WO2013128910A1 - 医療機器の製造方法および医療機器 - Google Patents
医療機器の製造方法および医療機器 Download PDFInfo
- Publication number
- WO2013128910A1 WO2013128910A1 PCT/JP2013/001151 JP2013001151W WO2013128910A1 WO 2013128910 A1 WO2013128910 A1 WO 2013128910A1 JP 2013001151 W JP2013001151 W JP 2013001151W WO 2013128910 A1 WO2013128910 A1 WO 2013128910A1
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- WIPO (PCT)
- Prior art keywords
- hollow tube
- core wire
- medical device
- main body
- longitudinal direction
- Prior art date
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0009—Making of catheters or other medical or surgical tubes
- A61M25/0012—Making of catheters or other medical or surgical tubes with embedded structures, e.g. coils, braids, meshes, strands or radiopaque coils
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0021—Catheters; Hollow probes characterised by the form of the tubing
- A61M25/0023—Catheters; Hollow probes characterised by the form of the tubing by the form of the lumen, e.g. cross-section, variable diameter
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0021—Catheters; Hollow probes characterised by the form of the tubing
- A61M25/0023—Catheters; Hollow probes characterised by the form of the tubing by the form of the lumen, e.g. cross-section, variable diameter
- A61M25/0026—Multi-lumen catheters with stationary elements
- A61M25/0032—Multi-lumen catheters with stationary elements characterized by at least one unconventionally shaped lumen, e.g. polygons, ellipsoids, wedges or shapes comprising concave and convex parts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/0105—Steering means as part of the catheter or advancing means; Markers for positioning
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/0105—Steering means as part of the catheter or advancing means; Markers for positioning
- A61M25/0133—Tip steering devices
- A61M25/0147—Tip steering devices with movable mechanical means, e.g. pull wires
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- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04C—ROTARY-PISTON, OR OSCILLATING-PISTON, POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; ROTARY-PISTON, OR OSCILLATING-PISTON, POSITIVE-DISPLACEMENT PUMPS
- F04C2270/00—Control; Monitoring or safety arrangements
- F04C2270/04—Force
- F04C2270/042—Force radial
- F04C2270/0421—Controlled or regulated
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T29/00—Metal working
- Y10T29/49—Method of mechanical manufacture
- Y10T29/49799—Providing transitory integral holding or handling portion
Definitions
- the present invention relates to a medical device manufacturing method and a medical device.
- Patent Document 1 describes a catheter in which a wire lumen (sublumen) is provided around a main lumen (main lumen), and a push / pull wire is inserted inside the sublumen. In this catheter, the distal end of the catheter is bent by operating the push / pull wire.
- a step of supplying a resin material around the core wire, and molding a hollow tube in which the core wire is inserted A step of disposing a hollow tube in which the core wire is inserted, on the outer peripheral side of the main lumen forming region of the tubular main body made of resin; Extending the core wire inside the hollow tube to reduce the diameter, separating the hollow tube and the core wire, and then removing the core wire from the inside of the hollow tube to form a sublumen; ,
- a method for manufacturing a medical device including a step of inserting an operation line into the hollow tube.
- the resin material is supplied around the core wire, and the hollow tube in which the core wire is inserted is formed. Therefore, the core wire and the inside of the hollow tube are in close contact with each other. After that, a hollow tube having a core wire inserted therein is disposed on the outer peripheral side of the main lumen forming region of the resin tubular main body. Since the core wire is inserted in close contact with the inside of the hollow tube, deformation of the shape of the hollow tube is suppressed in the catheter manufacturing process. Moreover, when removing the core wire from the hollow tube, the core wire can be easily removed by removing the hollow tube and the core wire by extending and reducing the diameter of the core wire. . Moreover, according to this invention, the medical device manufactured with the manufacturing method mentioned above can be provided.
- a tubular main body having a main lumen formed therein, and a hollow tube disposed on the outer peripheral side of the main lumen and defining a sub-lumen;
- An operation line is loosely inserted in the hollow tube, and a plurality of convex portions or a plurality of concave portions extending in the longitudinal direction of the hollow tube are formed on the inner surface of the hollow tube, The plurality of convex portions or the plurality of concave portions are spaced apart along the longitudinal direction of the hollow tube, By operating the proximal end of the operation line, it is possible to provide a medical device in which the distal end of the tubular main body is bent.
- Such a medical device can be manufactured by the manufacturing method described above.
- a plurality of convex portions or a plurality of concave portions extending in the longitudinal direction of the hollow tube are formed on the inner surface of the hollow tube. Since the plurality of convex portions or the plurality of concave portions are spaced from each other in the longitudinal direction of the hollow tube, it is possible to reduce the contact area between the inner surface of the hollow tube and the operation line. Thereby, a medical device with favorable operability can be provided.
- a method for manufacturing a medical device and a medical device capable of forming a sub-lumen having a desired shape are provided.
- (a) is a side view which shows the whole before bending a catheter
- (b) is a tip by operating a slider.
- (C) is a side view showing a state where the tip is bent upward with a larger curvature than (b) by operating the slider. It is a side view which shows the state which operated the slider and bent the front-end
- (e) is a side view which shows the state which operated the slider and bent the front-end
- (A) is a perspective view which shows a core wire
- (b) is sectional drawing along the longitudinal direction of a core wire and a hollow tube. It is sectional drawing which shows the manufacturing process of a catheter. It is sectional drawing which shows the manufacturing process of a catheter.
- (A) (b) is sectional drawing orthogonal to the longitudinal direction of a hollow tube, and shows an operation line and a hollow tube. It is sectional drawing orthogonal to the longitudinal direction of a hollow tube, and shows an operation line and a hollow tube.
- FIGS. 1, 2, and 4 the outline
- 1 is a cross-sectional view taken along the longitudinal direction of the catheter 100
- FIG. 2 is a cross-sectional view taken along the II-II direction of FIG.
- illustration of the reinforcing layer 30 is omitted.
- the catheter 100 of the present embodiment is a hollow main body (sheath) 10 in which a main lumen 20 is formed, and a hollow that is disposed on the outer peripheral side of the main lumen 20 and defines a sub-lumen 80 (80a, 80b).
- Operation lines 70 (70a, 70b) are loosely inserted in the hollow tubes 82 (82a, 82b).
- a plurality of convex portions 822 or a plurality of concave portions 821 extending in the longitudinal direction of the hollow tube 82 and spaced apart are formed on the inner surface of the hollow tube 82 (see FIG. 4).
- the catheter 100 includes a coat body 50 and an operation unit 60 (see FIG. 6) in addition to a tubular body having a tubular body unit 10 and an operation line 70.
- the tubular body includes a sheath (tubular body) 10 including an inner layer 11 having a main lumen therein and an outer layer 12 covering the inner layer 11, a reinforcing layer 30, a hollow tube 82, and a marker 40.
- a distal end DE the distal ends of the sheath 10 and the catheter 100 are referred to as a distal end DE, but the rear end of the sheath 10 is referred to as a proximal end PE, and the rear end of the catheter 100 is referred to as a proximal end CE.
- the inner layer 11 is a hollow tubular layer, and a main lumen 20 extending along the longitudinal direction of the catheter 100 is formed therein.
- a fluorine-based thermoplastic polymer material can be used for the inner layer 11. More specifically, any one or more of polytetrafluoroethylene (PTFE), polyvinylidene fluoride (PVDF), perfluoroalkoxy fluororesin (PFA), and the like can be used.
- PTFE polytetrafluoroethylene
- PVDF polyvinylidene fluoride
- PFA perfluoroalkoxy fluororesin
- the main lumen 20 has a circular cross section perpendicular to the longitudinal direction of the catheter 100.
- the outer layer 12 is a resin tubular body that covers the inner layer 11.
- the outer layer 12 is thicker than the inner layer 11 and constitutes the main thickness of the sheath 10.
- a thermoplastic polymer is widely used for the outer layer 12. Examples include polyimide (PI), polyamideimide (PAI), polyethylene terephthalate (PET), polyethylene (PE), polyamide (PA), nylon elastomer, polyurethane (PU), ethylene-vinyl acetate resin (EVA), poly Any one or more of vinyl chloride (PVC) and polypropylene (PP) can be used.
- the reinforcing layer 30 surrounds the inner layer 11 and is included in the outer layer 12.
- This reinforcing layer 30 is a coil 31.
- the wire material constituting the reinforcing layer 30 in addition to fine metal wires such as stainless steel (SUS) and nickel titanium alloy, fine fiber wires such as PI, PAI, and PET can be used.
- the cross-sectional shape of the wire material is not particularly limited, and may be a round wire or a flat wire.
- the sub-lumen 80 through which the operation lines 70 are inserted is formed inside the outer layer 12 and outside the reinforcing layer 30.
- the operation line 70 is loosely inserted in the sub-lumen 80 and extends along the longitudinal direction of the sub-lumen 80.
- the operation line 70 may be comprised by one line, as shown in FIG. 3, it is preferable that it is the twist line comprised by twisting together the several thin wire 72.
- the operation line 70 is composed of a single line, the cross section perpendicular to the longitudinal direction has a circular shape.
- the operation line 70 is composed of a stranded wire, the cross section orthogonal to the longitudinal direction of the thin wire 72 constituting the operation line 70 has a circular shape.
- the circular shape of the cross section is not limited to a perfect circle.
- the thin wire 72 is arranged so that each thin wire 72 constituting the outline of the operation wire 70 is inscribed in one circle R in a cross section orthogonal to the longitudinal direction.
- the number of fine wires constituting one stranded wire is not particularly limited, but is preferably 3 or more.
- a suitable example of the number of thin wires is three or seven.
- the number of fine lines is 3, the three fine lines are arranged point-symmetrically in the cross section.
- the seven fine lines are arranged point-symmetrically in a honeycomb shape in the cross section.
- the hollow tubes 82 (82 a and 82 b) are embedded in the outer layer 12 and are arranged around the main lumen 20 so that the longitudinal direction thereof is along the longitudinal direction of the main lumen 20. ing.
- the hollow tube 82 defines the sub-lumen 80.
- the hollow tube 82 that defines the sublumen 80 is provided along the longitudinal direction of the catheter 100, and although not shown, the proximal end PE side of the sheath 10 is open. The distal end side of the sheath 10 of the hollow tube 82 is closed by the marker 40.
- the hollow tube 82 is disposed outside the reinforcing layer 30, and the inner side of the reinforcing layer 30, that is, the main lumen 20 protects the operation line 70 (70 a, 70 b) disposed inside the hollow tube 82.
- a plurality of hollow tubes 82 are provided. Specifically, a plurality of hollow tubes 82 are arranged on the same circumference so as to surround the main lumen 20. In the present embodiment, four hollow tubes 82 are arranged at equal intervals.
- the operation line 70 is arrange
- the operation line 70 is not disposed inside the other pair of hollow tubes 82 facing each other across the center of the main lumen 20.
- the number of the hollow tubes 82 and the sub-lumens 80 is not limited to four, and can be appropriately selected as necessary.
- FIG. 4 shows a cross-sectional view in a direction orthogonal to the longitudinal direction of the hollow tube 82.
- FIG. 5 shows a cross-sectional view along the longitudinal direction of the hollow tube 82.
- 4A is a sectional view taken along the line IV-a-IV-a in FIG. 5
- FIG. 4B is a sectional view taken along the line IV-b-IV-b in FIG.
- the hollow tube 82 has a circular outer shape in a cross section orthogonal to the longitudinal direction.
- the sub-lumen 80 inside the hollow tube 82 also has a substantially circular cross-sectional shape perpendicular to the longitudinal direction of the catheter 100.
- a plurality of concave portions 821 and a plurality of convex portions 822 are formed on the inner surface of the hollow tube 82.
- the concave portion 821 and the convex portion 822 each extend along the longitudinal direction of the hollow tube 82.
- one recess 821 is not formed over the entire length in the longitudinal direction of the hollow tube 82, but a plurality of recesses 821 are spaced apart along the longitudinal direction of the hollow tube.
- the plurality of recesses 821 have at least one of length (length along the longitudinal direction of the hollow tube 82), depth, width (length in the direction perpendicular to the length and depth), and cross-sectional shape. It is preferable that one of them is different. As a result, even if the operation line 70 fits into the plurality of recesses 821, a difference occurs in the degree of the fit, so that the operation line 70 can be easily removed from the recess 821. Does not interfere with the operability. However, a recess 821 having the same shape and size may be formed.
- the cross-sectional shape of the concave portion 821 orthogonal to the longitudinal direction of the hollow tube is not particularly limited, but may be, for example, a V-shaped groove shape or a U-shaped groove shape.
- each recess 821 is preferably smaller than the diameter of the operation line 70.
- the width of the recess 821 is preferably smaller than the diameter of the fine wires 72. By doing so, the operation line 70 is prevented from entering the recess 821.
- the depth of the recess 821 can be 0.5 to 3 ⁇ m, and the width can be 0.5 to 3 ⁇ m.
- the depth and width of the recess 821 can be about 5 to 10% of the thickness of the hollow tube 82.
- the length of the recess 821 is not particularly limited, but is preferably longer than the width, for example, 1 to 100 ⁇ m.
- a plurality of convex portions 822 are spaced apart along the longitudinal direction of the hollow tube 82. It is not a structure in which one convex portion extends over the entire length of the hollow tube 82 in the longitudinal direction. Furthermore, although the recessed part 821 and the convex part 822 are adjacent along the longitudinal direction of the hollow tube 82, the recessed part 821 and the convex part 822 are also spaced apart. In the cross section orthogonal to the longitudinal direction of the hollow tube 82, the curvature radius of the convex portion 822 is smaller than the curvature radius of the operation line 70. Thereby, the contact area of the operation line 70 and the inner surface of the hollow tube 82 can be reliably reduced.
- the radius of curvature of the operation line 70 is the radius of curvature of the round line in a cross section orthogonal to the longitudinal direction when the operation line is composed of one round line.
- the curvature radius of the operation line 70 is a curvature radius in a cross section orthogonal to the longitudinal direction of the thin wire 72 constituting the operation line 70.
- the operation wire 70 when the operation wire 70 is a stranded wire formed by twisting a plurality of thin wires 72, it constitutes a circumscribed circle R of the stranded wire and an outer peripheral portion of the stranded wire, It is preferable that the height of the convex portion 822 and the width of the convex portion 822 are smaller than the diameter of the inscribed circle R2 that is in contact with two adjacent thin wires. Thereby, it can prevent that the convex part 822 gets stuck between the fine wires 72 of a strand wire.
- the plurality of convex portions 822 have at least a length (a length along the longitudinal direction of the hollow tube 82), a height, a width (a length in a direction perpendicular to the length and the height), and a cross-sectional shape. It is preferable that any one is different. However, the convex part 822 of the same shape and size may be formed.
- the height of the convex portion 822 can be 0.5 to 3 ⁇ m
- the width can be 0.5 to 3 ⁇ m.
- the depth and width of the convex portion 822 can be about 5 to 10% of the thickness of the hollow tube 82.
- the length of the convex portion 822 is not particularly limited, but is preferably longer than the width, for example, 1 to 100 ⁇ m.
- corrugation is formed and the outer peripheral surface may be roughened.
- the surface roughness (Ra) of the outer peripheral surface of the hollow tube 82 is preferably 0.1 to 0.3 ⁇ m.
- the fine irregularities on the outer peripheral surface of the hollow tube 82 are preferably embedded by the outer layer 12.
- the hollow tube 82 is made of a material different from that of the outer layer 12. By doing in this way, the hollow tube 82 can be comprised with the material whose bending rigidity and tensile elasticity modulus are higher than the outer layer 12.
- Examples of the material constituting the hollow tube 82 include materials such as polytetrafluoroethylene (PTFE), perfluoroalkoxy fluororesin (PFA), and tetrafluoroethylene / hexafluoropropylene copolymer (FEP). . It is preferable that any one or more of these materials are the main component. These materials can improve the slidability of the operation line and have high heat resistance.
- PTFE polytetrafluoroethylene
- PFA perfluoroalkoxy fluororesin
- FEP tetrafluoroethylene / hexafluoropropylene copolymer
- the distal end portion 71 (71 a, 71 b) of the operation line 70 (70 a, 70 b) is fixed to the marker 40 at the distal end DE of the sheath 10.
- the tip portions 71 (71a, 71b) of 70a, 70b) are fixed to the distal end DE.
- the operation line 70 is slidably inserted through the sub-lumen 80 (80a, 80b).
- the distal end 15 of the catheter 100 is bent by pulling the proximal end of each operation line 70 (70a, 70b) (see FIG. 6).
- the curvature and direction of the bent distal end portion 15 change in a plurality of ways depending on selection of the operation line 70 (70a, 70b) to be pulled.
- a specific material of the operation line 70 for example, a high material composed of at least one of polyether ether ketone (PEEK), polyphenylene sulfide (PPS), polybutylene terephthalate (PBT), PI or PTFE, and the like.
- PEEK polyether ether ketone
- PPS polyphenylene sulfide
- PBT polybutylene terephthalate
- PI or PTFE PI or PTFE
- a molecular fiber, or a metal wire made of any one or more of SUS, a corrosion-resistant coated steel wire, titanium, or a titanium alloy can be used.
- PVDF high density polyethylene
- HDPE high density polyethylene
- polyester or the like can also be used.
- the catheter 100 includes an operation unit 60.
- the operation unit 60 is provided at the proximal end portion 17 of the catheter 100.
- a portion between the distal end portion 15 and the proximal end portion 17 is referred to as an intermediate portion 16.
- the operation unit 60 includes a shaft portion 61 extending in the longitudinal direction of the catheter 100, a slider 64 (64a, 64b) that moves forward and backward in the longitudinal direction of the catheter 100 with respect to the shaft portion 61, and a handle portion that rotates the shaft portion 61 about its axis. 62 and a gripping portion 63 through which the sheath 10 is rotatably inserted. Further, the proximal end portion 17 of the sheath 10 is fixed to the shaft portion 61. Moreover, the handle
- the operation unit 60 of the present embodiment rotates the distal end portion 15 of the sheath 10.
- a handle portion 62 as a rotation operation portion for torque-rotating the sheath 10 and a slider 64 as a bending operation portion for bending the sheath 10 are integrally provided.
- the present invention is not limited to this, and the handle portion 62 and the slider 64 may be provided separately.
- the proximal end of the first operation line 70 a protrudes from the proximal end portion 17 of the sheath 10 to the proximal end side, and is connected to the slider 64 a of the operation portion 60.
- the proximal end of the second operation line 70 b is also connected to the slider 64 b of the operation unit 60. Then, by sliding the slider 64a and the slider 64b individually to the proximal end side with respect to the shaft portion 61, the first operation line 70a or the second operation line 70b connected thereto is pulled and the distal end of the sheath 10 is pulled. A tensile force is applied to the end portion 15. As a result, the distal end portion 15 bends toward the pulled operation line 70.
- a marker 40 is provided at the distal end of the sheath 10.
- the marker 40 is a ring-shaped member made of a material that does not transmit radiation such as X-rays. Specifically, a metal material such as platinum can be used for the marker 40.
- the marker 40 of this embodiment is provided around the main lumen 20 and inside the outer layer 12.
- the coat layer 50 constitutes the outermost layer of the catheter 100 and is a hydrophilic layer.
- a hydrophilic material such as polyvinyl alcohol (PVA) or polyvinyl pyrrolidone can be used.
- the radius of the main lumen 20 is about 200 to 300 ⁇ m
- the thickness of the inner layer 11 is about 10 to 30 ⁇ m
- the thickness of the outer layer 12 is about 50 to 150 ⁇ m
- the outer diameter (diameter) of the reinforcing layer 30 is about 500 ⁇ m to 860 ⁇ m.
- the inner diameter (diameter) of the layer 30 can be about 420 ⁇ m to 660 ⁇ m.
- the radius from the axial center of the catheter 100 to the center of the sublumen 80 can be about 300 to 350 ⁇ m
- the inner diameter of the sublumen 80 can be about 40 to 100 ⁇ m
- the thickness of the operation line 70 can be about 30 to 60 ⁇ m.
- the wall thickness of the hollow tube can be about 3 to 15 ⁇ m.
- the outermost diameter (radius) of the catheter 100 can be about 350 to 490 ⁇ m.
- the outer diameter of the catheter 100 of this embodiment is less than 1 mm in diameter, and can be inserted into blood vessels such as the celiac artery. Further, the catheter 100 according to the present embodiment is operated freely by pulling the operation line 70 (70a, 70b), so that the catheter 100 can be advanced in a desired direction even in a branching blood vessel, for example. Is possible.
- the distal end portion 15 of the catheter 100 refers to a predetermined length region including the distal end DE of the catheter 100.
- the proximal end portion 17 of the catheter 100 refers to a predetermined length region including the proximal end CE of the catheter 100.
- the intermediate portion 16 refers to a predetermined length region between the distal end portion 15 and the proximal end portion 17. The bending of the catheter 100 means that a part or all of the catheter 100 is bent or bent.
- the operation line 70 to be pulled is only the first operation line 70a, only the second operation line 70b, or whether the two operation lines 70a and 70b are pulled simultaneously.
- the curvature of the bent distal end portion 15 changes in a plurality of ways. Thereby, the catheter 100 can be freely entered into a body cavity that branches at various angles.
- the catheter 100 of the present embodiment can individually pull the proximal ends of the plurality of operation lines 70 (the first operation line 70a or the second operation line 70b).
- the bending direction can be changed by the operating line 70 to be pulled. Specifically, when the first operation line 70a is pulled as shown in FIGS. 6B and 6C, it bends to the side where the first operation line 70a is provided, as shown in FIGS. 6D and 6E. When the second operation line 70b is pulled, the second operation line 70b is bent. Further, the curvature of curvature (the radius of curvature) can be changed by adjusting the pulling amount of each operation line 70 (70a, 70b). Specifically, as shown in FIGS.
- a method for manufacturing the catheter 100 of the present embodiment will be described with reference to FIGS. First, an outline of a method for manufacturing the catheter 100 will be described.
- a liquid resin material is supplied around the core wire 90 to form the hollow tube 82 into which the core wire 90 is inserted, and the tubular main body 10 made of resin.
- the outer layer 12 is extruded.
- a material containing resin constituting the outer layer 12 is extruded around a mandrel (core material) (not shown).
- the gas is so formed that a long hollow portion (hole) along the longitudinal direction is formed at each position where the sub-lumen 80 is formed by the hollow tube 82 being embedded later.
- the hollow outer layer 12 can be formed by pulling out the mandrel.
- the hollow tube 82 is formed.
- a core wire 90 is prepared.
- a material containing a resin constituting the hollow tube 82 is melt-extruded around the core wire 90 (a liquid resin material is supplied around the core wire 90).
- the periphery of the core wire 90 is covered with the resin material, and the hollow tube 82 whose inner surface is in close contact with the core wire 90 is obtained.
- the material containing the resin constituting the hollow tube 82 is melted and extruded around the core wire 90.
- the present invention is not limited to this, and the hollow tube 82 may be manufactured by dispersion molding.
- an aqueous solution (liquid resin material) containing a resin material constituting the hollow tube 82 is prepared. Then, the core wire 90 is immersed in this aqueous solution and allowed to pass through the aqueous solution. As a result, a film made of the resin material is formed around the core member 90. Thereafter, the coating is dried and fired. Even with such a method, the hollow tube 82 whose inner surface is in close contact with the core wire 90 can be obtained.
- the cross section orthogonal to the longitudinal direction of the core wire 90 is circular, and the hollow tube also has a circular ring shape with a circular cross section orthogonal to the longitudinal direction.
- a plurality of convex portions 901 and concave portions 902 extending along the longitudinal direction are formed on the outer peripheral surface of the core wire 90.
- the convex portions 901 are spaced apart along the longitudinal direction of the core wire 90.
- the recesses 902 are also spaced apart along the longitudinal direction of the core wire 90.
- the convex portions 901 and the concave portions 902 correspond to the concave portions 821 and the convex portions 822 of the hollow tube 82 described above, and the shapes of the convex portions 901 and the concave portions 902 on the outer peripheral surface of the core wire 90 are transferred to the hollow tube 82. Thus, the above-described concave portion 821 and convex portion 822 are formed.
- the material of the core wire 90 examples include metal materials such as SUS.
- the method of cutting the outer peripheral surface of the core wire 90 and forming the convex part 901 and the recessed part 902 is mention
- dye in which the convex part corresponding to the convex part 901 and the recessed part 902 and the recessed part were used is used, and the wire used as the raw material of the core wire 90 is passed through this die
- the core wire 90 may be manufactured.
- the outer peripheral surface of the hollow tube 82 is surface-treated.
- the outer peripheral surface of the hollow tube 82 is subjected to plasma treatment or sodium treatment, and the outer peripheral surface of the hollow tube 82 is modified to improve the adhesion with the outer layer 12.
- the inner layer 11 is also prepared by extrusion molding.
- a material containing a resin constituting the inner layer 11 may be extruded around a mandrel (core material) M shown in FIG. Thereafter, the coil 31 is placed around the inner layer 11 with the core material M. Therefore, at this stage, the mandrel M is still inserted in the inner layer 11.
- the mandrel M can be made of the same material as the core wire 90.
- the outer layer 12 is covered around the coil 31 in a state where the coil 31 is covered around the inner layer 11.
- the hollow tube 82 containing the core wire 90 is inserted into the hollow portion of the outer layer 12.
- a heat shrinkable tube 91 is placed around the outer layer 12.
- the coil 31 is omitted.
- the sub-lumen in the hollow tube 82 has a circular cross section perpendicular to the longitudinal direction.
- the heat shrinkable tube 91 is contracted by heating, and the outer layer 12, the coil 31, the inner layer 11, and the hollow tube 82 are pressurized from the outside in the radial direction of the inner layer 11. Further, the outer layer 12 is melted by the heating.
- the heating temperature is higher than the melting temperature of the outer layer 12 and lower than the melting temperature of the inner layer 11 and the hollow tube 82.
- the outer layer 12 and the inner layer 11 are joined by welding.
- the material constituting the outer layer 12 encloses the coil 31 and the outer layer 12 is impregnated with the coil.
- the outer layer 12 and the hollow tube 82 are joined by welding.
- the outer peripheral surface of the outer layer 12 is substantially circular by tightening the outer peripheral surface of the outer layer 12 with the heat shrinkable tube 91.
- the hollow tube 82 is pressurized in this step, but since the core wire 90 that is in close contact with the inner surface of the hollow tube 82 is inserted into the hollow tube 82, the hollow tube 82 is crushed. Is prevented.
- both ends of the core wire 90 are fixed and tension (first tension) is applied to the core wire 90. It is preferable to keep it.
- the tension applied to the core wire 90 is set to such a force that the core wire 90 does not expand.
- the mandrel M may be tensioned or may not be tensioned. For example, as shown in FIG.
- a pair of jigs 95 and 96 are prepared.
- the core wire 90 is fixed to the mandrel M with the first tension applied to the core wire 90. Thereby, the position of the core wire 90 with respect to the mandrel M will be fixed. Specifically, one end of the core wire 90 and one end of the mandrel M (the end on the same side as the one end of the core wire 90) are fixed to the jig 95. Further, the other end of the core wire 90 and the other end of the mandrel M are fixed to the jig 96.
- the heat shrinkable tube 91 is cut from the outer layer 12 by cutting the heat shrinkable tube 91 and tearing the heat shrinkable tube 91.
- the core wire 90 is removed from the hollow tube 82.
- the mandrel M may be removed at the same time.
- a tension larger than the above-described first tension is applied to the core wire 90 and the mandrel M, and the core wire 90 and the mandrel M are expanded and reduced in diameter.
- the core wire 90 peels from the inner surface of the hollow tube 82.
- the mandrel M peels from the inner layer 11.
- the core wire 90 is taken out from the inside of the hollow tube 82 and the mandrel M is taken out from the inner side of the inner layer 11.
- the core wire 90 and the mandrel M may be extracted at the same time, or may be extracted separately.
- a hollow serving as the main lumen 20 is formed in the center of the inner layer 11.
- the operation line 70 is inserted into the sub-lumen inside the hollow tube 82.
- the operation line 70 is loosely inserted into the sub-lumen of the hollow tube 82.
- a marker 40 that is an annular metal member is prepared.
- the tip of the operation line 70 is fixed to the marker 40 and the marker 40 is fixed to the periphery of the tip of the outer layer 12 by caulking.
- a member (not shown) serving as an inlet for a chemical solution or the like is connected to the proximal end portion of the main lumen 20.
- the base end portion of the operation line 70 is connected to the separately created operation unit.
- the coat layer 50 is formed. From the above, the catheter 100 can be obtained.
- the hollow tube 82 is formed by melting and extruding a resin material around the core wire 90 and bringing the resin material into direct contact with the core wire 90.
- the inner surface of the hollow tube 82 and the core wire 90 are in close contact with each other. Since the core wire is inserted into the hollow tube 82 in a close contact state, and the hollow tube 82 is reinforced from the inside, the shape of the hollow tube 82 is deformed in the manufacturing process of the catheter 100. Is suppressed.
- the heat shrinkable tube 91 is contracted so that the outer layer 12, the hollow tube 82, and the like are directed in the radial direction of the outer layer 12. Pressurized from the outside. Since the core wire 90 is inserted into the hollow tube 82 in a close contact state, and the hollow tube 82 is reinforced from the inside, the shape of the hollow tube 82 is deformed in this pressurizing step. Can be prevented. Thereby, the hollow tube 82 in which the sub-lumen 80 having a desired shape is formed can be obtained.
- the core wire 90 when the core wire 90 is removed from the hollow tube 82, the core wire 90 may be stretched and reduced in diameter, and the hollow tube 82 and the core wire 90 may be peeled off. It can be easily removed.
- the outer layer 12, the coil 31, the inner layer 11, and the hollow tube 82 are pressurized with the heat shrinkable tube 91 in a state where tension is applied to the core wire 90. It is difficult to heat-shrink the heat-shrinkable tube 91 uniformly along the longitudinal direction of the heat-shrinkable tube 91, and a portion having a strong contraction force and a weak portion are locally generated. In the region where the pressure applied to the hollow tube 82 is high, in the region where the pressure applied to the hollow tube 82 is high, the hollow tube 82 approaches the main lumen 20 and the pressure applied to the hollow tube 82 is low. The hollow tube 82 may be separated from the main lumen 20.
- each end of the core wire 90 is fixed to the mandrel M via the jigs 95 and 96. Therefore, by pulling the pair of jigs 95 and 96 apart, the mandrel M inside the inner layer 11 and the core wire 90 can be simultaneously expanded to reduce the diameter. Thereby, the number of manufacturing steps can be reduced.
- the hollow tube 82 is formed by melting and extruding a resin material around the core wire 90 and bringing the resin material into direct contact with the core wire 90. Therefore, the convex portion 901 and the concave portion 902 formed on the outer peripheral surface of the core wire 90 can be transferred to the inner surface of the hollow tube 82, and the hollow tube 82 in which the concave portion 821 and the convex portion 822 are formed on the inner surface is easily manufactured. Can do.
- the diameter and shape of the operation line 70 with respect to the recess 821 and the protrusion 822, the contact area between the inner surface of the hollow tube 82 and the operation line 70 is reduced, and the operability of the operation line 70 is improved. It becomes possible.
- the plurality of recesses 821 are spaced apart along the longitudinal direction of the hollow tube 82.
- the operation line 70 is pulled and operated, a region between the recesses 821 in the inner surface of the hollow tube 82 and the operation line 70 are in contact with each other, and the operation line 70 is less likely to contact the bottom of the recess 821. Thereby, the contact area of the inner surface of the hollow tube 82 and the operation line 70 can be reduced.
- by arranging the plurality of recesses 821 apart along the longitudinal direction of the hollow tube 82 even if there is a recess 821 having a very wide width among the plurality of recesses 821, one recess It is possible to prevent the entire length of the operation line 70 from getting stuck. Therefore, it is possible to suppress the operability of the operation line 70 from being hindered.
- the operation line 70 comes into contact with the convex portions 822 adjacent in the longitudinal direction, The contact area between the operation line 70 and the inner surface of the hollow tube 82 can be reduced.
- the present invention is not limited to the above-described embodiment, and modifications, improvements, and the like within the scope that can achieve the object of the present invention are included in the present invention.
- the manufacturing method is not limited thereto.
- the resin material constituting the outer layer 12 is melt-extruded so that the core wire 90 is disposed on the outer peripheral side of the main lumen forming region of the outer layer 12. You may arrange
- the mandrel M and the core wire 90 are simultaneously stretched to reduce the diameter.
- the present invention is not limited to this, and for example, the core wire 90 is stretched to reduce the diameter and removed from the hollow tube 82. After that, the mandrel M may be stretched to have a reduced diameter and may be removed from the inner layer 11.
- the recessed part 821 and the convex part 822 were formed in the inner surface of the hollow tube 82, only the recessed part 821 or only the convex part 822 may be formed.
- the operation line 70 showed the example which is a strand wire, as shown to Fig.10 (a), (b), the operation line 70 may be a round line.
- the convex part 822 showed the example where the front end surface was curved, the cross section orthogonal to the longitudinal direction of a hollow tube is a triangle, for example, like FIG. It may be a shape, and the tip of the convex part 822 may have an acute angle.
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Abstract
Description
樹脂製の管状の本体部のメインルーメン形成領域の外周側に、前記芯線が内部に挿入された中空管を配置する工程と、
前記中空管内部の前記芯線を伸張させて縮径させて、前記中空管と前記芯線とを剥離した後、前記中空管内部から前記芯線を抜去して、サブルーメンを形成する工程と、
前記中空管内部に操作線を挿入する工程とを含む医療機器の製造方法が提供される。
また、中空管から芯線を除去する際には、芯線を伸張させて縮径させて、中空管と芯線とを剥離すればよいので、芯線を中空管から容易に除去することができる。
また、本発明によれば、上述した製造方法により製造された医療機器を提供できる。
内部にメインルーメンが形成された管状の本体部と、前記メインルーメンの外周側に配置され、サブルーメンを区画する中空管とを備え、
前記中空管内には、操作線が遊挿されており、前記中空管内面には、前記中空管の長手方向に延在する複数の凸部あるいは複数の凹部が形成され、
前記複数の凸部または複数の凹部は、前記中空管の長手方向にそって離間配置されており、
前記操作線の近位端を操作することで、管状の本体部の遠位端部が屈曲する医療機器を提供できる。
中空管内面には、中空管の長手方向に延在する複数の凸部あるいは複数の凹部が形成されている。この複数の凸部あるいは複数の凹部は、中空管の長手方向に離間配置されているため、中空管内面と操作線との接触面積の低減を図ることが可能となる。
これにより、操作性が良好な医療機器を提供することができる。
〔構成例〕
図1、2、4を参照して、本実施形態の医療機器であるカテーテル100の概要について説明する。図1は、カテーテル100の長手方向に沿った断面図であり、図2は、図1のII-II方向の断面図である。なお、図2においては、補強層30の図示を省略している。
本実施形態のカテーテル100は、内部にメインルーメン20が形成された管状の本体部(シース)10と、メインルーメン20の外周側に配置され、サブルーメン80(80a、80b)を区画する中空管82(82a、82b)とを備える。
中空管82(82a、82b)内には、操作線70(70a、70b)が遊挿されている。中空管82内面には、前記中空管82の長手方向に延在し、離間した複数の凸部822あるいは複数の凹部821が形成されている(図4参照)。操作線70(70a、70b)の近位端を操作することで、シース10の遠位端部が屈曲する構造となっている。
カテーテル100は、管状の本体部10を有する管状本体、操作線70に加えて、コート層50、操作部60(図6参照)を備える。
なお、以下、シース10とカテーテル100の先端は遠位端DEとよぶが、シース10の後端は近位端PEとよび、カテーテル100の後端は近位端CEとよぶ。
メインルーメン20は、カテーテル100の長手方向と直交する断面形状が円形形状となっている。
外層12には熱可塑性ポリマーが広く用いられる。一例として、ポリイミド(PI)、ポリアミドイミド(PAI)、ポリエチレンテレフタレート(PET)のほか、ポリエチレン(PE)、ポリアミド(PA)、ナイロンエラストマー、ポリウレタン(PU)、エチレン-酢酸ビニル樹脂(EVA)、ポリ塩化ビニル(PVC)またはポリプロピレン(PP)などのいずれか1種以上を用いることができる。
なお、本実施形態のカテーテル100においては、操作線70がそれぞれ挿通されたサブルーメン80は、外層12の内部であって、補強層30の外側に形成されている。
操作線70は、1本の線で構成されていてもよいが、図3に示すように、複数本の細線72を撚りあわせて構成された撚り線であることが好ましい。操作線70が、1本の線で構成される場合、その長手方向に直交する断面は円形形状である。一方で、操作線70が撚り線で構成される場合、操作線70を構成する細線72の長手方向に直交する断面は円形形状である。
ここで、断面が円形形状であるとは、真円に限られるものではない。
操作線70が撚り線で構成される場合、長手方向と直交する断面において、操作線70の外郭を構成する各細線72がひとつの円Rに内接するように、細線72が配置された構造であることが好ましい。
ここで、一本の撚り線を構成する細線の本数は特に限定されないが、3本以上であることが好ましい。細線の本数の好適な例は、3本又は7本である。細線の本数が3本の場合、横断面において3本の細線が点対称に配置される。細線の本数が7本の場合、横断面において7本の細線が点対称にハニカム状に配置される。
中空管82は、サブルーメン80を区画するものである。サブルーメン80を区画する中空管82はカテーテル100の長手方向に沿って設けられ、図示はしないが、シース10の近位端PE側が開口している。また、中空管82のシース10の遠位端側は、マーカ40により閉鎖されている。
本実施形態では、図2に示すように、中空管82は、複数設けられている。具体的には、メインルーメン20を取り囲むように、同一の円周上に複数の中空管82が配置されている。本実施形態では、4つの中空管82が等間隔で配置されている。そして、メインルーメン20の中心を挟んで対向する一対の中空管82内部に操作線70が配置されている。また、メインルーメン20の中心を挟んで対向する他の一対の中空管82内部には、操作線70は配置されていない。
なお、中空管82やサブルーメン80の個数は、4つに限られるものではなく、必要に応じて適宜選択することができる。
ここで、1本の凹部821が中空管82の長手方向全長にわたって形成されているのではなく、複数の凹部821が、中空管の長手方向に沿って離間配置されている。
ただし、同一形状、大きさの凹部821が形成されていてもよい。
中空管の長手方向と直交する凹部821の断面形状は、特に限定されないが、たとえばV字溝状あるいはU字溝状とすることができる。
このようにすることで、操作線70が凹部821内部に入り込んでしまうことが防止される。
ここで、凹部821の深さは、0.5~3μm、幅は、0.5~3μmとすることができる。また、凹部821の深さや幅は、中空管82の肉厚の5~10%程度とすることができる。また、凹部821の長さは特に限定されないが、幅よりも長いことが好ましく、たとえば、1~100μmとすることができる。
中空管82の長手方向と直交する断面において、凸部822の曲率半径は、操作線70の曲率半径よりも小さい。これにより、操作線70と中空管82内面との接触面積を確実に低減できる。
ここで、操作線70の曲率半径とは、操作線が1本の丸線で構成される場合には、その長手方向に直交する断面における前記丸線の曲率半径である。一方で、操作線70が撚り線で構成される場合には、操作線70の曲率半径は、操作線70を構成する細線72の長手方向と直交する断面における曲率半径である。
さらには、図3に示すように、操作線70は、複数の細線72を撚りあわせることにより構成された撚り線である場合、撚り線の外接円Rと、撚り線の外周部を構成し、隣接する2本の細線とに接触する内接円R2の径よりも、凸部822の高さおよび凸部822の幅が小さいことが好ましい。これにより、凸部822が撚り線の細線72間にはまりこんでしまうことが防止できる。
ここで、凸部822の高さは、0.5~3μm、幅は、0.5~3μmとすることができる。また、凸部822の深さや幅は、中空管82の肉厚の5~10%程度とすることができる。また、凸部822の長さは特に限定されないが、幅よりも長いことが好ましく、たとえば、1~100μmとすることができる。
中空管82は、外層12とは異なる材料で構成されている。このようにすることで、中空管82を、外層12よりも曲げ剛性や、引張り弾性率が高い材料で構成することができる。たとえば、中空管82を構成する材料としては、ポリテトラフルオロエチレン(PTFE)、ペルフルオロアルコキシフッ素樹脂(PFA)、四フッ化エチレン・六フッ化プロピレン共重合体(FEP)等の材料が挙げられる。これらの材料のいずれか1種以上を主成分とすることが好ましい。これらの材料は、操作線の摺動性をよくでき、耐熱性も高い。
このような中空管82を使用することで、カテーテル100のねじり剛性を高め、シースをその長手方向を回転軸として、回転させた際に、シースが局所的にねじれてしまうことを防止できる。
次に、本実施形態のカテーテル100の動作例について、図6を参照して、説明する。まず、本実施形態のカテーテル100において、操作線70(第一操作線70aまたは第二操作線70b)の近位端を牽引すると、カテーテル100の遠位端部15に引張力が与えられて、当該操作線70(第一操作線70aまたは第二操作線70b)が挿通されたサブルーメン80(サブルーメン80aまたはサブルーメン80b)の側に向かって遠位端部15の一部または全部が屈曲する。一方、操作線70の近位端をカテーテル100に対して押し込んだ場合には、当該操作線70からカテーテル100の遠位端部15に対して押込力が実質的に与えられることはない。
次に、図7~図9を参照して、本実施形態のカテーテル100の製造方法について説明する。
はじめに、カテーテル100の製造方法の概要について説明する。
本実施形態のカテーテル100の製造方法は、芯線90の周囲に液状の樹脂材料を供給し、芯線90が内部に挿入された中空管82を成形する工程と、樹脂製の管状の本体部10のメインルーメン形成領域の外周側に、前記芯線90が内部に挿入された中空管82を配置する工程と、中空管82内部の前記芯線90を伸張させて縮径させて、中空管82と前記芯線90とを剥離した後、中空管82内部から前記芯線90を抜去して、サブルーメン80を形成する工程と、中空管82内部に操作線70を挿入する工程とを含む。
はじめに、外層12を押し出し成形しておく。外層12を構成する樹脂を含む材料を図示しないマンドレル(芯材)の周囲に押し出す。このとき、外層12において、後に中空管82が埋設されることによりサブルーメン80が形成される位置の各々に、長手方向に沿う長尺な中空部(孔)が形成されるように、ガス等の流体を吐出しながら押出成形する。
押出成形後、マンドレルを引き抜くことにより、中空形状の外層12を作成することができる。
なお、ここでは、芯線90の周囲に、中空管82を構成する樹脂を含む材料を溶融押し出しするとしたが、これに限らず、ディスパージョン成形で中空管82を製造してもよい。具体的には、中空管82を構成する樹脂材料を含む水溶液(液状の樹脂材料)を用意する。そして、芯線90をこの水溶液中に浸し、水溶液中を通過させる。これにより芯材90の周囲に樹脂材料で構成された被膜が形成される。その後、前記被膜を乾燥、焼成させる。このような方法でも、芯線90に、内面が密着した中空管82を得ることができる。
また、芯線90の外周面には、図7(b)に示すように、その長手方向に沿って延在する複数の凸部901および凹部902が形成されている。凸部901は、芯線90の長手方向に沿って離間配置されている。同様に、凹部902も、芯線90の長手方向に沿って離間配置されている。
この凸部901、凹部902は、前述した中空管82の凹部821、凸部822に対応するものであり、芯線90の外周面の凸部901、凹部902の形状が中空管82に転写されて前述した凹部821、凸部822が形成されることとなる。
次に、中空管82の外周面を表面処理する。たとえば、中空管82の外周面にプラズマ処理やナトリウム処理を行ない、中空管82の外周面の改質を行なって、外層12との密着性を向上させる。
その後、芯材M付きの内層11の周囲にコイル31を被せる。従って、この段階では、未だ、内層11内にはマンドレルMが挿通されたままである。
なお、マンドレルMは、芯線90と同じ材料で構成することができる。
次に、外層12の中空部分に対し、芯線90入りの中空管82を挿入する。
その後、図8に示すように、外層12の周囲に、熱収縮チューブ91を被せる。図8においては、コイル31を省略している。このとき、中空管82内のサブルーメンは、その長手方向と直交する断面が円形である。
次に、加熱により、熱収縮チューブ91を収縮させて、外層12、コイル31、内層11、中空管82を内層11の径方向に向かって外側から加圧する。また、前記加熱により、外層12を溶融させる。なお、加熱温度は、外層12の溶融温度よりも高く、内層11、中空管82の溶融温度よりも低い。この加熱により、外層12と内層11とが溶着により接合する。このとき、外層12を構成する材料が、コイル31を内包し、外層12にコイルが含浸されることとなる。また、外層12と中空管82とが溶着により接合する。
なお、この工程において、外層12の外周面が熱収縮チューブ91により締め付けられることにより、外層12の外周面はほぼ円形となる。
一方で、中空管82は、この工程において加圧されるが、中空管82内部には、中空管82内面に密着した芯線90が挿入されているので、中空管82が潰れてしまうことが防止される。
ここで、熱収縮チューブ91で、外層12、コイル31、内層11、中空管82を加圧する際、芯線90の両端部を固定して、芯線90に対し張力(第一の張力)をかけておくことが好ましい。このとき芯線90にかかる張力は、芯線90が伸張しない程度の力とする。なお、マンドレルMには張力はかかっていてもよく、また、張力がかかっていなくてもよい。
たとえば、図9に示すように、一対の治具95,96を用意する。芯線90に第一の張力をかけた状態で、芯線90をマンドレルMに固定する。これにより、マンドレルMに対する芯線90の位置が固定されることとなる。具体的には、芯線90の一方の端部およびマンドレルMの一方の端部(芯線90の一方の端部と同じ側の端部)を治具95に固定する。また、芯線90の他方の端部およびマンドレルMの他方の端部を治具96に固定する。
一対の治具95,96を離間するように引っ張ることで、芯線90およびマンドレルMに対し前述した第一の張力よりも大きな張力がかかり、芯線90およびマンドレルMが伸長し、縮径する。これにより、芯線90が中空管82の内面から剥離する。また、マンドレルMが内層11から剥離する。その後、芯線90を中空管82内部から取り出すとともに、マンドレルMを内層11の内側から抜き去る。芯線90とマンドレルMとは同時に抜き去ってもよく、また、別々に抜き去ってもよい。内層11の中心には、メインルーメン20となる中空が形成される。
次に、マーカ40に対する操作線70の先端部の固定と、外層12の先端部の周囲に対するマーカ40のかしめ固定と、を行う。
次に、コート層50を形成する。
以上より、カテーテル100を得ることができる。
本実施形態では、芯線90の周囲に樹脂材料を溶融押し出し、芯線90に直接樹脂材料を接触させて、中空管82を成形している。中空管82内面と芯線90とは密着した状態となる。中空管82内部には芯線が密着した状態で挿入されており、内部側から中空管82が補強されるので、カテーテル100の製造工程において、中空管82の形状が変形してしまうことが抑制される。
特に、本実施形態では、外層12の中空部分に対し、中空管82を挿入した後、熱収縮チューブ91を収縮させて、外層12、中空管82等を外層12の径方向に向かって外側から加圧している。中空管82内部には芯線90が密着した状態で挿入されており、内部側から中空管82が補強されるので、この加圧工程において、中空管82の形状が変形してしまうことを防止できる。
これにより、所望の形状のサブルーメン80が形成された中空管82を得ることができる。
しかしながら、本実施形態では、中空管82の内面が密着した芯線90の端部を固定して、芯線90に張力をかけておくことで、熱収縮チューブ91による中空管82への加圧にばらつきが生じても、芯線90のメインルーメン20に対する位置ずれが生じにくくなる。そのため、芯線90を被覆する中空管82のメインルーメン20に対する位置ずれを抑制することができる。
さらに、本実施形態では、芯線90の各端部を、各治具95,96を介してマンドレルMに固定している。そのため、一対の治具95,96を離間するように、引っ張ることで内層11内側のマンドレルMと、芯線90とを同時に伸張させて縮径させることができる。これにより、製造工程の工程数を削減できる。
凹部821、凸部822に対して、操作線70の径、形状を適宜選択することで、中空管82内面と操作線70との接触面積の低減を図り、操作線70の操作性を高めることが可能となる。
さらに、複数の凹部821を、中空管82の長手方向に沿って離間配置することで、たとえ、複数の凹部821のうち凹部821の幅が非常に広いものがあったとしても、一つの凹部に操作線70の全長がはまり込んでしまうことが防止できる。そのため、操作線70の操作性が阻害されてしまうことが抑制できる。
たとえば、前記実施形態では、外層12を成形した後、外層12の中空部に中空管82を挿入していたが、このような製造方法に限られるものではない。たとえば、芯線90入りの中空管82を、内層11の周囲に配置した後、外層12を構成する樹脂材料を溶融押し出しして、外層12のメインルーメン形成領域の外周側に、芯線90が内部に挿入された中空管82を配置してもよい。
また、前記実施形態では、操作線70を、撚り線である例を示したが、図10(a)、(b)に示すように、操作線70は丸線であってもよい。
さらに、前記実施形態では、凸部822は、その先端面が湾曲した形状である例を示したが、たとえば、図11のように凸部822は中空管の長手方向と直交する断面が三角形状であり、凸部822の先端部が鋭角であってもよい。
Claims (11)
- 芯線の周囲に樹脂材料を供給し、前記芯線が内部に挿入された中空管を成形する工程と、
樹脂製の管状の本体部のメインルーメン形成領域の外周側に、前記芯線が内部に挿入された中空管を配置する工程と、
前記中空管内部の前記芯線を伸張させて縮径させて、前記中空管と前記芯線とを剥離した後、前記中空管内部から前記芯線を抜去して、サブルーメンを形成する工程と、
前記中空管内部に操作線を挿入する工程とを含む医療機器の製造方法。 - 請求項1に記載の医療機器の製造方法において、
樹脂製の管状の本体部の前記メインルーメン形成領域の周囲に前記本体部の長手方向に沿って延在する孔が形成された、前記本体部を用意し、
樹脂製の管状の本体部のメインルーメン形成領域の外周側に、前記中空管を配置する前記工程では、前記孔内に、前記芯線が内部に挿入された前記中空管を挿入し、
前記中空管内部から前記芯線を抜去する前記工程の前段において、
前記本体部および中空管を前記本体部の径方向に向かって外部から加圧するとともに加熱して、前記本体部を成形する工程を含む医療機器の製造方法。 - 請求項1または2に記載の医療機器の製造方法において、
前記芯線の外周面には、前記芯線の長手方向に延在し、前記芯線の長手方向に離間配置された複数の凸部あるいは複数の凹部が形成されており、
前記中空管を成形する前記工程では、前記芯線の外周面に形成された前記凸部または凹部を前記中空管内面に転写する医療機器の製造方法。 - 請求項1乃至3のいずれかに記載の医療機器の製造方法において、
メインルーメン形成領域内にメイン芯線が挿入された前記管状の本体部を用意し、
樹脂製の管状の本体部のメインルーメン形成領域の外周側に、前記中空管を配置する前記工程では、前記メイン芯線が挿入された前記管状の本体部のメインルーメン形成領域の周囲に、前記中空管を配置し、
前記芯線に第一の張力をかけた状態で、前記芯線の一方の端部と、前記メイン芯線の一方の端部とを治具を介して固定し、
前記芯線の他方の端部と、前記メイン芯線の他方の端部とを治具を介して固定した後、
前記本体部および中空管を前記本体部の径方向に向かって外部から加圧するとともに加熱して、前記本体部を成形する工程を実施し、
サブルーメンを形成する前記工程では、前記一対の治具を離間する方向に引っ張ることで、前記中空管内部の前記芯線および前記メイン芯線に対して、前記第一の張力よりも大きな第二の張力をかけて、前記芯線および前記メイン芯線を同時に伸張させて縮径させ、前記中空管内部から、前記芯線を抜去するとともに、前記管状の本体部から前記メイン芯線を抜去する医療機器の製造方法。 - 請求項1乃至4のいずれかに記載の医療機器の製造方法において、
芯線の周囲に樹脂材料を供給し、前記芯線が内部に挿入された中空管を成形する前記工程では、
前記芯線が内部に挿入された中空管の外周面の表面処理を行なう工程を含む医療機器の製造方法。 - 請求項1に記載の製造方法により製造された医療機器。
- 請求項6に記載の医療機器において、
前記中空管内面には、前記中空管の長手方向に延在する複数の凸部あるいは複数の凹部が形成され、
前記複数の凸部または複数の凹部は、前記中空管の長手方向にそって離間配置された医療機器。 - 内部にメインルーメンが形成された管状の本体部と、
前記メインルーメンの外周側に配置され、サブルーメンを区画する中空管とを備え、
前記中空管内には、操作線が遊挿されており、
前記中空管内面には、前記中空管の長手方向に延在する複数の凸部あるいは複数の凹部が形成され、
前記複数の凸部または複数の凹部は、前記中空管の長手方向にそって離間配置されており、
前記操作線の近位端を操作することで、管状の本体部の遠位端部が屈曲する医療機器。 - 請求項7または8に記載の医療機器において、
前記中空管の内面には、前記中空管の長手方向に延在する前記凹部が形成されており、
前記凹部の深さ方向および長手方向と直交する方向の長さである幅は、前記操作線の径よりも小さい医療機器。 - 請求項7乃至9のいずれかに記載の医療機器において、
前記中空管の内面には、前記中空管の長手方向に延在する前記凸部が形成されており、
前記凸部の曲率半径は、前記操作線の曲率半径よりも小さい医療機器。 - 請求項10に記載の医療機器において、
前記操作線は、複数の細線を撚りあわせることにより構成された撚り線であり、
前記撚り線の外接円と、前記撚り線の外周部を構成する隣接する2本の細線と、に接触する内接円の径よりも、前記凸部の高さおよび前記凸部の幅が小さい医療機器。
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US14/377,389 US10537706B2 (en) | 2012-02-28 | 2013-02-27 | Method for manufacturing medical instrument, and medical instrument |
KR1020147026693A KR20140127357A (ko) | 2012-02-28 | 2013-02-27 | 의료 기기의 제조 방법 및 의료 기기 |
CN201380011545.6A CN104144726A (zh) | 2012-02-28 | 2013-02-27 | 医疗设备的制造方法以及医疗设备 |
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US11395665B2 (en) | 2018-05-01 | 2022-07-26 | Incept, Llc | Devices and methods for removing obstructive material, from an intravascular site |
EP3787523A4 (en) | 2018-05-01 | 2022-02-23 | Incept, LLC | DEVICES AND METHODS FOR REMOVAL OF OBSTRUCTIVE MATERIAL FROM AN INTRAVASCULAR SITE |
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JP2023517575A (ja) | 2020-03-10 | 2023-04-26 | インパラティブ、ケア、インク. | 可撓性を増強した神経血管カテーテル |
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