WO2011033783A1

WO2011033783A1 - Catheter

Info

Publication number: WO2011033783A1
Application number: PCT/JP2010/005685
Authority: WO
Inventors: 田中速雄; 兼政賢一
Original assignee: 住友ベークライト株式会社
Priority date: 2009-09-17
Filing date: 2010-09-17
Publication date: 2011-03-24
Also published as: JP5604974B2; JP2011083594A

Abstract

A catheter (10) is provided with: a main lumen (20) which is disposed so as to extend in the longitudinal direction of the catheter (10); and a sub-lumen (30) which is formed to have a diameter smaller than that of the main lumen (20) and is disposed around the main lumen (20) so as to extend in the longitudinal direction of the catheter (10). The catheter (10) is also provided with an operation wire (40) which is slidably inserted in the sub-lumen (30) and is affixed to a distal end section (15) which is the tip section of the catheter (10). A coil (50) consisting of an elastic body is wound around the sub-lumen (30).

Description

catheter

The present invention relates to a catheter.

In recent years, catheters that can manipulate the direction of entry into a body cavity by bending the distal end have been provided. In Patent Document 1, two wire lumens (sublumens) having a smaller diameter are provided around the central lumen (main lumen) so as to face each other by 180 degrees, and a deflection wire (operation line) is provided inside the sublumen. ) Is described.

JP 2006-192269 A

By the way, in order to obtain sufficient flexibility of the catheter, it is necessary to form the catheter flexibly. However, if the catheter is made flexible, the catheter may be bent at a steep angle at the bent position. When the catheter is bent at a steep angle, the sub-lumen is bent at a steep angle at that position.
When the sub-lumen is bent at a steep angle, the coefficient of friction between the peripheral wall of the sub-lumen and the operation line increases at that position. For this reason, the bending operability of the catheter using the operation line is deteriorated or the operation line is cut.

In recent years, the diameter of catheters has been reduced from the viewpoint of insertion into blood vessels and the like, and those having an outer diameter of 1 mm or less (hereinafter sometimes referred to as microcatheter) have been provided. In such a microcatheter, it is assumed that the above-described problems are more likely to occur.

The present invention has been made in view of the above problems, and an object of the present invention is to provide a catheter capable of suppressing the sudden bending of sublumen while sufficiently securing the flexibility of the catheter.

The present invention comprises a main lumen disposed along the longitudinal direction of the catheter;
A sub-lumen formed with a smaller diameter than the main lumen and disposed along the longitudinal direction around the main lumen;
An operation line that is slidably inserted into the sub-lumen and is fixed to the distal end of the catheter;
A coil composed of an elastic body and wound around the sublumen;
A catheter is provided.

In the present invention, when the catheter is bent by an operation on the operation line, an external force is applied to the coil in an axial direction (an attempt to bend the coil), but the coil has its elastic repulsive force. By trying to resist that external force. For this reason, it is possible to suppress the sudden bending of the sub-lumen. Thereby, since the increase in the friction coefficient between the peripheral wall of the sub-lumen and the operation line can be suppressed, the bending operability of the catheter using the operation line can be maintained in a good state, and the occurrence of disconnection of the operation line can also be suppressed.
However, since the coil can be bent in accordance with an external force that attempts to bend its axial direction, it is possible to sufficiently ensure the flexibility of the catheter.
In short, it is possible to suppress the sudden bending of the sublumen by the elastic repulsive force of the coil while sufficiently securing the flexibility of the catheter.

According to the present invention, since the coil constituted by the elastic body is wound around the sub-lumen, the flexibility of the catheter is sufficiently ensured, and the elastic repulsive force of the coil has the effect of the sub-lumen. Steep bends can be suppressed.

The above-described object and other objects, features, and advantages will be further clarified by a preferred embodiment described below and the following drawings attached thereto.

It is a sectional side view of the tip part of the catheter concerning a first embodiment. FIG. 2 is a cross-sectional view taken along line AA in FIG. 1. It is a schematic diagram of the coil which the catheter which concerns on 1st embodiment has. It is a sectional side view of the front-end | tip part of the catheter which concerns on 1st embodiment, and shows a wider range than FIG. It is a side view of the catheter concerning a first embodiment. It is a side view which shows the operation example of the catheter which concerns on 1st embodiment. It is a side view which shows the modification of a coil. It is a sectional side view of the catheter which concerns on 2nd embodiment. It is an enlarged view of FIG.

Hereinafter, embodiments of the present invention will be described with reference to the drawings. In all the drawings, the same components are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

<First embodiment>
FIG. 1 is a side sectional view of the distal end portion of a catheter 10 according to the first embodiment of the present invention. The left side in FIG. 1 corresponds to the distal end side (hereinafter also referred to as the distal end side) of the catheter 10, and the right side corresponds to the proximal side (hereinafter also referred to as the proximal end side or the proximal end side). However, the proximal end side of the catheter 10 is not shown in FIG.
2 is a cross-sectional view taken along line AA in FIG.
FIG. 3 is a schematic diagram of the coil 50 included in the catheter 10.
FIG. 4 is a side sectional view of the distal end portion of the catheter 10, showing a wider range than FIG. However, the proximal end side of the catheter 10 is not shown in FIG.
FIG. 5 is a side view of the catheter 10.
FIG. 6 is a side view showing an operation example of the catheter 10.

The catheter 10 according to the present embodiment includes a main lumen 20 arranged along the longitudinal direction of the catheter 10, a sub-lumen 30, an operation line 40 for performing a bending operation of the catheter 10, a coil 50, It has.
The sub-lumen 30 is formed with a smaller diameter than the main lumen 20, and is disposed around the main lumen 20 along the longitudinal direction of the catheter 10.
The operation line 40 is inserted into the sub-lumen 30 and is slidable with respect to the sub-lumen 30. The operation line 40 is fixed to the distal end portion (distal end portion 15) of the catheter 10.
The coil 50 is configured by an elastic body. The coil 50 is wound around the sub-lumen 30.
Details will be described below.

Next, the catheter 10 of this embodiment will be described in detail.

As shown in FIG. 1, the catheter 10 according to the present embodiment includes an inner layer 21 made of a resin material and an outer layer 60 formed around the inner layer 21.
The main body of the catheter 10 including the inner layer 21 and the outer layer 60 is referred to as a sheath 16.
Here, the inner layer 21 is formed in a tubular shape, and a hollow main lumen 20 extending in the longitudinal direction of the catheter 10 is configured by the inner space.

The outer layer 60 is made of the same or different resin material as the inner layer 21.
In the outer layer 60, a sub-lumen 30 having a smaller diameter than the main lumen 20 is formed as a hollow extending in the longitudinal direction of the catheter 10. That is, the sub-lumen 30 is disposed around the main lumen 20.
A coil 50 is wound around the sub-lumen 30. The coil 50 is included in the outer layer 60.

Here, the number of sublumens 30 is arbitrary, but the catheter 10 of the present embodiment has, for example, two sublumens 30. When a plurality of sub-lumens 30 are provided, the sub-lumens 30 are arranged in a distributed manner around the main lumen 20 axis. When the catheter 10 includes two sub-lumens 30 as in the present embodiment, it is preferable to arrange the sub-lumens 30 around the main lumen 20 at intervals of 180 degrees as shown in FIG.
The catheter 10 may have three or more sub-lumens 30. For example, when three sub-lumens 30 are provided, the sub-lumens 30 are preferably arranged around the main lumen 20 at intervals of 120 degrees.

Here, the distal end portion 15 of the catheter 10 refers to a range of a predetermined length including the distal end (tip) DE of the catheter 10. The distal end DE is also the distal end of the sheath 16. Further, the proximal end portion 17 of the catheter 10 refers to a predetermined length range including the proximal end CE of the catheter 10 (see FIG. 5). Similarly, the distal end portion of the sheath 16 refers to a predetermined length range including the distal end DE, and the proximal end portion of the sheath 16 refers to a predetermined length including the proximal end PE of the sheath 16. This is the range.

The sublumen 30 is open at least at the proximal end of the sheath 16, specifically, for example, at the proximal end PE of the sheath 16. In addition, you may open in the distal end DE side rather than the proximal end PE of the sheath 16. FIG.

The operation lines 40 are inserted into the respective sub-lumens 30, and the operation lines 40 are slidable with respect to the sub-lumen 30.

As shown in FIG. 1, the distal end (distal end 41) of the operation line 40 is fixed to the distal end 15 of the catheter 10.
A mode of fixing the distal end 41 of the operation line 40 to the distal end portion 15 is not particularly limited. For example, as shown in FIG. 1, the distal end 41 of the operation line 40 may be connected to a marker 66 described later, or may be welded to a portion other than the marker 66 in the distal end portion 15, or The marker 66 or the distal end portion of the sheath 16 may be adhered and fixed with an adhesive.

The operation line 40 is guided in the sub-lumen 30 from the distal end portion to the proximal end portion of the sheath 16. A proximal end 42 of the operation line 40 is led out from an opening of the sub-lumen 30 at the proximal end PE of the sheath 16 and is fixed to a slider 72 of the operation unit 70 described later.

When the slider 72 of the operation unit 70 is operated in a direction in which the proximal end 42 of the operation line 40 is pulled (that is, rightward in FIG. 6), a tensile force is applied to the distal end 15 of the catheter 10 via the operation line 40. As a result, the distal end portion 15 bends toward the sub-lumen 30 through which the operation line 40 is inserted.
The operation wire 40 is a wire made of a flexible material and has high flexibility. For this reason, even if the slider 72 of the operation unit 70 is operated in the direction in which the proximal end 42 of the operation line 40 is pushed into the catheter 10 (that is, the left direction in FIG. 6), the distal end 15 However, the pushing force is not substantially applied.

Here, the bending of the catheter 10 means that the catheter 10 is deformed (bent) so that the central axis of the catheter 10 (for example, the central axis of the main lumen 20) is not a straight line (such as a curved line or a polygonal line). To do.

The sub-lumen 30 through which the operation line 40 is inserted is provided apart from the main lumen 20 so that when the medicine or the like is supplied through the main lumen 20 or when the optical system is inserted, these sub-lumens 30 leak into the sub-lumen 30. You can avoid it.
Then, by winding the coil 50 around the sub-lumen 30 as in the present embodiment, the inner side of the catheter 10, that is, the main lumen 20 is protected from the sliding operation line 40, that is, the coil 50. . Here, the coil 50 being wound around the sub-lumen 30 means a state in which at least a part of the sub-lumen 30 through which the operation wire 40 is inserted is formed inside the winding of the coil 50. To do. The coil 50 may be completely embedded in the outer layer 60 without being exposed to the sublumen 30, or a part or all of the coil 50 may be exposed to the sublumen 30.

Around the outer layer 60 at the distal end portion of the sheath 16, a hydrophilic coat layer 64 having a lubrication treatment applied to the outer surface is optionally provided as the outermost layer of the sheath 16.

The distal end portion 15 of the catheter 10 is provided with a ring-shaped marker 66 made of a material that cannot transmit radiation such as X-rays. Specifically, a metal material such as platinum can be used for the marker 66. The marker 66 of this embodiment is provided around the main lumen 20 and inside the outer layer 60.
In the example of FIG. 1, the distal end 41 of the operation line 40 is connected and fixed to the marker 66.

As an example of the material of the inner layer 21, a fluorine-based thermoplastic polymer can be used. More specifically, polytetrafluoroethylene (PTFE), polyvinylidene fluoride (PVDF), perfluoroalkoxy fluororesin (PFA), or the like can be used.
By using a fluorine-based resin for the inner layer 21, the delivery property when supplying a contrast medium or a drug solution to the affected area through the main lumen 20 of the catheter 10 is improved.

As the material of the outer layer 60, for example, a thermoplastic polymer can be used. Examples include polyimide (PI), polyamideimide (PAI), polyethylene terephthalate (PET), polyethylene (PE), polyamide (PA), nylon elastomer, polyurethane (PU), ethylene-vinyl acetate resin (EVA), poly Vinyl chloride (PVC) or polypropylene (PP) can be used.

Here, as a method for inserting the operation line 40 into the sub-lumen 30, for example, the operation line 40 may be inserted from one end side of the sheath 16 of the catheter 10 on which the sub-lumen 30 is formed in advance. Alternatively, when the sheath 16 is extruded, the operation line 40 may be extruded together with the resin material and inserted into the sub-lumen 30.

When the operation line 40 is extruded together with the resin material and is inserted into the sub-lumen 30, the operation line 40 is required to have heat resistance equal to or higher than the melting temperature of the resin material constituting the sheath 16. In the case of the operation line 40, specific materials include, for example, polyether ether ketone (PEEK), polyphenylene sulfide (PPS), polybutylene terephthalate (PBT), polymer fibers such as PI or PTFE, or stainless steel. (SUS), a steel wire with a corrosion-resistant coating, a metal wire such as titanium or a titanium alloy can be used.
On the other hand, in the case where the operation line 40 is not required to have heat resistance, such as when the operation line 40 is inserted into the sub-lumen 30 of the sheath 16 formed in advance, in addition to the above materials, PVDF, high-density polyethylene ( HDPE) or polyester can also be used.

For the coating layer 64, a hydrophilic material such as polyvinyl alcohol (PVA) or polyvinyl pyrrolidone can be used.

Here, typical dimensions of the catheter 10 of the present embodiment will be described.
The radius of the main lumen 20 is about 200 to 300 μm, the thickness of the inner layer 21 is about 10 to 30 μm, the thickness of the outer layer 60 is about 100 to 220 μm, the outer diameter of the coil 50 is 70 to 160 μm, and the inner diameter of the coil 50 is 40 to 40 μm. It can be set to 100 μm. The radius from the axis of the catheter 10 (the sheath 16) to the center of the sublumen 30 can be about 300 to 450 μm, the inner diameter of the sublumen 30 can be 40 to 100 μm, and the thickness of the operation line 40 is 30. It can be ˜60 μm. The outermost radius (of the sheath 16) of the catheter 10 can be set to about 350 to 490 μm.
That is, the outer diameter of the catheter 10 of this embodiment is less than 1 mm in diameter, and can be inserted into blood vessels such as the celiac artery. In addition, the catheter 10 of the present embodiment is freely operated in the direction of travel by pulling the operation line 40, so that the catheter 10 can be advanced in a desired direction even in a branching blood vessel, for example.

As shown in FIG. 5, an operation unit 70 is provided at the proximal end portion 17 of the catheter 10.
The operation unit 70 includes a shaft portion 71 extending in the longitudinal direction of the catheter 10, and sliders 72 (for example, a first slider 72 a and a second slider 72 b) that move forward and backward in the longitudinal direction of the catheter 10 with respect to the shaft portion 71. The handle portion 74 that rotates around the axis of the shaft portion 71 integrally with the shaft portion 71 and the grip portion 75 into which the proximal end portion of the sheath 16 is rotatably inserted around the shaft are provided.
The proximal end portion of the sheath 16 is fixed to the shaft portion 71.
The distal end portion 15 of the catheter 10 can be bent by performing an operation of pulling a plurality of operation lines 40 individually or simultaneously on the slider 72 of the operation unit 70. It has become.
Further, for example, the entire sheath 16 can be rotated together with the shaft portion 71 by rotating the handle portion 74 with respect to the gripping portion 75 with the other hand while holding the gripping portion 75 with one hand. It can be done.

Here, as described above, in the case of this embodiment, the catheter 10 includes, for example, two sub-lumens 30 and the operation lines 40 respectively inserted through the sub-lumens 30.
Hereinafter, for convenience of explanation, one sub-lumen 30 is referred to as a first sub-lumen 30a, and the other sub-bloom 30 is referred to as a second sub-bloom 30b (see FIG. 1). The operation line 40 inserted into the first sub-lumen 30a is referred to as a first operation line 40a, and the operation line 40 inserted into the second sub-lumen 30b is referred to as a second operation line 40b (FIG. 1, FIG. 5).

The proximal end 42 a of the first operation line 40 a is connected to the first slider 72 a of the operation unit 70. Similarly, the proximal end 42 b of the second operation line 40 b is connected to the second slider 72 b of the operation unit 70.
Then, by sliding the first slider 72a and the second slider 72b individually to the proximal end side with respect to the shaft portion 71, the first operation line 40a or the second operation line 40b connected thereto is individually pulled. Then, a tensile force is applied to the distal end portion 15 of the catheter 10 (that is, the distal end portion of the sheath 16). As a result, the distal end portion 15 bends toward the pulled operation line 40.
When individually pulling the operation line 40 of the first operation line 40a or the second operation line 40b, the curvature of the distal end portion 15 changes according to the distance to which the operation line 40 is pulled.
When the distal end portion 15 cannot be bent to a desired posture by merely pulling the operation lines 40 individually, the first operation line 40a and the second operation line 40b are simultaneously pulled to A desired posture of the distal end portion 15 may be realized.
In this manner, the distal end portion 15 is bent into various shapes, and the rotational phase of the sheath 16 is adjusted by the rotation operation with respect to the handle portion 74, thereby adjusting the bending amount and the bending direction of the distal end portion 15. The catheter 10 can be freely entered into a body cavity that branches at various angles.
Therefore, for example, the catheter 10 of the present embodiment can be advanced in a desired direction even for a branched blood vessel or a peripheral blood vessel.
In addition, in the catheter 10 of this embodiment, it is preferable that the bending angle of the distal end part 15 exceeds 90 degrees. Thereby, even if it is a case where the branch angle of a blood vessel is an acute angle which makes a U-turn, the catheter 10 can be made to approach with respect to this branch branch.

Next, the coil 50 will be described in detail.

As shown in FIG. 3, the coil 50 is configured by, for example, bending a single wire 50a formed of an elastic body in a spiral shape.
As shown in FIGS. 1 and 4, a plurality of sublumens 30 are formed in the sheath 16 (inner layer 21 or outer layer 60) so as to extend in the axial direction. Here, the sub-lumen 30 may be provided by hollowly molding the resin material of the sheath 16. Alternatively, the sub-lumen 30 may be provided by embedding a preformed hollow tube in the sheath 16. The coil 50 of this embodiment is wound around each sub-lumen 30. However, the coil 50 may be included in the sheath 16 (inner layer 21, outer layer 60) or a hollow tube constituting the peripheral wall of the sub-lumen 30.
Alternatively, a part of the coil 50 may be exposed inside the sheath 16 or the hollow tube constituting the peripheral wall of the sub-lumen 30. In this case, the coil 50 constitutes a part of the peripheral wall of the sub-lumen 30. When the wire 50a is made of a metal material, the coil 50 in which the wire 50a is covered with a resin film (not shown) may be used.

The coil 50 of this embodiment is wound around at least the tip of the sub-lumen 30.
Specifically, for example, the coil 50 extends from the distal end portion to the proximal end portion of the sub-lumen 30 (see FIG. 5).

As a material of the wire 50a constituting the coil 50, for example, a metal is preferably used. However, the material is not limited to this example, and any other material may be used as long as it is more rigid and elastic than the inner layer 21 and the outer layer 60. (For example, resin) may be used.
Specifically, for example, stainless steel (SUS), nickel titanium alloy, steel, titanium, or copper alloy can be used as the metal material of the wire 50a.
Although the cross-sectional shape of the wire 50a is not specifically limited, For example, it is a preferable example that it is circular.

By providing such a coil 50, the morphological stability of the sub-lumen 30 can be improved, and as a result, the stiffness and morphological stability of the catheter 10 can be improved. Here, the stiffness of the catheter 10 is the form stability when a bending or torque load is applied to the catheter 10.

The coil 50 may have a uniform winding pitch of the wire 50 a over the entire length of the coil 50.
However, as will be described below, in the coil 50, it is also preferable that the winding pitch of the wire 50a at the distal end portion is larger than the winding pitch of the wire 50a at the proximal end portion.

That is, as shown in FIG. 3, the coil 50 includes, for example, a first portion 51 including a distal end portion of the coil 50, and a proximal end (base end) CE of the catheter 10 than the first portion 51 (see FIG. 5). And a second portion 52 located on the side.
The winding pitch of the first portion 51 is set larger than the winding pitch of the second portion 52.

Hereinafter, a winding state in which adjacent windings among the windings wound spirally in the coil 50 are substantially in contact with each other is referred to as a dense winding of the coil 50. However, due to the accuracy of the winding work of the coil 50, in the tightly wound state, not only when adjacent windings are in contact with each other over the entire circumference, but also a local gap (clearance) between adjacent windings. ) Is allowed to exist. This gap (clearance) measured in the winding axis direction is preferably equal to or less than the diameter of the winding.
On the other hand, a state in which adjacent windings are wound with a predetermined gap (pitch interval) is referred to as pitch winding. The size of the gap (pitch interval) is not particularly limited.

In the case of the present embodiment, for example, in the second portion 52 of the coil 50, the adjacent "windings" are closely wound.

Here, when the coil 50 is pitch-wound, the axial distance between adjacent windings can be expanded and contracted. For this reason, when the distal end portion of the catheter 10 is bent, the pitch of the winding outside the bend is enlarged, and the pitch of the winding inside the bend is shortened. Thereby, the coil 50 of pitch winding deform | transforms following the bending | flexion of the catheter 10 flexibly. Since the coil 50 is bent while maintaining the circular winding shape, the sub-lumen 30 is prevented from kinking even when the catheter 10 is bent, and the pulling operation of the operation line 40 is not impaired.

On the other hand, by making the coil 50 densely wound, the adjacent windings are restricted from moving in the axial direction, so that the catheter 10 is prevented from bending.
In the case of the pitch-wound coil 50, the smaller the pitch interval of the wire 50a, the more flexible it bends, and the greater the pitch interval, the lower the elasticity as a spring. For this reason, the order of the bending rigidity of the coil 50 is (1) dense winding, (2) pitch winding (pitch interval large), and (3) pitch winding (pitch interval small).

Next, an example of a method for manufacturing the catheter 10 will be described.

First, the inner layer 21 is formed as a film on a cylindrical mandrel which is optionally mold-released on the surface.
Next, the outer layer 60 is extruded around the inner layer 21. At the time of this extrusion molding, the hollow tube constituting the sub-lumen 30 is extruded, the hollow tube is embedded in the outer layer 60, and the coil 50 is extruded so as to be extrapolated into the hollow tube. Embedded in the outer layer 60.
The hollow tube is formed in advance before this extrusion molding. The hollow tube is made of a material having a melting temperature higher than that of the outer layer 60 so that the hollow tube does not melt during extrusion molding.
Next, the operation line 40 is inserted into the hollow tube embedded in the outer layer 60.
Next, the distal end 41 of the operation line 40 is fixed to the distal end 15 of the catheter 10.
Next, the mandrel is removed from the inner layer 21. At this time, if necessary, the mandrel is reduced in diameter by pulling both ends of the mandrel in opposite directions.
Thus, the catheter 10 including the main lumen 20, the sub-lumen 30, the operation line 40, and the coil 50 can be manufactured.
The operation line 40 is extruded into the resin layer while performing the extrusion molding of the outer layer 60 and the extrusion molding of the resin layer constituting the sub-lumen 30 in parallel without using the hollow tube constituting the sub-lumen 30. May be.

Next, the operation of the catheter 10 will be described.

In the present embodiment, the first sub-lumen 30a and the second sub-lumen 30b are formed so as to face each other by 180 degrees across the axis of the catheter 10. The first operation line 40a is inserted through the first sub-lumen 30a, and the second operation line 40b is inserted through the second sub-lumen 30b.

In the catheter 10 of the present embodiment, when the operation portion 70 (FIG. 6) is operated to pull the first operation line 40a toward the proximal end CE, the distal end of the catheter 10 as shown in FIG. 6 (a). The part 15 bends upward in FIG. Further, when this pulling amount is increased, the distal end portion 15 of the catheter 10 is greatly bent upward in FIG. 6 as shown in FIG.
When the operation unit 70 is operated and the second operation line 40b is pulled toward the proximal end CE, the distal end 15 of the catheter 10 bends downward in FIG. 6 as shown in FIG. 6B. . Further, when this pulling amount is increased, the distal end portion 15 of the catheter 10 is greatly bent downward in FIG. 6 as shown in FIG.

Note that when the first operation line 40a and the second operation line 40b are pulled together, the pulling amounts may be different from each other. That is, if a desired curvature is not achieved even if any of the operation lines 40 is pulled individually, the curvature may be adjusted by pulling both the operation lines 40.
More specifically, by pulling one of the other operation lines 40, an operation for reducing the amount of bending of the distal end portion 15 or an original linear posture from a state in which the posture of the distal end portion 15 is bent. The operation to return to can be performed. The amount of bending can be finely adjusted by the operation of reducing the amount of bending.

Further, by performing an operation of rotating the catheter 10 by a maximum of 90 degrees while the distal end portion 15 of the catheter 10 is bent, the operator changes the bending direction of the distal end portion 15 of the catheter 10 to a desired direction. Can be changed.
Since the coil 50 is wound around the sub-lumen 30, the torsional rigidity of the sheath 16 is increased. Therefore, the torque transmission efficiency during the rotation operation of the catheter 10 is increased, and the rotation response of the distal end portion 15 to the rotation operation is improved.

The bending mode of the coil 50 during the bending operation of the catheter 10 will be described. The coil 50 is largely bent at the first portion 51 on the distal end side, whereas the bending of the second portion 52 by the bending operation is the first portion 51. Small compared to that of. Specifically, for example, in the second portion 52, bending along the shape of the body cavity is free, but bending due to the bending operation hardly occurs. This is because the second portion 52 is tightly wound and is not substantially compressed even when the operation line 40 is pulled.

Here, if the coil 50 is tightly wound over its entire length, the coil 50 is not compressed even when the operation wire 40 is pulled, so that the bending operation of the distal end portion 15 by pulling the operation wire 40 is performed. It becomes difficult. This is even more so when the coil 50 extends from the distal end portion to the proximal end portion of the sub-lumen 30.
On the other hand, in this embodiment, the winding pitch of the first portion 51 including the tip portion of the coil 50 is larger than the winding pitch of the second portion 52. In other words, the first portion 51 is always pitch-wound (not tightly wound).
For this reason, in the 1st part 51 of the coil 50, since the side of the pulled operation line 40 exhibits the behavior compressed, the bending operation of the distal end part 15 by the pulling of the operation line 40 can be performed easily.

In the catheter 10 according to the embodiment as described above, since the coil 50 formed of an elastic body is wound around the sub-lumen 30, the coil 10 is bent when the catheter 10 is bent by the operation on the operation line 40. An external force is applied to 50 to bend its axial direction. However, the coil 50 tries to resist the external force by its elastic repulsive force.
Therefore, the sudden bending of the sub-lumen 30 can be suppressed. Thereby, since the increase in the friction coefficient between the peripheral wall of the sub-lumen 30 and the operation line 40 can be suppressed, the bending operability of the catheter 10 using the operation line 40 can be maintained in a good state, and the disconnection of the operation line 40 can be prevented. Occurrence can also be suppressed.
However, since the coil 50 can be bent in accordance with an external force that attempts to bend its axial direction, the flexibility of the catheter 10 can be sufficiently ensured.
In short, it is possible to suppress the sudden bending of the sub-lumen 30 by the elastic repulsive force of the coil 50 while sufficiently securing the flexibility of the catheter 10.

Moreover, not only can the sudden bending of the sub-lumen 30 be suppressed in this way, but also the sudden bending of the catheter 10 can be suppressed. For this reason, the sharp bending of the main lumen 20 can also be suppressed. Thereby, since the internal space cross-sectional area of the main lumen 20 can be maintained at a sufficient size, it is possible to suitably perform the supply of medicines and the like through the main lumen 20 and the insertion of the optical system.

In addition, since the coil 50 is wound at least around the distal end portion of the sublumen 30, the steep angle of the catheter 10 while sufficiently securing the flexibility of the catheter 10 at the distal end portion 15 of the catheter 10 is ensured. Can be bent.

The coil 50 includes a first portion 51 including the distal end portion of the coil 50, and a second portion 52 located closer to the proximal end CE side (base end side) of the catheter 10 than the first portion 51, The winding pitch of the first portion 51 is larger than the winding pitch of the two portions 52.
For this reason, in the 1st part 51 of the coil 50, since the side of the pulled operation line 40 exhibits the behavior compressed, the bending operation of the distal end part 15 by the pulling of the operation line 40 can be performed easily.
Moreover, since the winding pitch of the second portion 52 is smaller than the winding pitch of the first portion 51, when the catheter 10 is pushed into the body cavity, the pushing force is applied to the first portion 51 via the second portion 52. Can be transmitted effectively. That is, the pushability of the catheter 10 can be improved. The pushability of the catheter 10 is further improved by the coil 50 extending from the distal end portion to the proximal end portion of the main lumen 20. Furthermore, the pushability of the catheter 10 is remarkably improved because the second portion 52 of the coil 50 is tightly wound.

The present invention is not limited to the above-described embodiment, and includes various modifications and improvements as long as the object of the present invention is achieved.

For example, in the above embodiment, in the outer layer 60, a blade layer (not shown) formed by knitting wires may be disposed at a position on the outer peripheral side or the inner peripheral side of the sub-lumen 30 and the coil 50.

In the above embodiment, an example in which the winding pitch in the first portion 51 of the coil 50 is constant has been described. However, the present invention is not limited to this example, and the winding pitch of the wire 50a in the first portion 51 is not limited to this example. It may be changed in multiple stages.
As the coil 50 has a larger winding pitch, a force (hereinafter referred to as bending rigidity) that resists an external force that attempts to bend the axial direction 58 (FIG. 3) increases.
For this reason, by changing the winding pitch of the wire 50a in the first portion 51 in a plurality of steps, the bending rigidity in the first portion 51 also changes in a plurality of steps, so that the flexibility at the distal end portion 15 of the catheter 10 is increased. It can be set stepwise in the longitudinal direction.

For example, in the example illustrated in FIG. 7A, the first portion 51 of the coil 50 includes a third portion 53 that is a tip portion of the coil 50, and a proximal end CE side (base) of the catheter 10 with respect to the third portion 53. And a fourth portion 54 located on the end side.
For example, the fourth portion 54 is adjacent to the third portion 53 on the proximal end CE side of the catheter 10.
The winding pitch of the third portion 53 is set smaller than the winding pitch of the fourth portion 54.
In this example, the flexibility at the third portion 53 with a small winding pitch is higher than the flexibility at the fourth portion 54. For this reason, the flexibility at the distal end portion of the catheter 10 can be improved.
In addition, since the winding pitch of the fourth portion 54 located on the base end side with respect to the third portion 53 is larger than the winding pitch of the third portion 53, the fourth portion 54 of the coil 50 is larger than the third portion 53. High bending rigidity.

Here, a case will be described in which the catheter 10 that has progressed in a straight blood vessel is guided from this blood vessel to a blood vessel that branches vertically.
When the winding pitch of the first portion 51 of the coil 50 is constant, even if the distal end of the catheter 10 is caught in the branch at the branch of the blood vessel (even if the distal end DE enters the blood vessel side of the branch destination). When the catheter 10 is further pushed in, the coil 50 is buckled and the catheter 10 may not be guided to the branch destination blood vessel and may go straight through the branch source blood vessel.
On the other hand, as shown in FIG. 7A, the first portion 51 includes the third portion 53 and the fourth portion 54, so that the catheter 10 can smoothly enter the branching vessel. it can.
That is, when a portion of the distal end portion 15 of the catheter 10 corresponding to the third portion 53 of the coil 50 is hooked to the branch and then the catheter 10 is further pushed in, the third portion is passed through the fourth portion 54 having a large bending rigidity. The second portion 52 is bent while pushing 53. Thereby, the 3rd part 53 can be pushed in smoothly in the direction of the blood vessel of a branch destination.
Here, during this operation, since the curvature of the fourth portion 54 is relatively small (compared to the third portion 53), the fourth portion 54 suppresses the buckling of the fourth portion 54 and the third portion. This is the operation of suitably pushing 53.
Then, when the second portion 52 passes through the branch, the third portion 53 and the fourth portion 54 have already advanced in the correct direction (into the branch target blood vessel), so the second portion 52 is also pushed. It can follow the 3rd part 53 and the 4th part 54, and can progress in the blood vessel of a branch destination, without buckling and bending.
As described above, the coil 50 includes the fourth portion 54 on the proximal end side of the third portion 53, whereby the catheter 10 can be more reliably guided to a desired direction at the branch portion.

In the example shown in FIG. 7B, the winding pitch of the fourth portion 54 is set smaller than the winding pitch of the third portion 53 on the tip side, contrary to the example of FIG. 7A. Has been.
In this example, the bendability at the fourth portion 54 with a small winding pitch can be made higher than the bendability at the third portion 53. In other words, the shape retention in the third portion 53 is enhanced as compared with the case of FIG. For this reason, compared with the case of Fig.7 (a), the shape retention property in the front-end | tip part of the catheter 10 is securable. Therefore, there is an advantage that the propulsive force of the catheter 10 can be improved.

Further, in the example shown in FIG. 7C, the first portion 51 of the coil 50 has a proximal end CE side (base end side) of the catheter 10 with respect to the fourth portion 54 in addition to the configuration of FIG. ) And the fifth portion 55.
For example, the fifth portion 55 is adjacent to the fourth portion 54 on the proximal end CE side of the catheter 10.
The winding pitch of the fifth portion 55 is set smaller than the winding pitch of the fourth portion 54. For example, in the fifth portion 55 and the third portion 53, the winding pitch is set to be equal to each other.
In this example, the same effect as in the case of FIG. 7A can be obtained, and the effect that the flexibility at the fifth portion 55 located on the rear side of the fourth portion 54 can be improved.
In this case, when the catheter 10 is further pushed after the portion corresponding to the third portion 53 of the coil 50 is hooked at the distal end portion 15 of the catheter 10, the third portion passes through the fourth portion 54 having a large bending rigidity. While the portion 53 is pushed in, the fifth portion 55 is bent.
During this operation, the curvature of the fourth portion 54 is relatively small (compared to the third portion 53 and the fifth portion 55), so that the fourth portion 54 prevents the fourth portion 54 from buckling. This is an operation to favorably push the three portions 53.
Then, when the fifth portion 55 passes through the branch, the third portion 53 and the fourth portion 54 have already advanced in the correct direction (into the blood vessel at the branch destination). It can follow the 3rd part 53 and the 4th part 54, and can progress in the blood vessel of a branch destination, without buckling and bending.
In the example of FIG. 7C, the third portion 53 that is the most distal portion of the first portion 51 may be closely wound.

<Second embodiment>
FIG. 8 is a side sectional view of the distal end portion of the catheter 10 according to the second embodiment of the present invention.
The left side of the figure corresponds to the distal end side of the catheter 10, and the right side corresponds to the proximal end side. In the same figure, the intermediate part and the proximal end side of the catheter 10 are not shown.
FIG. 9 is an enlarged view showing the vicinity of the coil 50 in the catheter 10 of the present embodiment.

The catheter 10 of this embodiment includes a hollow tube 32 in which a sub-lumen 30 is formed and an operation line 40 is inserted. The coil 50 is provided on the distal end side of the hollow tube 32, and the sub-lumen 30 is formed continuously from the coil 50 to the hollow tube 32.

In the catheter 10 of the present embodiment, the coil 50 is provided over several tens of millimeters at the distal end portion, and the hollow tube 32 is provided from the intermediate portion to the proximal end portion of the catheter 10.
When a plurality of sublumens 30 are provided, the coils 50 and the hollow tubes 32 may be connected to all of them, or only a part of the sublumens 30 may be connected to the coils 50 and the hollow tubes 32. Also good.

The catheter 10 (outer layer 60) is made of a resin material. The hollow tube 32 is made of a material having a higher melting point and lower adhesion than the resin material. That is, the melting point of the material of the hollow tube 32 is higher than the melting point of the resin material of the outer layer 60. And the adhesiveness of the material of the hollow tube 32 is lower than the adhesiveness of the resin material of the outer layer 60.

Specifically, for the hollow tube 32 of the present embodiment, a fluorine-based polymer material such as PTFE, PFA, or a tetrafluoroethylene / hexafluoropropylene copolymer (FEP) can be used. In addition, the hollow tube 32 includes PI, PAI, polysulfone (PSF), polyethersulfone (PES), polyphenylene sulfide (PPS), polyetheretherketone (PEEK), polyetherimide (PEI), or liquid crystal polymer. Non-fluorine polymer materials such as (LCP) can also be used.

The hollow tube 32 has a higher melting point than the resin material constituting the outer layer 60. Thereby, when the outer layer 60 is thermoformed in a state where the hollow tubes 32 are arranged in parallel around the inner layer 21, the hollow tubes 32 are not melted.
For example, the hollow tube 32 is made of PTFE (melting point = 327 ° C.), PFA (melting point = 302 ° C.) or PEEK (melting point = 334 ° C.), and the outer layer 60 (resin material) is nylon elastomer (melting point = 160-220 ° C.). ), PU (melting point = 60-140 ° C.) or EVA (melting point = about 90 ° C.).

For the thermoforming of the outer layer 60, an extrusion molding method may be used, or after the outer layer 60 previously formed into a tubular shape is mounted around the inner layer 21 and the hollow tube 32, it is press-molded in a heating environment with a heat-shrinkable material. May be. Here, the melting point of the hollow tube 32 is higher than the melting point of the outer layer 60 by 10 ° C. or more, preferably 30 ° C. or more, more preferably 100 ° C. or more. Thereby, when the outer layer 60 is heated to a sufficient temperature equal to or higher than the melting point and thermoformed, the hollow tube 32 is preferably prevented from melting.

The polymer material for forming the hollow tube 32 may be mixed with an inorganic filler such as silica, talc, calcium carbonate, aluminum hydroxide, magnesium hydroxide, and titanium dioxide. By mixing the inorganic filler with the polymer material to improve the smoothness of the inner wall surface of the hollow tube 32, the workability when inserting the operation line 40 into the hollow tube 32 is improved. Friction reduction during traction operation is achieved.

The bending rigidity of the coil 50 is smaller than the bending rigidity of the hollow tube 32. In other words, the middle portion and the proximal end portion of the catheter 10 can be given sufficient stiffness due to the large bending rigidity of the hollow tube 32, and the flexible coil 50 can be given good flexibility at the distal end portion.

Further, the catheter 10 of the present embodiment further includes another coil (main coil 80) spirally wound between the main lumen 20 and the sub-lumen 30. The wire diameter of the other coil (main coil 80) is larger than the wire diameter of the coil 50.

More specifically, the main coil 80 is spirally wound around the inner layer 21 around the axis of the main lumen 20 as a winding axis. The cross-sectional shape of the wire 80a of the main coil 80 is not particularly limited, and may be a round wire or a flat wire (square wire). Here, the wire diameters of the main coil 80 and the coil 50 are the diameters of circles having the same area as the cross sections of the wire rods 80a and 50a.

Further, the wire diameters of the wire rods 80a and 50a of the main coil 80 and the coil 50 may be increased continuously or stepwise in the axial direction from the distal end side to the proximal end side of the catheter 10. In addition, when the wire diameters of the wire rods 80a and 50a change depending on the position in the axial direction as described above, the wire diameter of the wire rod 80a of the main coil 80 is larger than the wire diameter of the wire rod 50a of the coil 50. It means that the wire diameter of the wire 80a when compared at the same position is larger than the wire diameter of the wire 50a.

The main coil 80 is pitch-wound at the distal end 15 and densely wound at the proximal end 17. That is, the main coil 80 includes a pitch winding area 81 and a dense winding area 82 as shown in FIG. Accordingly, the main coil 80 is given high flexibility by the pitch winding region 81 at the distal end portion 15, and sufficient stiffness (shape retention) is given to the catheter 10 by the close winding region 82 at the proximal end portion 17. Is done.

A shaping unit 90 is provided on the tip side of the marker 66. The shaping portion 90 is a length region where a pre-shape that is pre-shaped into an arbitrary shape such as a bent or curved shape when the catheter 10 is manufactured, or a post-shape that is formed into an arbitrary shape when the catheter 10 is used. The shaping unit 90 is formed by laminating an inner layer 21, an outer layer 60, and a coat layer 64 made of a resin material. The marker 66, the main coil 80, the operation line 40, and the sub-lumen 30 are provided on the proximal end side with respect to the shaping unit 90.

By providing the main coil 80 around the main lumen 20 as in the present embodiment, the main lumen 20 is prevented from kinking when the catheter 10 is bent. Further, the catheter 10 is prevented from bending at a steep angle.
In addition, the main coil 80 further increases the transmission effect of the pushing force in the axial direction of the catheter 10 and the torque transmission efficiency when the catheter 10 is rotated.

As shown in FIG. 9, the coil 50 of the present embodiment also includes a first portion 51 including a distal end portion, and is positioned closer to the proximal end of the catheter 10 than the first portion 51, and a winding pitch than the first portion 51. And a second portion 52 having a small size. The second portion 52 is a first densely wound region in which the wire 50a is wound closely.

The first portion 51 of the present embodiment includes a first pitch winding region (fifth portion 55) in which adjacent windings have a gap, and a further tip of the first pitch winding region (fifth portion 55). And a second densely wound region (fourth portion 54) provided on the side.

The first portion 51 of the present embodiment optionally includes a second pitch winding region (third portion 53) provided further on the distal end side of the fourth portion 54.
In other words, in the coil 50 of the present embodiment, the wire 50a is spirally wound in the order of pitch winding, dense winding, pitch winding, and dense winding in order from the tip side.

The inside of the coil 50 is hollow, and the distal end portion of the operation wire 40 is fixed to the catheter 10 at a position further on the distal end side of the second densely wound region (fourth portion 54) of the coil 50. More specifically, in the coil 50, the inside of the second portion 52, the fifth portion 55, and the fourth portion 54 is hollow, and the third portion 53 on the further distal end side of the fourth portion 54 is solid and inside. An outer layer 60 is formed on the surface.

In other words, in the outer layer 60 of the present embodiment, the gap portion 34 is formed from the second portion 52 to the fifth portion 55 and the fourth portion 54. The gap 34 has a columnar shape and constitutes a part of the sub-lumen 30. The diameter of the gap 34 is larger than the inner diameter of the coil 50, and at least a part of the wire 50 a is exposed to the gap 34. Further, the diameter of the gap 34 may be larger than the outer diameter of the coil 50. In this case, the wire 50a whose tip is fixed to the third portion 53 is separated from the outer layer 60 in the entire length of the fourth portion 54, the fifth portion 55, and the second portion 52, or a gap portion. 34 may be completely exposed.

In the axial direction of the coil 50, in the pitch winding region (fifth portion 55) on the most proximal side, part or all of the wire 50a is exposed to the sub-lumen 30. More specifically, the wire 50 a in the fifth portion 55 is completely exposed to the sub-lumen 30. As a result, the windings in the fifth portion 55 can move relative to each other in the axial direction. For this reason, the catheter 10 can be flexibly deformed in the fifth portion 55.

Therefore, when the operation line 40 is pulled, the bending position of the catheter 10 is specified as the fifth portion 55. In other words, the catheter 10 of the present embodiment has the largest curvature in the fifth portion 55 when the operation line 40 is pulled, and the distal end DE (see FIG. 8) is bent and deformed exclusively from the fifth portion 55. To do. When the pulling length of the operation line 40 is changed, although the bending angle from the fifth portion 55 to the distal end DE changes, the bending length region becomes almost unchanged. Thereby, for example, the operation of selecting one of the branched blood vessels and allowing the catheter 10 to enter is facilitated. In this case, in a state where the fifth portion 55 is positioned in the vicinity of the bifurcation of the blood vessel, the desired blood vessel can be obtained without changing the bending position by adjusting the bending direction of the catheter 10 and the pulling length of the operation line 40 to a predetermined value. The catheter 10 can be bent in accordance with the branch angle. By pushing the catheter 10 in such a state, the catheter 10 can be easily entered into the blood vessel.

As for the second part 52 and the fourth part 54, whether or not the wire 80a is exposed to the sub-lumen 30 as long as the sub-lumen 30 is formed in the inside and the operation line 40 can slide. Is optional. Therefore, the wire 80 a may be embedded in the outer layer 60 in the second portion 52 and the fourth portion 54.

The second pitch winding region (third portion 53) is impregnated with the outer layer 60, and the tip end portion of the operation line 40 is welded to the outer layer 60 inside the third portion 53.
Thereby, since the tension when the operation line 40 is pulled is transmitted to the entire third portion 53 through the outer layer 60, the operation line 40 comes out of the outer layer 60 even when a large traction force is applied to the operation line 40. There is no.

The first densely wound region (second portion 52) corresponding to the most proximal end portion of the coil 50 is abutted against the distal end of the hollow tube 32. Thereby, the bending rigidity of the catheter 10 does not become remarkably discontinuous at the boundary between the hollow tube 32 and the coil 50 (second portion 52). Further, by sandwiching the distal end side and the proximal end side of the fifth portion 55 between the closely wound regions (the second portion 52 and the fourth portion 54), the operation line 40 is centered on the fifth portion 55 having the maximum curvature. During the pulling operation, the catheter 10 bends smoothly.

The catheter 10 of this embodiment can be manufactured as follows.
First, the inner layer 21 is formed around a mandrel (not shown), and the main coil 80 is wound around the inner layer 21.

On the other hand, the hollow tube 32 is abutted against the proximal end portion (second portion 52) of the coil 50 formed by spirally winding the wire 50a in advance, and from the proximal end side of the hollow tube 32 to the fourth portion 54 of the coil 50. In the meantime, a core material (not shown) having the same diameter as the inner diameter of the coil 50 is inserted.

The core material, the coil 50 and the hollow tube 32 are fixed around the main coil 80 along the axial direction. In this state, the resin material is extruded, and the outer layer 60 is formed by covering the coil 50 and the hollow tube 32. At this time, the third portion 53 is impregnated with the resin material because the wire 50a is in a pitch winding state and the core material is not inserted.

Next, after the core material is removed from the coil 50 and the hollow tube 32 to the proximal end side to form the sub-lumen 30 hollow, the operation wire 40 is inserted into the sub-lumen 30. Thereby, the wire 50 a in the second portion 52 to the fourth portion 54 including the fifth portion 55 is exposed to the sub-lumen 30. For this reason, the wire 50a in the 5th part 55 can move back and forth between windings, and high flexibility is acquired. Further, since the sliding operation line 40 contacts the inner peripheral surface of the coil 50 and does not contact the outer layer 60, the operation line 40 can be pulled with low friction.

Then, with the entire outer layer 60 or the vicinity of the third portion 53 heated to the softening temperature or higher, the distal end portion of the operation line 40 is inserted into the outer layer 60 inside the third portion 53, and then the outer layer 60 is cooled and cured. Then, the operation line 40 is fixed.

Then, the coat layer 64 and the marker 66 (see FIG. 8) are provided, the mandrel is removed from the inner layer 21, the main lumen 20 is formed, and the operation unit 70 (see FIG. 6) is further attached to create the catheter 10. Is done.

Moreover, in the said 1st and 2nd embodiment, although the catheter 10 demonstrated the example which has the two operation lines 40 (1st operation line 40a, 2nd operation line 40b), it is not restricted to this. Three or more sublumens 30 through which the operation lines 40 are inserted may be formed on the sheath 16. In this case, the bending operation of the catheter 10 can be performed by pulling one or more of the operation lines 40. In this case, the distal end portion 15 can be bent in any direction over 360 degrees by individually controlling the pulling lengths of the three or more operation lines 40. Thus, the approach direction of the catheter 10 can be performed only by pulling the operation line 40 by the operation unit 70 without performing a rotation operation for applying a rotational force to the entire catheter 10 and directing the distal end portion 15 in a predetermined direction. Can be operated.
In addition, the catheter 10 may have a configuration having only one operation line 40. Also in this case, the distal end portion 15 can be bent in an arbitrary bending amount direction and direction by using the bending operation of the distal end portion 15 by pulling the operation line 40 and the rotating operation of the catheter 10 together.

This application claims priority based on Japanese Patent Application No. 2009-215806 filed on September 17, 2009 and Japanese Application No. 2010-116373 filed on May 20, 2010. The entire disclosure is incorporated herein.

Claims

A main lumen disposed along the length of the catheter;
A sub-lumen formed with a smaller diameter than the main lumen and disposed along the longitudinal direction around the main lumen;
An operation line that is slidably inserted into the sub-lumen and is fixed to the distal end of the catheter;
A coil composed of an elastic body and wound around the sublumen;
A catheter comprising:
The catheter according to claim 1, wherein the coil is wound around at least a tip portion of the sublumen.
The coil is
A first portion including a distal end portion of the coil, and a second portion located closer to the proximal end of the catheter than the first portion;
Including
The catheter according to claim 1 or 2, wherein the winding pitch of the first part is larger than the winding pitch of the second part.
4. The catheter according to claim 3, wherein the coil is a close winding in which adjacent windings are in contact with each other in the second portion.
The catheter according to claim 4, wherein the first portion includes a pitch winding region in which adjacent windings have a gap, and a dense winding region provided further on the distal end side of the pitch winding region.
The inside of the coil is hollow,
The catheter according to claim 5, wherein a distal end portion of the operation line is fixed to the catheter at a position further on the distal end side of the tightly wound region of the coil.
The catheter further comprises a hollow tube in which the sublumen is formed and the operation line is inserted;
The coil is provided on the distal end side of the hollow tube, and the sublumen is formed continuously from the coil to the hollow tube. The catheter according to Item.
The catheter according to claim 7, wherein the catheter is made of a resin material, and the hollow tube is made of a material having a higher melting point and lower adhesion than the resin material.
The catheter according to claim 7 or 8, wherein the bending rigidity of the coil is smaller than the bending rigidity of the hollow tube.
The catheter further comprises another coil spirally wound between the main lumen and the sub-lumen;
The catheter according to any one of claims 1 to 9, wherein a wire diameter of the other coil is larger than a wire diameter of the coil.
The catheter according to any one of claims 1 to 6, wherein the coil extends from a distal end portion to a proximal end portion of the sublumen.
A plurality of the sub-lumens through which the operation lines are inserted are arranged around the axis of the main lumen,
The catheter according to any one of claims 1 to 11, wherein the coil is wound around each sublumen.