion where the inclined bending rigidity is desired. The reinforcing tube 111 is made of, for example, SUS, but the material is not particularly limited. For example, the reinforcing tube 111 may be formed with a spiral slit or may be coiled. The slant decrease in the rigidity of the reinforcing tube 111 is not limited to the adjustment by the thickness, but can be adjusted by the slit width, the slit pitch, the coil diameter, the coil pitch, or the like.

  According to the ultrasonic catheter 110 according to the third embodiment, the bending rigidity of the portion where the outer tube 5 and the inner tube 7 overlap is decreased in an inclined manner toward the distal direction, so that the operability is improved and the operation is improved. Time bending can be suppressed.

  The present invention is not limited to the above-described embodiment, and various modifications can be made within the scope of the claims. For example, in the above embodiment, the case where the present invention is applied to an ultrasonic catheter has been described. However, an optical probe for a diagnostic device (catheter) using light such as an optical coherence tomography diagnostic device or an optical frequency domain imaging diagnostic device. ), Balloon catheters, etc., and can be applied to any catheter as long as it has a tubular body. In this embodiment, the guide wire lumens 26A and 26B are divided into two. However, the present invention can also be applied to a catheter having a single guide wire lumen.

1,100,110 ultrasonic catheter (catheter),
2 sheath,
5 Outer pipe,
6 Tip outer tube,
7 Inner pipe,
8 End inner tube,
21 sheath body,
22 Tip tube (tube body),
29,129 Intermediate tube (tube body),
26A Lumen for first guide wire (second lumen),
26B Lumen for second guide wire (second lumen),
27, 28 Lumen for observation section (first lumen),
71 1st rigidity reduction part,
81 2nd rigidity reduction part,
111 Reinforcement pipe.

Claims (5)

A catheter having a long sheath body portion in which a first lumen is formed, and a tube body provided on a side portion of a distal end portion in the insertion direction of the sheath body portion to form a second lumen. ,
The sheath main body includes an outer tube made of polyetheretherketone (PEEK),
An inner tube made of polyetheretherketone, which is arranged inside the outer tube and extends to the tip side of the outer tube;
A tip outer tube that is provided on the tip side of the outer tube and outside the inner tube, and made of a material lower in rigidity than polyetheretherketone;
A catheter.   The catheter according to claim 1, wherein the inner tube extends to a distal end side rather than a proximal end portion of the tube body.   Between the inner tube and the distal outer tube, further includes a distal inner tube that extends from the proximal end side to the distal end side of the distal outer tube from the proximal end side to the distal end side of the distal outer tube. The catheter according to any one of claims 1 and 2.   The catheter according to any one of claims 1 to 3, wherein at least one of the distal end side of the inner tube and the inner tube at the distal end has a stiffness reducing portion in which the bending stiffness is gradually decreased toward the distal direction.   The catheter according to any one of claims 1 to 4, wherein a reinforcing tube is provided between the outer tube and the inner tube, the bending rigidity of which gradually decreases toward the distal direction.

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