WO2024071117A1 - バルーンカテーテル - Google Patents
バルーンカテーテル Download PDFInfo
- Publication number
- WO2024071117A1 WO2024071117A1 PCT/JP2023/034940 JP2023034940W WO2024071117A1 WO 2024071117 A1 WO2024071117 A1 WO 2024071117A1 JP 2023034940 W JP2023034940 W JP 2023034940W WO 2024071117 A1 WO2024071117 A1 WO 2024071117A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- tip
- balloon
- shaft
- crystallinity
- layer
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Ceased
Links
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
- A61M25/10—Balloon catheters
-
- 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
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/0045—Catheters; Hollow probes characterised by structural features multi-layered, e.g. coated
-
- 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
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/0054—Catheters; Hollow probes characterised by structural features with regions for increasing flexibility
-
- 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
- A61M25/10—Balloon catheters
- A61M25/1027—Making of balloon catheters
- A61M25/1029—Production methods of the balloon members, e.g. blow-moulding, extruding, deposition or by wrapping a plurality of layers of balloon material around a mandril
-
- 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
- A61M25/10—Balloon catheters
- A61M25/1027—Making of balloon catheters
- A61M25/1034—Joining of shaft and balloon
-
- 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
- A61M25/10—Balloon catheters
- A61M25/104—Balloon catheters used for angioplasty
-
- 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
- A61M25/10—Balloon catheters
- A61M2025/1043—Balloon catheters with special features or adapted for special applications
- A61M2025/1093—Balloon catheters with special features or adapted for special applications having particular tip characteristics
Definitions
- the present invention relates to a balloon catheter.
- Balloon catheters are used to introduce a balloon into a narrowed area in a lumen or body cavity and expand the narrowed area from the inside outward in order to relieve and treat narrowed areas in the body.
- balloon catheters are used in percutaneous coronary intervention, which improves blood flow by expanding narrowed areas in the coronary arteries with a balloon.
- a guiding catheter is first introduced and placed at a specific location in the blood vessel, and then a treatment device such as a balloon catheter is inserted into it to perform the specified treatment.
- the catheter has a long shaft member that is stretched in the axial direction. Since the shaft member is introduced by the user (operator) to a specified position, such as near a narrowed area inside the living body, it is necessary for the tip side to be flexible so as to reduce the stress applied to the living body while maintaining sufficient hardness to transmit the user's operation to the tip in order to prevent buckling inside the living body.
- Patent Document 1 discloses a configuration in which a soft tip is fixed to the tip of the inner tube of a balloon catheter, thereby providing flexibility to the tip.
- Patent Document 2 discloses a balloon catheter in which a balloon portion is joined to both the soft tip and the outer periphery of the shaft portion, and the tip of the balloon portion is tapered.
- balloon catheters need to be easy to pass through the body, so they need to be sufficiently flexible.
- the present invention aims to provide a highly flexible balloon catheter.
- the crystallinity on the distal end side of the balloon tip portion gradually decreases from the base end side toward the distal end side.
- the crystallinity on the tip side of the balloon tip portion is preferably 1.5 to 6% lower than that on the base side.
- the tip of the balloon in a cross-sectional view in the axial direction, it is preferable that the tip of the balloon has a wedge portion having a wedge shape, and the wedge portion has a parallel portion that is parallel to the axial direction.
- the balloon has an inner layer, a base layer, and an outer layer, and the crystallinity of the outer layer in the parallel portion is lower than the crystallinity of the inner layer.
- the inner layer and the outer layer contain an elastomer.
- the balloon catheter further comprises a tip member fused to the tip side of the shaft and softer than the shaft, and that the crystallinity of the base end of the tip member and the crystallinity of the tip region of the balloon tip are each less than 40%.
- the thickness of the tip of the balloon located at the portion fused to the shaft is equal to or smaller than the thickness of the shaft at a portion adjacent to the base end side of the portion where the balloon is joined to the shaft, and is greater than the thickness of the shaft at the portion joined to the balloon.
- the above aspect of the present invention makes it possible to provide a highly flexible balloon catheter.
- FIG. 1 is a diagram showing the overall configuration of a balloon catheter according to an embodiment of the present invention
- 1 is a diagram showing a cross section along the axial direction near a balloon of a balloon catheter according to one embodiment of the present invention.
- FIG. FIG. 3 is a partially enlarged view showing part A in FIG. 2 .
- FIG. 3B is a view corresponding to FIG. 3A of a balloon catheter according to a modified example.
- 1A to 1C are diagrams for explaining a method for manufacturing a balloon catheter according to one embodiment of the present invention.
- FIG. 3C is a view corresponding to FIG. 3B of a balloon catheter according to an embodiment of the present invention.
- FIG. 3C is a view corresponding to FIG. 3B of a balloon catheter according to an embodiment of the present invention.
- FIG. 1 is a graph showing the IR spectrum of Resin 1 used in the balloon catheter of the example.
- 1 is a graph showing the IR spectrum of Resin 2 used in the balloon catheter of the embodiment.
- 1 is a graph showing the IR spectrum of Resin 3 used in the balloon catheter of the example.
- 1 is a graph showing the IR spectrum of Resin 4 used in the balloon catheter of the example.
- 1 is a graph showing the IR spectrum of Resin 5 used in the balloon catheter of the example.
- 1 is an image showing the results of measurement of crystallinity distribution by IR imaging of balloon catheters of Examples and Comparative Examples.
- 1 is an image showing the relationship between the crystallinity distribution measured by IR imaging of a balloon catheter according to an embodiment and each component.
- FIG. 1 is a diagram showing the relationship between appearance photographs and IR images and measurement positions in balloon catheters of Examples and Comparative Examples.
- FIG. 1 shows the results of a cantilever bending test on balloon catheters of Examples and Comparative Examples.
- X to Y includes X and Y and means "X or more and Y or less.”
- any combination of two or more of the individual preferred embodiments of the present invention described below is also a preferred embodiment of the present invention and is considered to be disclosed in this specification (i.e., it is a legitimate basis for amendment).
- One aspect of the present invention is a balloon catheter having an axially extending shaft and a balloon disposed on the outer periphery of the shaft, with the crystallinity of the distal end side of the balloon being lower than that of the proximal end side.
- the crystallinity of the distal end side of the balloon tip is lower than that of the proximal end side, making it flexible and allowing for good passage through the body.
- the balloon tip refers to the portion where the balloon and the shaft are joined.
- the tip side of the balloon tip refers to the area closer to the tip than the center of the balloon tip.
- the base side of the balloon tip refers to the area closer to the base than the center of the balloon tip.
- Crystallization is an index showing the crystallization rate of a resin, and in this specification is expressed as (crystalline band intensity (absorbance) / amorphous band intensity (absorbance)) x 100 (%).
- a crystalline band refers to a band that disappears when measured by FT-IR at the melting temperature
- an amorphous band refers to a band that does not disappear when measured by FT-IR even at the melting temperature.
- select one crystalline band and one amorphous band as described below. Specifically, select one peak with minimal peak overlap and baseline fluctuation.
- crystallinity is expressed as follows:
- the specific crystalline band is that crystalline band if there is one, and is the selected band if there are multiple crystalline bands.
- the specific amorphous band is that amorphous band if there is one, and is the selected band if there are multiple amorphous bands.
- the crystalline band intensity is the intensity at 1161 cm ⁇ 1 .
- the amorphous band intensity is the intensity at 1369 cm ⁇ 1 .
- the crystallinity of the resin is measured as a crystallinity distribution by IR imaging.
- the crystallinity distribution is measured under the following conditions: Measurement method: Microscopic transmission method Measurement range: 700 ⁇ m square (128 pixel square) Element size: 5.5 ⁇ m square Accumulation: 128 times Spectral resolution: 4 cm
- Measurement method Microscopic transmission method Measurement range: 700 ⁇ m square (128 pixel square) Element size: 5.5 ⁇ m square Accumulation: 128 times Spectral resolution: 4 cm
- Pretreatment The sample is embedded in epoxy resin and processed into thin sections with a thickness of approximately 10 ⁇ m using a microtome.
- melting means that at least a part of the resin melts, preferably 80% by mass or more of the resin melts, more preferably 95% by mass or more of the resin melts, and even more preferably 99% by mass or more of the resin melts.
- the melting temperature is not particularly determined as long as it is a temperature at which the resin melts, but if the resin is a crystalline thermoplastic resin, it is preferably the melting point of the thermoplastic resin + 10°C or more, and more preferably the melting point of the thermoplastic resin + 20 to 80°C.
- the resin is a non-crystalline thermoplastic resin
- it is preferably the glass transition temperature of the thermoplastic resin + 10°C or more, and more preferably the glass transition temperature of the thermoplastic resin + 20 to 80°C.
- the melting temperature is 150 to 300°C, or 200 to 250°C.
- crystallinity at the tip side of the balloon tip refers to the average crystallinity of the balloon in the region distal to the center of the balloon tip when viewed in axial cross section.
- Crystallism at the base side of the balloon tip refers to the average crystallinity of the balloon in the region proximal to the center of the balloon tip when viewed in axial cross section. The average crystallinity can be determined by calculating the average value of the above regions.
- the crystallinity at the balloon tip refers to the crystallinity of the balloon base layer.
- the crystallinity on the distal end side of the balloon tip is preferably 10-50%, more preferably 20-45% or less, and may be 30-40%.
- the crystallinity on the proximal end side of the balloon tip is preferably 10-50%, and may be 20-45% or 30-45%.
- the crystallinity of the balloon tip gradually decreases from the base end toward the tip end.
- “Gradually decreases” means that when the balloon tip is divided into four regions in the axial direction, the average crystallinity of each region is (region on the base end side ⁇ region on the tip end side).
- a gradual change in crystallinity results in a gradual change in hardness from the tip end to the base end side, resulting in a gradient of physical properties that can contribute to improved passability within the body and maintain flexibility against bending at the balloon tip.
- the crystallinity at the tip side of the balloon tip is preferably 2 to 6% lower than that at the base end.
- the crystallinity at the tip side of the balloon tip may be 1.5 to 6%, preferably 1.7 to 5.8%, and more preferably 1.8 to 5.5% lower than that at the base end. This results in a gradual change in hardness from the tip side to the base end, resulting in a gradient in physical properties that contributes to improved passability within the body and maintains flexibility against bending at the balloon tip.
- FIG. 1 is a diagram showing the overall configuration of a balloon catheter 3 according to one embodiment of the present invention.
- Figure 2 is a diagram showing a cross section along the axial direction near the tip of a balloon catheter 3 according to one embodiment.
- Figure 3A is a partially enlarged view near the tip of Figure 2.
- the balloon catheter 3 is a medical device that inserts a long shaft 310 into a biological organ and expands a balloon 60 located at the tip of the shaft 310 at the stenosis (lesion) to expand the stenosis and provide treatment.
- the balloon catheter 3 is configured as a PTCA dilation balloon catheter used to widen narrowed areas of the coronary artery, but can also be configured for use, for example, in treating and improving narrowed areas formed in other biological organs, such as other blood vessels, bile ducts, tracheas, esophagus, other digestive tracts, urethra, ear and nose cavities, and other organs, and can also be configured as a delivery balloon catheter used to transport medical devices such as stents inside the body.
- the side of the balloon catheter 3 that is inserted into the living body (the left side in FIG. 1) is referred to as the distal side
- the side of the balloon catheter 3 where the hub 340 is located is referred to as the proximal side
- the direction in which the shaft 310 of the balloon catheter 3 extends is referred to as the axial direction.
- the distal end refers to a certain range including the distal end (the most distal end) and its periphery
- the proximal end refers to a certain range including the proximal end (the most proximal end) and its periphery.
- the balloon catheter 3 has a shaft 310 extending in the axial direction, a tip member 320 arranged at the tip end of the shaft 310, a hub 340 arranged at the base end of the shaft 310, and a balloon 60 arranged on the outer periphery of the shaft 310.
- the shaft 310 has an outer tube shaft 311 having an inner cavity 311H, and an inner tube shaft 312 disposed in the inner cavity 311H of the outer tube shaft 311.
- the shaft according to the preferred embodiment of the present invention corresponds to the inner tube shaft 312.
- the shaft 310 has a double-tube structure in which the inner tube shaft 312 and the outer tube shaft 311 are aligned concentrically.
- the balloon catheter 3 is a so-called rapid exchange type in which a base end opening (base end opening of the inner tube shaft 312) 312R from which the guide wire 280 is led out is provided near the tip end of the shaft 310. Note that the inner tube shaft 312 and the outer tube shaft 311 do not have to be aligned concentrically.
- the inner tube shaft 312 has a tubular shape with a guidewire lumen 315 through which the guidewire 280 is inserted.
- the inner tube shaft 312 has a tapered section 318 in the axial vicinity of the base end 65 of the balloon 60, the diameter of which decreases from the base end toward the tip.
- the inner diameter of the inner tube shaft 312 on the base end side of the tapered section 318 is larger than the inner diameter of the inner tube shaft 312 located at the X-ray contrast marker 270 described below, and is larger than the outer diameter of the inner tube shaft 312 at the portion where the balloon 60 is joined to the inner tube shaft 312.
- the inner cavity 311H of the outer tube shaft 311 functions as a pressurized medium lumen that circulates the pressurized medium between the outer tube shaft 311 and the inner tube shaft 312.
- the hub 340 has a port 341 that can be liquid-tightly and air-tightly connected to a supply device (not shown) such as an indeflator for supplying a pressurized medium to the balloon 60.
- a supply device such as an indeflator for supplying a pressurized medium to the balloon 60.
- the port 341 of the hub 340 can be configured, for example, by a known luer taper that is configured to allow a fluid tube or the like to be connected and disconnected.
- the pressurized medium e.g., saline, contrast medium, etc.
- the inner tube shaft 312 has an outer layer 313 (outer shaft layer) and an inner layer 314 (inner shaft layer) disposed radially inward of the outer layer 313.
- the inner tube shaft 312 has a tapered section 318 in the vicinity of the base end 65 of the balloon 60 in the axial direction, the diameter of which decreases from the base end to the tip.
- the outer diameter of the inner tube shaft 312 on the base end side of the tapered section 318 is larger than the outer diameter of the inner tube shaft 312 located at the X-ray contrast marker 270 described below, and the outer diameter of the inner tube shaft 312 located at the X-ray contrast marker 270 is larger than the outer diameter of the inner tube shaft 312 at the portion where the balloon 60 is joined to the inner tube shaft 312.
- the inner diameter of the inner tube shaft 312 proximal to the tapered portion 318 is larger than the inner diameter of the inner tube shaft 312 located at the X-ray contrast marker 270 described below, and is larger than the outer diameter of the inner tube shaft 312 at the portion where the balloon 60 is joined to the inner tube shaft 312.
- the average thickness of the shaft inner layer is preferably 0.5 to 49.5 ⁇ m, and more preferably 5 to 25 ⁇ m.
- the average thickness of the shaft outer layer is preferably 0.5 to 10 ⁇ m, and more preferably 1 to 5 ⁇ m.
- the tip 312A of the inner tube shaft 312 is formed so as to draw an arc and extend radially outward from the inner surface 320H of the tip member 320, as shown in FIG. 3A.
- the tip 312A of the inner tube shaft 312 extends radially outward from the lumen 310H of the shaft 310 toward the tip of the balloon catheter 3, in a curved manner, as shown in FIG. 3A.
- the tip portions of the outer layer 313 and inner layer 314 of the inner tube shaft 312 are formed to arc radially outward from the inner surface 320H of the tip member 320.
- the tip portion 313A of the outer layer 313 and the tip portion 314A of the inner layer 314 extend radially outward from the lumen 310H of the shaft 310 toward the tip of the balloon catheter 3, curving outward as far as the tip, as shown in FIG. 3A.
- the inner layer 314 of the inner tube shaft 312 has a portion where the crystallinity gradually decreases from the tip 314A of the inner layer 314 toward the base end in the region where the tip 60A of the balloon 60 is joined to the inner tube shaft.
- the tip 312A of the inner tube shaft 312 is thinner than the rest of the body because the balloon 60 is embedded in it.
- the tip portion 312A of the inner tube shaft 312 is formed so as to draw an arc from the inner surface 320H of the tip member 320 toward the radially outward (upward in the figure) in an axial cross-sectional view.
- the tip portion 312A of the inner tube shaft 312 starts from the lumen 30H of the inner tube shaft 312 and extends in a curved manner radially outward toward the tip side of the balloon catheter 3 (left side in the figure) to the tip end 312D, and then extends in a curved manner radially outward from the tip end 312D toward the base end side of the balloon catheter 3 (right side in the figure).
- the tip 312A of the inner tube shaft 312 curves and extends radially outward from the portion 30H1 of the lumen 30H of the balloon catheter 3 toward the tip side of the balloon catheter 3 (the left side of the figure) to the most distal end 312D.
- the tip 312A of the inner tube shaft 312 extends from the most distal end 312D toward the apex 312P toward the base end side of the balloon catheter 3 (the right side of the figure).
- the tip member 320 has a clamping portion 321 that is clamped by the tip 312A of the inner tube shaft 312 and the tip 60D of the balloon 60.
- the clamping portion 321 is engaged with the tip 312A of the inner tube shaft 312.
- the apex 312P of the tip 312A of the inner tube shaft 312 extends in the axial direction toward the base end.
- the clamping portion 321 of the tip member 320 is arranged to be clamped by the apex 312P of the tip 312A of the inner tube shaft 312, which extends like a claw, and the tip 60D of the balloon 60.
- the clamping portion 321 of the tip member 320 firmly engages the tip member 320, the inner tube shaft 312, and the balloon 60.
- the clamping portion 321 is located between the outer layer 313 of the inner tube shaft 312 and the inner layer 66 of the balloon 60, and the thickness gradually decreases toward the base end, and extends to the terminal end 321P.
- the inner surface side base end 320Ha of the tip member 320 is located in a section sandwiched between the inner surface 320H of the tip member 320 and the inner surface 312H of the inner tube shaft 312 that contacts the tip member 320.
- the thickness of the inner surface side base end 320Ha increases in the section from the portion 310H1 of the lumen 310H of the inner tube shaft 312 toward the tip according to the curvature of the inner surface 312H.
- the outer surface side base end 320Ga of the tip member 320 is located in a section sandwiched between the outer surface 320G of the tip member 320 and the outer surface 60G of the balloon 60.
- the thickness of the outer surface side base end 320Ga increases in the section from the portion 30G1 of the outer periphery 30G of the balloon catheter 3 toward the tip according to the curvature of the balloon 60.
- the outer surface 320G of the tip member 320 and the outer surface 60G of the balloon 60 form a straight section without any steps in a cross-sectional view in the axial direction.
- the inner surface 320H of the tip member 320 and the inner surface 312H of the inner layer 314 of the inner tube shaft 312 facing the lumen 310H form a straight section without any step in the axial cross section.
- the straight section formed by the outer surface 320G of the tip member 320 and the outer surface 60G of the balloon 60 is inclined so that an intersection point exists on the extension line of each straight section on the tip side of the balloon catheter 3 with respect to the straight section of the inner surface 312H.
- the part 30G1 of the outer surface side base end 320Ga of the tip member 320 is located on the tip side in the axial direction from the part 30H1 of the inner surface side base end 320Ha.
- the end 321P of the clamping part 321 is located on the tip side in the axial direction from the part 30G1 of the outer surface side base end 320Ga of the tip member 320.
- the end 321P of the clamping part 321 is located on the tip side in the axial direction from the part 30H1 of the inner surface side base end 320Ha of the tip member 320.
- the inner tube shaft 312 is provided with two X-ray contrast markers 270 that indicate the axial position of the balloon 60.
- the X-ray contrast markers 270 can be made of thin metal wires made of X-ray opaque materials such as metals such as platinum, gold, silver, titanium, and tungsten, or alloys of these metals.
- the X-ray contrast markers 270 can also be made of a resin material containing powder of an X-ray opaque material.
- the base end 65 of the balloon 60 is joined to the tip 311A of the outer tube shaft 311 as shown in FIG. 2.
- the tip 60A of the balloon 60 is formed so as to draw an arc from the outer surface of the tip member 320 toward the inside in the radial direction as shown in FIG. 3A.
- the tip 60A of the balloon 60 is configured to be convex so as to narrow toward the tip side as shown in FIG. 3A and FIG. 3B.
- the tip 60D of the tip 60A of the balloon 60 is rounded.
- the tip member 320, the inner layer 314, the outer layer 313, the tip member 320, the tip 60D1 of the tip 60A of the balloon 60, and the tip member 320 are located in this order in the radial direction from the central axis.
- the tip portion 60A of the balloon 60 has a wedge portion 60A1 having a wedge shape as shown in FIG. 3A.
- the wedge portion 60A1 has a parallel portion 60A2 parallel to the axial direction.
- the outer surface of the base layer 67 has a wedge portion 60A1 that is inclined almost linearly with respect to the axial direction.
- the inner surface of the base layer 67 has a parallel portion 60A2 extending parallel to the axial direction.
- the parallel portion 60A2 extends parallel to the inner layer 314 of the inner tube shaft and the outer layer 313 of the inner tube shaft.
- a mixed layer 69 of the balloon inner layer 66 and the balloon outer layer 68 is located on the tip side of the intersection between the wedge portion 60A1 and the parallel portion 60A2.
- the rigidity of the balloon 60 gradually shifts from the tip side to the base end side, so that the balloon 60 is smoothly bent at the point where it is fused to the inner tube shaft 312.
- the base layer 67 at the tip of the balloon the base end side of the wedge portion 60A1 has higher crystallinity than the tip side. This, combined with the inclination of the wedge portion 60A1, may make it easier to pass through a hard fibrous stenosis while pushing the lesion apart when inserted.
- the base layer 67 at the tip of the balloon has an outer layer 68 laminated on its outer surface, so it may be easier to pass through soft lesions while penetrating them.
- the balloon catheter 3 has, from the tip side, a constant outer diameter section 3E, a first tapered section 3F, a second tapered section 3G, and a third tapered section 3H.
- the inclination of the second tapered section 3G relative to the axial direction is greater than the inclination of the first tapered section 3F.
- the inclination of the third tapered section 3H relative to the axial direction is less than the inclination of the second tapered section 3G.
- the above-mentioned multi-stage tapered section makes it easier to insert and pass through a narrowed section.
- Each of the above tapered sections is formed by being pressed from a direction corresponding to the inclination.
- the third tapered section 3H may be a constant outer diameter section whose outer diameter is made approximately constant.
- the balloon may have a one-layer structure consisting of a base layer, a two-layer structure consisting of an inner layer and a base layer laminated from the lumen side, a three-layer structure consisting of an inner layer, a base layer (middle layer), and an outer layer from the lumen side, or a structure of four or more layers.
- the tip portion 60A of the balloon 60 corresponds to the base layer. It is preferable that the crystallinity of the outer layer in the parallel portion 60A2 is lower than that of the inner layer. This allows the fusion (joining) portion to maintain flexibility against bending.
- the cross-sectional area ratio of the balloon's base layer is preferably 30 to 70%, and more preferably 35 to 60%.
- the average thickness of the base layer is preferably 5 to 20 ⁇ m.
- the thickness of the balloon base layer may be set to an appropriate thickness based on the balloon diameter and the required burst resistance and passability.
- the average thickness of the balloon's base layer is measured by calculating it from the design dimensions of the original tube and the thickness of the balloon.
- the average thickness of the balloon's base layer is the average thickness of the base layer in the membrane-like body that makes up the balloon.
- the average thickness of the balloon's outer layer is preferably 5 to 15 ⁇ m, and more preferably 5 to 10 ⁇ m. If the average thickness is in the range of 5 to 15 ⁇ m, abrasion resistance to hard components such as calcified lesions can be improved, making it possible to apply the procedure more safely.
- the average thickness of the balloon's outer layer refers to the average thickness of the outer layer of the membrane-like body that constitutes the balloon.
- the cross-sectional area ratio of the outer layer is preferably 20-50%, and more preferably 25-50%. Within this range, it is possible to achieve both burst resistance and expansion performance for hard lesions such as calcified lesions.
- the average thickness of the balloon's inner layer is preferably 0.1 to 10 ⁇ m, and more preferably 0.1 to 7 ⁇ m. An average thickness in the range of 0.1 to 10 ⁇ m is preferable because it provides a balance between the flexibility of the entire balloon and its low compliance characteristics.
- the average thickness of the balloon's inner layer is the average thickness of the inner layer in the membrane-like body that constitutes the balloon.
- the thickness D1 at the tip 60D of the balloon 60 located at the portion fused to the inner tube shaft 312 is equal to or smaller than the thickness D2 of the inner tube shaft 312 at a site P adjacent to the base end side of the portion where the balloon 60 is joined to the inner tube shaft 312, and is greater than the thickness D3 of the inner tube shaft 312 at the portion joined to the balloon 60.
- the balloon 60 has, from the inside, an inner layer 66, a base layer 67, and an outer layer 68.
- the inner layer 66 and the outer layer 68 are mixed together to form a mixed layer 69.
- the mixed layer 69 is formed by mixing the balloon inner layer 66 and the outer layer 68 together and integrating them.
- a balloon catheter according to a preferred embodiment of the present invention includes a tip member that is fused to the tip side of a shaft (inner tube shaft) and is softer than the shaft, and it is preferable that the crystallinity of the base end side of the tip member and the tip region of the balloon tip are each less than 40%. This makes it possible to suppress the occurrence of cracks such as layer peeling, since the difference in crystallinity with adjacent resins is small.
- There is no particular lower limit to the crystallinity of the base end side of the tip member and the tip region of the balloon tip but it is usually 10% or more, and may be 20% or more.
- the crystallinity of the base end of the tip member is determined by the average value of the crystallinity of the tip member in the area obtained by drawing perpendicular lines in the axial direction at the very tip of the shaft and at a position 200 ⁇ m distal to the tip when viewed in axial cross section.
- the average crystallinity can be calculated by averaging the crystallinity values for each pixel in the above areas.
- the crystallinity of the tip region of the balloon tip is determined by the average crystallinity of the balloon in the region obtained by drawing perpendicular lines to the axial direction at the very tip of the balloon and at a position 150 ⁇ m proximal to that tip when viewed in axial cross section.
- the average crystallinity can be found by calculating the average crystallinity value for each pixel that corresponds to the above region.
- the method for calculating the average value based on the crystallinity values of the pixels that correspond to the region is the same below, so it will not be repeated.
- the thickness of the balloon at the tip located at the portion fused to the shaft is preferably equal to or smaller than the thickness of the shaft at the portion adjacent to the base end side of the portion where the balloon is joined to the shaft, and is greater than the thickness of the shaft at the portion where the balloon is joined.
- FIG. 5 is a view corresponding to FIG. 3B of the balloon catheter 5 according to the second embodiment.
- the balloon catheter 5 As shown in FIG. 5, the balloon catheter 5 according to the second embodiment has an inner tube shaft 512, a tip member 520 arranged on the tip side of the inner tube shaft 512, and a balloon 560 arranged on the outer periphery of the inner tube shaft 512.
- the inner tube shaft 512 has an outer layer 513 and an inner layer 514 disposed radially inward of the outer layer 513.
- the tip 512A of the inner tube shaft 512 is formed so as to draw an arc and extend radially outward from the inner surface 520H of the tip member 520, as shown in FIG. 5.
- the tip 512A of the inner tube shaft 512 starts from a portion 512H1 of the lumen 512H of the inner tube shaft 512 and extends radially outward toward the tip side of the balloon catheter 5, curving to the most distal end 512D.
- the inner tube shaft 512 is configured to bulge outward in the radial direction at a portion 512E located on the base end side from the tip end 512A of the inner tube shaft 512.
- the bulging portion 512F is positioned to engage with a clamping portion 521 of the tip member 520 (described later), improving the joining strength of the inner tube shaft 512 to the tip member 520.
- the tip member 520 has a clamping portion 521 that is clamped by the tip portion 512A of the inner tube shaft 512 and the tip portion 560D of the balloon 560.
- the base end portion 522 of the tip member 520 is located between the tip portion 560D of the balloon 560 and the tip portion 512A of the inner tube shaft 512.
- the clamping portion 521 functions as a buffer between the tip portion 560D of the balloon 560 and the tip portion 512A of the inner tube shaft 512, and it is possible to suppress the tip portion 560D of the balloon 560 from turning over or coming off. It is believed that the clamping portion 521 is formed because the tip member 520 flows between the inner tube shaft 512 and the balloon 560 during molding.
- the inner surface side base end 520Ha of the tip member 520 is located in a section sandwiched between the inner surface 520H of the tip member 520 and the inner surface 512H of the inner tube shaft 512 that contacts the tip member 520.
- the thickness of the inner surface side base end 520Ha in this section increases from the portion 510H1 of the lumen 510H of the inner tube shaft 512 toward the tip according to the curvature of the inner surface 512H.
- the tip portion 512A of the inner tube shaft 512 is located between the inner surface side base end 520Ha of the tip member 520 and the base end 522 (clamping portion 521) of the tip member 520.
- the tip portion 512A, the inner surface side base end 520Ha, and the clamping portion 521 are in contact with each other by fusion.
- the tip member 520 is arranged to encase the tip 560D of the balloon 560.
- the tip member 520 covers the radial outside of the tip 560D1 of the balloon 560 with the outer surface side base end 520Ga of the tip member 520, and the outer surface side base end 520Ga and the tip 560D1 to the part 560G1 of the outer circumference 560G form a curved boundary.
- the tip member 520 covers the radial inside of the tip 560D1 with the middle base end 522M of the tip member 520, and the middle base end 522M and the tip 560D1 form a curved boundary from the tip 560D1 to the base end side.
- the tip 560D1 of the tip 560D of the balloon 560 is covered by the outer surface side base end 520Ga and the middle base end 522M of the tip member 520.
- This configuration increases the bonding area between the tip member 520 and the tip 560A of the balloon 560, and prevents the tip 560D of the balloon 560 from turning over, improving the bonding strength.
- the tip 560A of the balloon 560 is formed so as to draw an arc and extend radially inward from the outer surface of the tip member 520.
- the tip 560D of the balloon 560 is formed in a tongue shape toward the tip side of the balloon catheter 5, as shown in FIG. 5.
- the tip 560D of the balloon 560 is configured so that its thickness is smaller on the tip side of the portion 562, and is configured so that its thickness is larger on the base end side of the portion 562.
- the balloon 560 like the balloon 60 according to the first embodiment described above, has an inner layer 566, a base layer 567, and an outer layer 568. At the tip 560A of the balloon 560, the inner layer 566 and the outer layer 568 are mixed together to form a mixed layer 569.
- FIG. 6 is a view corresponding to FIG. 3B of the balloon catheter 6 according to the third embodiment.
- the balloon catheter 6 As shown in FIG. 6, the balloon catheter 6 according to the third embodiment has an inner tube shaft 612, a tip member 620 arranged on the tip side of the inner tube shaft 612, and a balloon 660 arranged on the outer periphery of the inner tube shaft 612.
- the inner tube shaft 612 has an outer layer 613 and an inner layer 614 disposed radially inward of the outer layer 613.
- the tip 612A of the inner tube shaft 612 is formed so as to draw an arc and extend radially outward from the inner surface 620H of the tip member 620, as shown in FIG. 6.
- the tip 612A of the inner tube shaft 612 starts from a portion 612H1 of the lumen 612H of the inner tube shaft 612 and extends radially outward toward the tip side of the balloon catheter 6, curving to the most distal end 612D.
- the tip member 620 has a clamping portion 621 that is clamped by the tip portion 612A of the inner tube shaft 612 and the tip portion 660D of the balloon 660.
- the base end portion 622 of the tip member 620 is located between the tip portion 660D of the balloon 660 and the tip portion 612A of the inner tube shaft 612.
- the clamping portion 621 functions as a buffer between the tip portion 660D of the balloon 660 and the tip portion 612A of the inner tube shaft 612, and can suppress the tip portion 660D of the balloon 660 from turning over or coming off.
- the clamping portion 621 is formed because the tip member 620 flows between the inner tube shaft 612 and the balloon 660 during molding. Note that the clamping portion 621 according to the third embodiment is formed shorter in the axial direction than the clamping portion 521 according to the second embodiment.
- the tip member 620 is arranged to encase the tip 660D of the balloon 660.
- the tip member 620 covers the radial outside of the tip 660D1 of the balloon 660 with the outer surface side base end 620Ga of the tip member 620, and the outer surface side base end 620Ga and the tip 660D1 to the part 660G1 of the outer circumference 660G form a curved boundary.
- the tip member 620 covers the radial inside of the tip 660D1 with the middle base end 622M of the tip member 620, and the middle base end 622M and the tip 660D1 toward the base end form a curved boundary.
- the tip 660D1 of the tip 660D of the balloon 660 is covered by the outer surface side base end 620Ga and the middle base end 622M of the tip member 620.
- This configuration suppresses curling of the tip 660D of the balloon 660, improving the bonding strength.
- This configuration also increases the bonding area between the tip member 620 and the tip 660D of the balloon 660, improving the bonding strength.
- the tip 660A of the balloon 660 is formed so as to draw an arc and extend radially inward from the outer surface of the tip member 620.
- the tip 660D of the balloon 660 is formed in a tongue shape toward the tip side of the balloon catheter 6.
- the balloon 660 like the balloon 60 according to the first embodiment described above, has an inner layer 666, a base layer 667, and an outer layer 668. At the tip 661 of the balloon 660, the inner layer 666 and the outer layer 668 are mixed together to form a mixed layer 669.
- This section describes the materials used for the tip member, shaft (inner shaft) and balloon, which are components of a balloon catheter according to a preferred embodiment of the present invention.
- the resin constituting the tip member examples include polyolefin (e.g., polyethylene, polypropylene, polybutene, ethylene-propylene copolymer, ethylene-vinyl acetate copolymer, ionomer, or a mixture of two or more of these), polyvinyl chloride, polyamide, polyamide elastomer, polyurethane, polyurethane elastomer, polyimide, fluororesin, etc.
- the above resins may be used alone or in combination of two or more.
- the resin constituting the tip member preferably contains a polyamide elastomer, which has high flexibility and little affinity or hardness difference with adjacent members.
- the polyamide elastomer is preferably 50% by weight or more, more preferably 80% by weight or more, and even more preferably 100% by weight (made of polyamide elastomer).
- the polyamide elastomer may be used alone or in combination of two or more.
- Polyamide elastomers are thermoplastic resins made of copolymers with hard segments derived from crystalline polymers with high melting points and soft segments derived from amorphous polymers with low glass transition temperatures, and refer to those that have amide bonds (-CONH-) in the main chain of the polymer that forms the hard segments.
- a structural unit that has an amide bond (-CONH-) in the main chain of the polymer that forms the hard segments is also called the amide unit of a polyamide elastomer.
- the "amide unit of a polyamide elastomer” refers to a repeating unit derived from an amide bond in the polymer chain of the polyamide elastomer, and the amide unit in the polyamide elastomer is preferably at least one of the repeating units represented by the following formula (1) or formula (2).
- n is preferably an integer from 2 to 20, and more preferably an integer from 5 to 11.
- a is an integer from 4 to 12 and b is an integer from 4 to 10, and it is more preferable that a is an integer from 11 to 12 and b is an integer from 4 to 8.
- the polyamide elastomer contains at least one of the repeating units represented by the above formula (1) or formula (2).
- the polyamide elastomer may be a polyamide block copolymer represented by formula (3) or (4) described in the section on the shaft outer layer, either alone or in combination of two or more.
- polymers that form soft segments include polyesters and polyethers. Further examples include polyethers such as polyethylene glycol, polypropylene glycol, polytetramethylene ether glycol (PTMG), polyester polyols, and ABA triblock polyether diols. These can be used alone or in combination of two or more. In addition, polyether diamines obtained by reacting ammonia or the like with the terminals of polyethers can be used, for example, ABA triblock polyether diamines can be used.
- polyethers such as polyethylene glycol, polypropylene glycol, polytetramethylene ether glycol (PTMG), polyester polyols, and ABA triblock polyether diols. These can be used alone or in combination of two or more.
- polyether diamines obtained by reacting ammonia or the like with the terminals of polyethers can be used, for example, ABA triblock polyether diamines can be used.
- the soft segment content of the polyamide elastomer is preferably 1 to 50% by weight, more preferably 1 to 35% by weight, and even more preferably 10 to 30% by weight.
- the polyamide elastomer is preferably a polyether block amide copolymer obtained by condensation polymerization of a polyether block amide in which a polyamide block, which is a hard segment, and a polyether block, which is a soft segment, are bonded via an ester bond.
- polyamide elastomers may contain chain extenders such as dicarboxylic acids.
- polyamide elastomers may be used alone or in combination of two or more types.
- the Shore D hardness of the polyamide elastomer used in the tip member is preferably 50 to 80, and more preferably 55 to 80, from the viewpoint of flexibility.
- the Shore D hardness according to ISO 868 is used to measure the hardness of the polyamide elastomer.
- the polyamide elastomer may be synthesized or may be a commercially available product.
- Examples of commercially available products include the PEBAX (registered trademark) series, such as PEBAX (registered trademark) 2533, 3533, 4033, 5533, 6333, 7033, and 7233 manufactured by Arkema, the VESTAMID (registered trademark) E series manufactured by Polypla-Evonik, Grilflex ELG5660 (manufactured by EMS, polyamide block ratio: 67 wt%, Shore D hardness: 56), and Grilflex ELG6260 (manufactured by EMS, product name: Grilflex, polyamide block ratio: 85 wt%, Shore D hardness: 62). These commercially available products may be mixed and used.
- the tip member may contain pigments or dyes that emit white, black, blue, red, or yellow, or mixtures thereof.
- pigments or dyes may be selected from materials that absorb laser light and generate heat.
- materials that absorb laser light and generate heat include carbon black, activated carbon, graphite, carbon nanotubes, fullerenes; cyanine pigments, nickel dithiolene pigments, squalium pigments, naphthoquinone pigments, diimmonium pigments, azo organic pigments, phthalocyanine pigments, naphthalocyanine pigments, azulenocyanine pigments, and other condensed polycyclic organic pigments.
- the tip member can also be configured to contain a powdered contrast material.
- materials include compounds of gold, titanium, bismuth, and tungsten.
- the tip member may have a reinforcing body made of tungsten, SUS, or the like disposed within the above-mentioned materials. Examples of the reinforcing body include a coil-shaped or blade-shaped form.
- the resins that make up the shaft include polyolefins such as polypropylene, ethylene-propylene copolymer, and ethylene-vinyl acetate copolymer, modified polyolefin resins, thermoplastic resins such as soft polyvinyl chloride, various elastomers such as polyurethane elastomers, polyamide elastomers, and polyester elastomers, and crystalline plastics such as polyamide, crystalline polyethylene, and crystalline polypropylene.
- polyolefins such as polypropylene, ethylene-propylene copolymer, and ethylene-vinyl acetate copolymer
- modified polyolefin resins such as soft polyvinyl chloride
- various elastomers such as polyurethane elastomers, polyamide elastomers, and polyester elastomers
- crystalline plastics such as polyamide, crystalline polyethylene, and crystalline polypropylene.
- the resin constituting the shaft is preferably polyamide and/or polyamide elastomer.
- the resin constituting the outer layer of the shaft contains polyamide elastomer
- the resin constituting the inner layer of the shaft contains polyamide.
- the resin constituting the outer layer contains polyamide elastomer and polyamide
- the resin constituting the inner layer of the shaft contains polyamide.
- the resin constituting the outer layer contains polyamide elastomer and polyamide
- the resin constituting the inner layer of the shaft consists of polyamide (only).
- the mixing weight ratio is not particularly limited, but taking into consideration the stiffness of the catheter shaft and the fusion affinity with the inner layer, it is preferable that the polyamide elastomer:polyamide ratio is 1:0.1 to 1:10, and more preferably 1:0.5 to 1:5.
- the polyamide that can be contained in the inner and outer layers of the shaft is not particularly limited as long as it is a polymer having an acid amide bond (-CO-NH-) in the main chain, and is usually produced by polymerization of lactams or amino acids with a ring structure, or by condensation polymerization of dicarboxylic acids and diamines. Therefore, it is preferable to use a homopolyamide as this polyamide.
- Monomers that can be polymerized independently include ⁇ -caprolactam, aminocaproic acid, enantholactam, 7-aminoheptanoic acid, 11-aminoundecanoic acid, 12-aminododecanoic acid, 9-aminononanoic acid, piperidone, etc.
- examples of the dicarboxylic acids include adipic acid, sebacic acid, dodecanedicarboxylic acid, glutaric acid, terephthalic acid, 2-methylterephthalic acid, isophthalic acid, naphthalenedicarboxylic acid, etc.
- examples of the diamines include tetramethylenediamine, hexamethylenediamine, nonamethylenediamine, decamethylenediamine, undecamethylenediamine, dodecamethylenediamine, paraphenylenediamine, metaphenylenediamine, etc.
- Polyamides include nylon 4, 6, 7, 8, 11, 12, 6.6, 6.9, 6.10, 6.11, 6.12, 6T, 6/6.6, 6/12, 6/6T, 6T/6I, etc. Polyamides can be used alone or in combination of two or more. Among them, nylon 11 and nylon 12 (e.g., Grilamid L16, L25 manufactured by EMS; Daiamid L1940, L1940W manufactured by Polypla-Evonik Co., Ltd.) are preferred.
- the polyamide may be terminated at its ends with a carboxylic acid, an amine, or the like.
- carboxylic acid include aliphatic monocarboxylic acids such as adipic acid, caproic acid, caprylic acid, capric acid, lauric acid, myristic acid, palmitic acid, stearic acid, and behenic acid.
- amine include aliphatic primary amines such as hexylamine, octylamine, decylamine, laurylamine, myristylamine, palmitylamine, stearylamine, and behenylamine.
- the weight average molecular weight of the polyamide is preferably from 2.0 ⁇ 10 4 to 5.0 ⁇ 10 4 , more preferably from 3.0 ⁇ 10 4 to 5.0 ⁇ 10 4 , and further preferably from 4.0 ⁇ 10 4 to 5.0 ⁇ 10 4 .
- the molecular weight of the polymer according to the preferred embodiment of the present invention can be measured by known methods such as MS spectroscopy, light scattering, liquid chromatography, gas chromatography, and gel permeation chromatography (GPC), and in this specification, the molecular weight is measured by GPC.
- the polyamide elastomer that can be included in the outer layer of the shaft can be the polyamide elastomer described in the tip member section above.
- the weight of the amide units in the polyamide elastomer that can form the shaft outer layer is preferably 60% by weight or more, and more preferably 60 to 85% by weight.
- the weight of amide units in the polyamide elastomer is 60% by weight or more
- the weight of amide units (also called repeating units derived from amide bonds) in the polymer chain of the polyamide elastomer is 60% by weight or more relative to the weight of the entire polyamide elastomer.
- the weight of the amide unit in the polyamide elastomer is calculated by identifying peaks derived from the amide unit in the polyamide elastomer using 1H -NMR and 13C -NMR, calculating the unit ratio of the amide unit in one polymer chain from the integral ratio of 1H -NMR, and then multiplying the unit ratio by the molecular weight of the amide unit to obtain the weight percent of the amide unit.
- the polyamide elastomer that may be included in the outer layer of the shaft is preferably a polyamide block copolymer, and more preferably a diblock copolymer.
- the amide units of the polyamide elastomer which are represented by formula (1) or formula (2), preferably account for 60% by weight or more relative to the weight (100% by weight) of one polymer chain of the polyamide block copolymer.
- the polyamide block copolymer is represented by the following formula (3) or formula (4):
- a is an integer of 4 to 12
- b is an integer of 4 to 10
- c and d are integers of 0 to 100
- p is an integer of 2 to 4
- q is an integer of 1 to 100
- Ln is a linker moiety, -C(O)-R-C(O)-;
- the R is an alkylene group having 2 to 12 methylene groups, and preferably an alkylene group having 4 to 10 methylene groups.
- n is an integer of 5 to 11
- m and l are integers of 0 to 100
- p is an integer of 2 to 4
- q is an integer of 1 to 100
- Ln is a linker moiety, -C(O)-R-C(O)-;
- the R is an alkylene group having 2 to 12 methylene groups, and preferably an alkylene group having 4 to 10 methylene groups. It is more preferable that the composition contains at least one selected from the group consisting of:
- the alkylene group having 2 to 12 methylene groups in R may be linear, branched, or cyclic, and is not particularly limited. Specific examples include tetramethylene, 2-methylpropylene, 1,1-dimethylethylene, n-pentylene, n-hexylene, n-nonylene, 1-methyloctylene, 6-methyloctylene, 1-ethylheptylene, 1-(n-butyl)pentylene, 4-methyl-1-(n-propyl)pentylene, 1,5,5-trimethylhexylene, 1,1,5-trimethylhexylene, n-decylene, 1-methylnonylene, 1-ethyloctylene, 1-(n-butyl)hexylene, 1,1-dimethyloctylene, 3,7-dimethyloctylene, n-undecylene, and 1-methyldecylene.
- the polyamide elastomer that can be used in the outer layer of the shaft may be one type of polyamide block copolymer represented by the above formula (3) or (4), or a combination of two or more types.
- the polyamide block polymer may be terminated at its ends with a carboxylic acid, an amine, or the like.
- carboxylic acid include aliphatic monocarboxylic acids such as adipic acid, caproic acid, caprylic acid, capric acid, lauric acid, myristic acid, palmitic acid, stearic acid, and behenic acid.
- amine include aliphatic primary amines such as hexylamine, octylamine, decylamine, laurylamine, myristylamine, palmitylamine, stearylamine, and behenylamine.
- the weight average molecular weight of the polyamide elastomer is preferably from 1.0 ⁇ 10 4 to 1.0 ⁇ 10 5 , more preferably from 2.0 ⁇ 10 4 to 5.0 ⁇ 10 4 , and even more preferably from 2.0 ⁇ 10 4 to 4.0 ⁇ 10 4 .
- the Shore D hardness of the polyamide elastomer is preferably 54 or more and 62 or less from the viewpoint of flexibility.
- the polyamide elastomer may be synthesized or may be a commercially available product.
- examples of commercially available products include Grilflex ELG5660 (manufactured by EMS, polyamide block ratio: 67 wt%, Shore D hardness: 56) and Grilflex ELG6260 (manufactured by EMS, product name: Grilflex, polyamide block ratio: 85 wt%, Shore D hardness: 62).
- modified polyolefin resins can also be used for the shaft inner layer.
- modified polyolefin resins can be used for the shaft inner layer without using polyamide resins.
- modified polyolefin resins include polyethylene, polypropylene, ⁇ -olefin (e.g., 1-butene, 1-hexene, 4-methyl-1-pentene, 1-octene, 1-decene, etc.) polymers, ethylene-propylene copolymers, cycloolefin polymers (e.g., polymers of cyclic olefins such as norbornene, cyclobutene, cyclopentene, etc.), cycloolefin copolymers (e.g., copolymers of cyclic olefins and linear olefins such as polyethylene, or copolymers of cyclic olefins and dienes such as 1,4-hexa
- modified polyethylene high density polyethylene, low density polyethylene, linear low density polyethylene, etc.
- modified polypropylene is preferred as the modified polyolefin resin, and modified polyethylene is more preferred.
- the polar groups and reactive groups include carboxyl groups, carboxylic anhydride groups, hydroxyl groups, alkoxy groups, imide groups, acryloyl groups, methacryloyl groups, silanyl groups, and/or silanol groups.
- modified polyolefin resins such as the MODIC (registered trademark) series (H511, H503, L502, L533, L504, M142, M502, M512, M545, A543, A515), LINKLON (registered trademark) series (all from Mitsubishi Chemical Corporation), ADMER (registered trademark) series (Mitsui Chemicals, Inc.), and HIMILAN (registered trademark) series (Mitsui-DuPont Polychemicals Co., Ltd.).
- MODIC registered trademark
- H511, H503, L502, L533, L504, M142, M502, M512, M545, A543, A515) LINKLON (registered trademark) series (all from Mitsubishi Chemical Corporation), ADMER (registered trademark) series (Mitsui Chemicals, Inc.), and HIMILAN (registered trademark) series (Mitsui-DuPont Polychemicals Co., Ltd.).
- the weight average molecular weight of the modified polyolefin resin is preferably 1,000 to 10,000,000.
- the resin constituting the outer layer of the shaft contains polyamide and/or polyamide elastomer. More preferably, the resin constituting the outer layer of the shaft is polyamide and/or polyamide elastomer. In another preferred embodiment, the resin constituting the outer layer of the shaft contains polyamide and polyamide elastomer. In another preferred embodiment, it is preferable that the resin constituting the outer layer of the shaft contains polyamide and polyamide elastomer. In another preferred embodiment, a middle layer is provided between the inner layer and the outer layer containing the modified polyolefin resin, the middle layer and the outer layer contain polyamide, and the outer layer contains a laser light absorbing material described later.
- the effects of the outer layer such as improved abrasion resistance, protection of the strength layer from external damage, and prevention of pinholes, are easily exhibited, and the effects of the inner layer, such as ensuring the necessary pressure resistance and compliance, are also easily exhibited.
- the interlayer adhesion between the inner and outer layers of the shaft is improved.
- the shaft may contain pigments or dyes that emit white, black, blue, red, or yellow, and mixtures thereof.
- pigments or dyes may be selected from materials that absorb laser light and generate heat.
- materials that absorb laser light and generate heat include carbon black, activated carbon, graphite, carbon nanotubes, fullerenes; cyanine pigments, nickel dithiolene pigments, squarium pigments, naphthoquinone pigments, diimmonium pigments, azo organic pigments, phthalocyanine pigments, naphthalocyanine pigments, azulenocyanine pigments, and other condensed polycyclic organic pigments.
- the shaft inner layer contains a laser light absorbing material
- the shaft outer layer does not substantially contain a laser light absorbing material.
- the inner layer absorbs the laser light, generates heat, and the temperature rises above the glass transition point, accelerating deformation due to pressure, and the melting point is reached, increasing fluidity, which makes it easier to assume a suitable configuration in which "the tip of the inner layer draws an arc from the inner surface of the tip member toward the outside in the radial direction, while the tip of the outer layer draws an arc from the outer surface of the tip member toward the inside in the radial direction.”
- the amount of the laser light absorbing material is not particularly limited, but may be, for example, 1 to 25% by weight, 1 to 20% by weight, 1 to 10% by weight, or 2 to 8% by weight in the inner layer.
- a laser light absorbing material is blended into the shaft inner layer, it is preferable to select a transparent resin from the above-mentioned resin for the shaft outer layer. This makes it easier for the inner layer
- the surface of the outermost layer that may come into contact with the living body may be coated with a hydrophilic lubricating material.
- the hydrophilic lubricating material is not particularly limited as long as it is hydrophilic and has lubricating properties, and known materials can be used.
- hydrophilic lubricating materials include copolymers of epoxy group-containing monomers such as glycidyl acrylate, glycidyl methacrylate, 3,4-epoxycyclohexylmethyl acrylate, 3,4-epoxycyclohexylmethyl methacrylate, ⁇ -methylglycidyl methacrylate, and allyl glycidyl ether with hydrophilic monomers such as N-methylacrylamide, N,N-dimethylacrylamide, and acrylamide; (co)polymers composed of the above hydrophilic monomers; cellulose-based polymeric substances such as hydroxypropyl cellulose and carboxymethyl cellulose; polysaccharides, polyvinyl alcohol, methyl vinyl ether-maleic anhydride copolymers, water-soluble polyamides, poly(2-hydroxyethyl (meth)acrylate), polyethylene glycol, polyacrylamide, polyvinylpyrrolidone, and copolymers of polyvin
- the surface of the outer layer containing the polyamide elastomer which is the outermost layer that can come into contact with the living body, may be further coated with a biocompatible material or an antithrombotic material.
- a biocompatible material or antithrombotic material various known polymers can be used alone or in mixture, and for example, natural polymers (collagen, gelatin, chitin, chitosan, cellulose, polyaspartic acid, polyglutamic acid, polylysine, casein, etc.), synthetic polymers (phospholipid polymers, MPC (methacryloyloxyethyl phosphorylcholine) block polymers having phosphate groups in the side chains, polyhydroxyethyl methacrylate, copolymers of hydroxyethyl methacrylate and styrene (e.g. HEMA-St-HEMA block copolymers), polymethyl methacrylate, polylactic acid, polyglycolic acid, lactic acid-glycolic acid copolymers
- the base layer of the balloon preferably contains polyamide.
- a base layer containing polyamide preferably contains at least 50% by weight of polyamide, more preferably at least 80% by weight, and most preferably 100% by weight (i.e., made of polyamide resin) of the resin constituting the inner layer.
- polyamide as the resin of the base layer, it is possible to ensure the pressure resistance and low compliance characteristics during expansion required for a catheter balloon, and this is preferable.
- the base layer may contain known additives as necessary, or may be composed only of polyamide.
- any of those listed in the tip member section above can be appropriately selected and used.
- the polyamide used in the base layer of the balloon can be one type alone or two or more types in combination.
- nylon 11 and nylon 12 are preferred polyamides used in the base layer of the balloon.
- the weight average molecular weight of the polyamide used in the base layer of the balloon is preferably 2.0 ⁇ 10 4 to 5.0 ⁇ 10 4 , more preferably 3.0 ⁇ 10 4 to 5.0 ⁇ 10 4 , and even more preferably 4.0 ⁇ 10 4 to 5.0 ⁇ 10 4 .
- Additives that may be included in the base layer as needed include, but are not necessarily limited to, higher alcohols, hydroxybenzoic acid esters, and aromatic sulfonamides.
- the outer layer of the balloon preferably contains an elastomer. Furthermore, it is preferable that the inner layer of the balloon and the outer layer of the balloon contain an elastomer.
- An outer layer containing an elastomer is sufficient if it contains 1 to 100% by weight of elastomer, and may contain known additives as necessary, or may be composed of elastomer alone.
- Additives that may be included in the outer layer of the balloon if necessary are the same as those in the base layer of the balloon, so they will not be described here.
- the inner layer of the balloon preferably contains a polyamide elastomer, since this provides good adhesion to the base layer of the balloon and is less susceptible to delamination.
- An inner layer containing a polyamide elastomer preferably means that the resin constituting the inner layer is 50% or more by weight of polyamide elastomer, more preferably 80% or more by weight, and most preferably 100% by weight (i.e., made of polyamide elastomer resin).
- a catheter balloon When a balloon is formed with an inner layer containing a polyamide elastomer on the innermost side, a catheter balloon can be provided that exhibits stable pressure resistance, and the balloon as a whole can be made flexible, allowing it to pass easily through blood vessels or body cavities.
- an inner layer containing the same resin as the outer layer of the shaft is formed on the innermost part of the balloon, the adhesive affinity between the two resins will be excellent and the melt joint strength will be maintained at a high level. If an inner layer containing polyamide elastomer is formed on the innermost part, it is preferable when an outer layer containing polyamide or polyamide elastomer is formed on the shaft, as this will increase the affinity between the two and provide excellent joint strength.
- the polyamide elastomer contained in the inner and outer layers of the balloon can be the same material as the polyamide elastomer in the shaft described above, so a description of the polyamide elastomer will be omitted here.
- a preferred embodiment of the balloon according to the present invention is formed from a membrane-like body having an inner layer made of polyamide elastomer on the innermost side, a base layer made of polyamide laminated on the surface of the inner layer, and an outer layer made of polyamide elastomer provided on the outside of the base layer.
- the base layer, outer layer, and inner layer of the balloon are all preferably transparent.
- the balloon catheter which is a preferred embodiment of the present invention, can be manufactured by preparing a joint between a tip member and a shaft, and fusing the joint to a balloon.
- the joint of the tip member and the shaft is manufactured by joining the base end side of the tip member and the tip end side of the shaft. Specifically, it is preferable to have the following steps: (1) inserting the contact part of the tip member and the shaft into the hollow part of the elastic body (step (A)), (2) applying pressure radially inward and heating (step (B)), (3) releasing the pressure and removing the fused (joined) joint of the tip member and the shaft (step (C)).
- the bonded body and the balloon can be fused together by passing the material through the bonded body and the balloon core material and employing steps (A) to (C) similar to those described above.
- Step (A) The shaft 10 and the tip member 20 are inserted into the core material 150. This allows the shaft 10 and the tip member 20 to move and rotate integrally with the core material 150.
- the core material is made of, for example, metal.
- the core material 150 or the elastic body 130 is moved in the axial direction to position the contact portion of the shaft 10 and the tip member 20 in the hollow portion of the elastic body 130.
- the shaft 10 and the tip member 20 are not in contact with the hollow portion of the elastic body 130 in the radial direction, and a gap is generated.
- the elastic body is laser light transparent, and specifically, examples of the material of the elastic body include silicone rubber and fluororubber.
- the elastic body is elastically deformed in the radial direction by pressure applied by the pressure member described below, making it possible to maintain the contact state of the shaft and the tip member, and efficient joining can be performed.
- the elastic body is laser light transparent, it does not thermally shrink due to laser light, and can be reused.
- the pressurizing method is not particularly limited, but for example, a hollow cylindrical pressurizing member can be used.
- the hollow cylindrical pressurizing member is configured to be supported rotatably with the axial direction as the rotation axis, similar to the core material and the elastic body.
- the elastic body can be inserted into the hollow portion of the pressurizing member having such a shape.
- the elastic body is stretched in the axial direction, and the diameter of the elastic body is made smaller than the inner diameter of the pressurizing member, so that the elastic body can be inserted into the hollow portion of the pressurizing member.
- the inner diameter of the pressurizing member is preferably smaller than the diameter (outer diameter) of the elastic body.
- the elastic body is pressurized in the radial direction by reducing the internal volume of the hollow portion of the pressurizing member. This allows a substantially uniform force to act from the inner periphery of the pressurizing member through the elastic body to the outer periphery of the catheter shaft and the tip member.
- the shape of the pressure member is not limited to a hollow cylinder, and is not particularly limited as long as it can apply pressure to the elastic body in the radial direction.
- the pressure member like the elastic body, is laser light transmissive. Laser light transmissive means that the laser light transmittance per 1 mm of radial thickness is 80% or more.
- the material used for the pressure member may be any material that can apply an external force to the elastic body, such as glass, quartz, or sapphire.
- the contact area is directly heated.
- the contact area can also be locally heated by irradiating the contact area with laser light.
- the core material 150, elastic body 130, and pressure member (not shown) can be rotated about the axial direction as the axis of rotation, thereby rotating the tip member 20 and shaft 10 about the axial direction as the axis of rotation, so that heating is performed uniformly.
- the laser light is locally irradiated to the end faces and surrounding areas of the two members arranged in the axial direction.
- Such laser light irradiation causes the catheter shaft and/or the tip member to heat up, and further, heat is transferred from the core material to the catheter shaft and tip member, fusing the contact area between the base end side of the tip member and the tip side of the catheter shaft to form a fused part.
- at least one of the catheter shaft and/or the tip member, preferably at least the catheter shaft contains a laser light absorbing material. With this configuration, the member containing the laser light absorbing material is locally heated.
- the surrounding elastic body is laser light transparent, the elastic body is not heated, and heat is dissipated to the elastic body and surroundings (e.g., the core material) from the moment the fused part is heated. Furthermore, when the laser light irradiation is stopped after fusion, the fused part is cooled by heat dissipation. It is believed that such rapid local heating and subsequent rapid cooling makes it difficult for crystals to grow, and therefore the crystallinity of the fused part is reduced.
- a laser light of a wavelength that generates heat in the fused portion through radiative heating is irradiated.
- the spot diameter of the laser light can be set to ⁇ 0.1 to ⁇ 10 mm, and the wavelength of the laser light can be set to 800 to 10,000 nm.
- a fiber laser (wavelength 1070 nm), a YAG laser (wavelength 1064 nm), a laser diode (808 nm, 840 nm, 940 nm), or even a laser that generates wavelengths as described below can be used.
- the outer layer of the shaft is subjected to the greatest pressure, and the tip of the shaft tapers due to heating, making it easier for the inner and outer layers to become integrated.
- the balloon catheter can be manufactured by passing the joint and balloon core material through the same steps (A) to (C) as above.
- the components do not mix and form a lump. If a lump is present between the components, it is possible that cracks may occur due to the difference in mechanical properties between the base material of the component and the lump. Comparing the preferred embodiment of the present invention before and after molding, the shape of the components themselves in the axial cross section changes, but the radial positional relationship between the components is maintained.
- the laser irradiation unit irradiates laser light with a wavelength that generates heat in the fusion part by radiation heating.
- the spot diameter of the laser light can be configured to be ⁇ 0.1 to ⁇ 10 mm, and the wavelength of the laser light can be configured to be 800 to 10,000 nm.
- the wavelength of the laser light is appropriately selected from these ranges depending on the object to be processed. In the case of fusion between members containing a laser light absorbing material, the wavelength can be selected from 800 to 5,000 nm, preferably 900 to 2,300 nm.
- the wavelength can be selected from 1,300 to 2,500 nm, preferably 1,500 to 2,300 nm.
- the laser light is basically irradiated in a direction perpendicular to the axial direction of the object to be processed.
- the laser light may be irradiated at an angle appropriately changed depending on the object to be processed.
- the hollow elastic body made of silicone is laser light transmissive.
- Laser light transmissive means that the workpiece is made of a material with a laser light transmittance of 80% or more per mm of radial thickness.
- the workpiece is passed through a metal core and pressurized by the hollow elastic body in the axial direction of the core.
- the workpiece, core, hollow elastic body and their supports rotate around the axis of the core.
- the catheter with tip manufactured in 4-1 above was inserted into the core material, and the planned welding position of the tip of the balloon was arranged so as to straddle the boundary between the tip and the shaft.
- the hollow elastic body was passed through the elastic body so as to cover the planned welding position.
- the inner diameter of the hollow elastic body was larger than the outer diameter of the workpiece, and the workpiece and the hollow elastic body were not in contact before pressing.
- the workpiece was rotated around the axis of the core material, and the elastic body was pressurized from the outside and irradiated with laser light, so that a radially inward force was applied to the workpiece and the member irradiated with the laser light was heated.
- the temperature of the tip and the inner layer of the shaft which were mixed with a laser light absorbing material, rose earlier than the other members.
- the laser light irradiation and the pressurization by the hollow elastic body were stopped.
- the workpiece was cooled, it was removed from the core material. In this way, a balloon catheter (inner diameter: 0.41 mm, outer diameter: 0.57 mm) was produced.
- Pretreatment The samples were embedded in epoxy resin and cut into thin sections approximately 10 ⁇ m thick using a microtome. Resins 2 and 3 were cut into thin sections 10 ⁇ m thick using a microtome. Resins 1, 4, and 5 were cut into thin sections using a cutter.
- Resins 1 to 5 are as follows:
- Resin 1 Tube made of distal tip material
- Resin 2 Pellets of polyamide elastomer (Grilflex ELG5660, manufactured by EMS; material for inner and outer layers of balloons)
- Resin 3 Pellets of polyamide (Grilamid L25, manufactured by EMS; material for middle layer of balloons)
- Resin 4 Tube made of outer shaft layer material
- Resin 5 Tube made of inner shaft layer material The tubes were molded by extruding each resin while heating.
- the band A3 which has little peak overlap and baseline fluctuation, was selected as the band to be used for evaluating crystallinity.
- the crystallinity was evaluated using the peak intensity ratio of the crystalline band C9 to the amorphous band A3 as an index.
- Resin 2 balloon inner and outer layers
- 1) Resin 2 pellet form was processed into 10 ⁇ m thin slices using a microtome.
- the band C7 which has little peak overlap and baseline fluctuation, was selected as the band to be used for evaluating crystallinity.
- Five amorphous bands (A1 to A5) were identified (lower part of Figure 8).
- the crystallinity was evaluated using the peak intensity ratio of the crystalline band C7 to the amorphous band A3 as an index.
- ⁇ Resin 3 (middle layer of balloon) 1) Resin 3 (pellet form) was processed into 10 ⁇ m thin slices using a microtome.
- each resin was collected from pellets or components before they were processed into products, but it is also possible to select the bands to be used by collecting thin pieces of resin directly from the product.
- the crystalline band and amorphous band of each resin specified in 1-2 above were selected as follows.
- the crystalline band was selected to be 1161 cm -1 , which is common to each resin.
- the amorphous band had a width of 1366 to 1359 cm -1 when melted (lower row of Figures 7 to 11), but the band after cooling (upper row of Figures 7 to 11) was approximately 1369 cm -1 , so the amorphous band was set to 1369 cm -1 .
- the crystalline bands and amorphous bands were common for resins of the same series, but if different bands are selected for different resins, each band is selected using the following method to create an image of the crystallinity distribution. That is, when first selecting the crystalline bands and amorphous bands using method 1-2 above, a resin whose absorption peaks do not overlap with others is identified, and the crystalline bands and amorphous bands of that resin are selected.
- a region of the resin identified in the imaging IR is specified, and based on the data on the crystalline bands and amorphous bands of the specified region, the crystallinity is calculated using a formula in which Equation 2 is replaced with the crystalline bands and amorphous bands selected for the different resin, and a color image corresponding to the numerical value of the crystallinity is incorporated into the color image of the other resin.
- the balloon catheter of the embodiment has lower crystallinity than the comparative example. Also, unlike the balloon catheter of the comparative example, the balloon catheter of the embodiment has lower crystallinity on the tip side of the balloon middle layer than on the base side. Therefore, it is clear that the balloon catheter of the embodiment has improved flexibility compared to the balloon catheter of the comparative example.
- Figure 13 shows the relationship between the crystallinity distribution measured by IR imaging in the balloon catheter of the embodiment and each component.
- the tip of the balloon middle layer has a wedge-shaped portion, and the wedge portion has a parallel portion that is parallel to the axial direction. This is thought to result in a gradual transition in physical properties from the tip side of the balloon middle layer to the base side, which allows the fused portion to bend more smoothly.
- the crystallinity of the outer layer of the balloon is lower than that of the inner layer of the balloon.
- the crystallinity decreases from the base end to the tip end, and in particular in the middle layer of the balloon, the crystallinity gradually decreases from the base end to the tip end.
- the crystallinity at the tip end (mainly green) is about 1.5 to 6% lower than that at the base end (mainly orange) (crystallinity is 35.7%, 37.5%, 40.0%, and 41.2% from the tip end). This results in a gradual change in hardness from the tip end to the base end, resulting in a gradient of physical properties that contributes to improved passability within the body and maintains flexibility against bending near the fused part.
- the thickness of the balloon middle layer at the tip end is greater than the thickness of the shaft at the portion where it is joined to the balloon, and is equal to or slightly smaller than the thickness of the shaft (not shown) at the portion adjacent to the base end side of where the balloon is joined to the shaft. This is thought to allow the thickness of the balloon middle layer to be absorbed at the portion where the balloon is joined to the shaft, thereby suppressing an increase in stiffness.
- the crystallinity of the base end of the tip and the tip region of the balloon tip are each less than 40% (green to light blue). This is believed to improve strength while maintaining flexibility of the fused portion. In addition, because the difference in crystallinity with adjacent resins is small, it is believed that the occurrence of cracks such as delamination can be suppressed.
- the crystallinity of the shaft tip is higher than that of the tip region of the balloon tip, but it is thought that gradient physical properties can be achieved by buffering the stiffness of the shaft in the tip region of the balloon tip.
- the crystallinity on the base end of the distal tip (the average crystallinity of the distal tip in the region formed by drawing a perpendicular line in the axial direction from the most distal end of the shaft inner layer to a position 200 ⁇ m toward the tip) was 28%.
- the region showing a crystallinity of less than 20% was 42%.
- the crystallinity of the tip region of the balloon tip was 21.5%.
- Part B Interface between tip (blue) and shaft (black)
- Part A 0.5 mm from part B to the tip
- Part C 0.5 mm from part B towards the base end.
- the crystallinity of the distal end of the shaft inner layer and the proximal end of the distal tip are each less than 40% (green to light blue), and the crystallinity of the distal end of the middle layer of the balloon is around 40% (green), meaning that the crystallinity of the middle layer of the balloon is lower on the distal side than on the proximal side.
- the crystallinity of the tip of the shaft is over 40% to around 50% (orange), and the crystallinity of the tip of the balloon is around 50% in the axial direction (orange).
- the balloon catheter of the embodiment has lower crystallinity at the tip side of the shaft inner layer, the base end side of the tip tip, and the tip side of the balloon middle layer compared to the comparative example.
- the test results for the flexibility of the tip tip show that the result of the embodiment (40.0 gf after correcting for outer diameter) at a load of 0.3 mm pressed with a cantilever beam is approximately 23% more flexible than the result of the comparative example (51.8 gf).
- the test results for the flexibility of the balloon tip and the fused portion (fusion margin) of the shaft show that the result of the embodiment (37.0 gf after correcting for outer diameter) is approximately 30% more flexible than the result of the comparative example (52.8 gf).
- Materials 1-1. Tip material 2 A pigment (DAIREN ORANGE PPD-3865, manufactured by DIC, containing 8.57% by weight of perylene red and 8.57% by weight of condensed azo yellow) was mixed with a polyamide elastomer (Griflex ELG6260, manufactured by EMS) to obtain a mixture so that the blending amount was 5% by weight. The mixture and a polyamide elastomer (Griflex ELG5660, manufactured by EMS) were mixed in a weight ratio of 7:3 to prepare tip material 2.
- DAIREN ORANGE PPD-3865 manufactured by DIC, containing 8.57% by weight of perylene red and 8.57% by weight of condensed azo yellow
- Griflex ELG6260 manufactured by EMS
- Shaft inner layer material A pigment (DAIREN BLACK PPB-0491, manufactured by DIC Corporation, containing 25% by weight of carbon black) was blended with polyamide (DAIAMID (registered trademark) L1940W, manufactured by Polypla-Evonik Co., Ltd.) to give a blending amount of 20% by weight to prepare shaft inner layer material 2.
- DAIREN BLACK PPB-0491 manufactured by DIC Corporation, containing 25% by weight of carbon black
- polyamide DAIAMID (registered trademark) L1940W, manufactured by Polypla-Evonik Co., Ltd.
- Polyamide Diamid (registered trademark) L1940W, manufactured by Polypla Evonik Co., Ltd.
- Grilflex ELG6260 manufactured by EMS Co., Ltd.
- Shaft A shaft tube 2 was formed by co-extrusion of the shaft inner layer material and the shaft outer layer material.
- the tip tube 2 and the shaft tube 2 were inserted into the core material, and passed through the hollow elastic body with both tubes butted against each other.
- the inner diameter of the hollow elastic body was larger than the outer diameter of the workpiece, and the workpiece and the hollow elastic body were not in contact before pressing.
- Both tubes (workpiece) were rotated around the axis of the core material, and an external force was applied to the hollow elastic body while laser light was irradiated, thereby applying a radially inward force to the workpiece and heating the parts irradiated with the laser light.
- the temperature of the tip and the inner layer of the shaft which were blended with a laser light absorbing material, rose earlier than the other parts.
- Balloon catheter 2 The catheter 2 with a tip manufactured in 4-1 above was inserted into the core material, and the planned welding position of the tip of the balloon 2 was arranged so as to straddle the boundary between the tip and the shaft.
- the hollow elastic body was passed through the elastic body so as to cover the planned welding position.
- the inner diameter of the hollow elastic body was larger than the outer diameter of the workpiece, and the workpiece and the hollow elastic body were not in contact before pressing.
- the workpiece was rotated around the axis of the core material, and the elastic body was pressurized from the outside and irradiated with laser light, so that a radially inward force was applied to the workpiece and the member irradiated with the laser light was heated.
- the balloon catheter 2 of the embodiment had a structure as shown in Figure 5.
- the tip of the shaft (or the inner layer of the shaft) draws an arc and sinks from the inner surface of the tip tip radially outward. This increases the contact area with the adjacent resin, and it is believed that a necessary and sufficient bonding strength can be obtained even with a short fusion length. It is believed that a short fusion length results in a flexible tip.
- the crystallinity at the tip end of the balloon tip (43.2%) was lower than the crystallinity at the base end of the balloon tip (45.0%).
- the crystallinity at the tip end of the balloon tip was approximately 1.8% lower than the crystallinity at the base end of the balloon tip. This results in a gradual change in hardness from the tip to the base end, resulting in gradient physical properties that contribute to improved permeability within the body and are thought to maintain flexibility against bending near the fused area.
- 3 balloon catheter, 3A the tip of the balloon catheter; 10, 110 shaft, 130 Elastic body, 20, 320 tip member, 150 core material, 320H Inner surface of tip member; 60 balloons, 60A: balloon tip 60A1: wedge portion, 60A2 Parallel section, 60D balloon tip, 65 proximal end of balloon; 66 balloon inner layer, 67 balloon base layer, 68 outer layer of the balloon; 69 Mixed layer, 270 X-ray contrast markers, 280 guide wire, 310 shaft, 310H Shaft bore, 311 outer tube shaft, 311A: tip of outer tube shaft; 311H outer tube shaft bore, 312 Inner tube shaft, 312A: tip of inner tube shaft; 312R: Proximal end opening of inner tube shaft; 313 outer layer of inner tube shaft; 313A: the tip of the outer layer of the inner tube shaft; 314 Inner layer of inner tube shaft; 314A: distal end of inner layer of inner tube shaft; 315: guidewire lumen; 340 Hub, 341 Hub port.
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Abstract
Description
(1)軸方向に延在するシャフトと、前記シャフトの外周に配置されるバルーンと、を有し、前記バルーン先端部の先端側の結晶性が基端側の結晶性よりも低い、バルーンカテーテルである。
(2)上記(1)のバルーンカテーテルでは、前記バルーン先端部の先端側の結晶性は、基端側から先端側に向けて徐々に低くなることが好ましい。
(3)上記(1)または(2)のバルーンカテーテルでは、前記バルーン先端部の前記先端側の結晶性は、前記基端側と比較して1.5~6%低いことが好ましい。
(4)上記(1)~(3)のいずれかに記載のバルーンカテーテルでは、前記軸方向の断面視において、前記バルーンの前記先端部は、楔形状を備える楔部を有し、前記楔部は、前記軸方向と平行な平行部を有することが好ましい。
(5)上記(4)のバルーンカテーテルでは、前記バルーンが内層、基材層および外層を有し、前記平行部における前記外層の結晶性は、前記内層の結晶性よりも低いことが好ましい。
(6)上記(5)のバルーンカテーテルでは、前記内層および外層がエラストマーを含むことが好ましい。
(7)上記(1)~(6)のいずれかに記載のバルーンカテーテルでは、前記シャフトの先端側に融着され、前記シャフトよりも柔軟な先端部材を含み、前記先端部材の基端部と、前記バルーン先端部の先端領域の結晶性が各々40%未満であることが好ましい。
(8)上記(1)~(7)のいずれかに記載のバルーンカテーテルでは、前記シャフトと融着している部分に位置する前記バルーンの先端における厚さは、前記バルーンが前記シャフトに接合している部分よりも基端側に隣接する部位における前記シャフトの厚みと同等かそれよりも小さく、かつ、前記バルーンと接合している部分の前記シャフトの厚みよりも大きいことが好ましい。
測定法:顕微透過法
測定範囲:700μm角(128ピクセル角)
素子サイズ:5.5μm角
積算:128回
スペクトル分解能:4cm-1
前処理:試料をエポキシ樹脂に包埋し、ミクロトームで厚さ約10μmの薄片に加工する。
Lnは、リンカー部位であり、-C(O)-R-C(O)-であり、
前記Rは、メチレン数が2~12からなるアルキレン基であり、メチレン数が4~10からなるアルキレン基が好ましい。)
Lnは、リンカー部位であり、-C(O)-R-C(O)-であり、
前記Rは、メチレン数が2~12からなるアルキレン基であり、メチレン数が4~10からなるアルキレン基が好ましい。)
からなる群から選択される少なくとも1種を含むことがより好ましい。
以下、本発明に係るバルーンカテーテルの製造方法の好ましい実施形態について説明する。
シャフト10および先端部材20を、芯材150に挿通する。これにより、シャフト10と先端部材20は芯材150と一体的に移動可能および回転可能になる。芯材は、例えば金属製である。
次いで、シャフトおよび先端部材の接触部を径方向に加圧する。加圧方法としては特に限定されないが、例えば、中空円筒状の加圧部材を用いることができる。中空円筒状の加圧部材によれば、芯材、弾性体と同様に、軸方向を回転軸として回転可能に支持されるように構成される。そして、かような形状の加圧部材の中空部に、弾性体を挿入することができる。この際、弾性体を軸方向に延伸させ、加圧部材の内径より弾性体の直径を小さくすることで、弾性体を加圧部材の中空部に挿入することができる。さらに、加圧部材の中空部内に弾性体を配置した後に軸方向への伸長を解除する 。加圧部材の内径は、弾性体の直径(外径)より小さいことが好ましい。このように弾性体の外径と、加圧部材の内径を設計することで、伸長を解除した際に、加圧部材に弾性体が接触することとなり、径方向内側に外圧が付与されることとなる。なお、外力付与の形態は上記形態に限定されず、例えば直方体形状の加圧部材を径方向に弾性体に接触させることで、弾性体を径方向に加圧してもよい。また、別の態様として、加圧部材の中空部の内容積を減少させることで弾性体を径方向に加圧する。これによって、加圧部材の内周から弾性体を通してカテーテルシャフトと先端部材の外周へ実質的に均一な力が作用できる。
1.材料
1-1.先端チップ用材料
ポリアミドエラストマー(PEBAX7033SA01MED、アルケマ社製)とポリアミドエラストマー(ベスタミドE40-S1、ポリプラ・エボニック社製)とを8:2(重量比)で混合して混合物を得た。配合量が0.7重量%となるように顔料(DAIREN BLUE NPN-4970、DIC社製、フタロシアニンブルー33.30重量%、カーボンブラック1.72重量%含有)を混合物に配合して、先端チップ用材料を作製した。
配合量が5重量%となるようにカーボンナノチューブ(MWNT-7、保土谷化学工業社製)をポリアミド(Grilamid L16、EMS社製)に配合してシャフト内層用材料を作製した。
ポリアミドエラストマー(Grilflex ELG6260、EMS社製)とポリアミド(Rilsamid AESN O TL、アルケマ社製)とを3:7(重量比)で混合して、シャフト外層用材料を作製した。
バルーン内層および外層用材料として、ポリアミドエラストマー(Grilflex ELG5660、EMS社製)を使用した。バルーン中層(基材層)用材料として、ポリアミド(Grilamid L25、EMS社製)を使用した。いずれもレーザー光吸収材料を含まない透明な部材であった。
2-1.先端チップ
先端チップ用材料を加熱しながら押し出して先端チップ用チューブを成形した。
シャフト内層用材料とシャフト外層用材料とを共押出しによりシャフト用チューブを成形した。
バルーン内層用材料、バルーン中層用材料およびバルーン外層用材料を加熱しながら共押出しでチューブに成形後、二軸延伸にてバルーン形状に成形した。
3-1.レーザー加工機
レーザー照射部は、輻射加熱により融着部を発熱させる波長のレーザー光を照射する。レーザー光のスポット径は、φ0.1~φ10mmに構成でき、レーザー光の波長は、800~10000nmに構成できる。レーザー光の波長は、それらの範囲から加工対象物に応じて適宜選択した。レーザー光吸収性材料が配合された部材同士の融着の場合は、800~5000nm、好ましくは900~2300nmの中から選択できる。透明部材同士やレーザー光吸収性材料が配合された部材と透明部材の融着の場合は、1300~2500nm、好ましくは1500~2300nmの中から選択できる。レーザー光は、基本的に加工対象物の軸方向に対して直交する方向に照射する。レーザー光は、加工対象物によって適宜角度を変えて照射してもよい。
シリコーン製の中空弾性体に外力を与えることにより、中空弾性体が加工対象物を押圧する。シリコーン製の中空弾性体は、レーザー光透過性を有する。レーザー光透過性とは、加工対象物の径方向の厚さが1mmにつきレーザー光に対する透過率80%以上の材料にて構成することを意味する。加工対象物は、金属製芯材を通されて、中空弾性体により芯材の軸方向に向かって加圧される。加工対象物、芯材、中空弾性体及びその支持物が芯材の軸を中心に回転する。
4-1.先端チップ付きカテーテル
先端チップ用チューブとシャフト用チューブを芯材に挿通し、両チューブを突き合せた状態で中空弾性体内に通した。中空弾性体の内径は、加工対象物の外径より大きく、加工対象物と中空弾性体とは押圧前には接していない。両チューブ(加工対象物)を芯材の軸を中心に回転させ、中空弾性体に外力を与えるとともにレーザー光を照射することにより、加工対象物に径方向内向きの力を加えると共にレーザー光が照射された部分の部材を加熱した。特にレーザー光吸収性の材料が配合された先端チップとシャフトの内層は他の部材よりも先に部材の温度が上昇した。所定の時間経過後にレーザー光照射と中空弾性体による加圧を停止した。加工対象物の熱が取れたところで芯材から外した。このようにして、先端チップ付きカテーテル(内径:0.41mm、外径:0.58mm)を作製した。
上記4-1にて製造した先端チップ付カテーテルを芯材に挿通し、バルーンの先端の溶着予定位置を先端チップとシャフトの境界部分を跨ぐように配置した。中空弾性体が溶着予定位置を覆うように弾性体内に通した。中空弾性体の内径は、加工対象物の外径より大きく、加工対象物と中空弾性体とは押圧前には接していない。加工対象物を芯材の軸を中心に回転させ、弾性体を外部から加圧するとともにレーザー光を照射することにより、加工対象物に径方向内向きの力が加わると共にレーザー光が照射された部分の部材が加熱された。特にレーザー光吸収性の材料が配合された先端チップとシャフトの内層は他の部材よりも先に部材の温度が上昇した。所定の時間経過後にレーザー光照射と中空弾性体による加圧を停止した。加工対象物の熱が取れたところで芯材から外した。このようにして、バルーンカテーテル(内径:0.41mm、外径:0.57mm)を作製した。
1.結晶バンド及び非晶バンドの選定
1-1.条件
装置名:アジレントテクノロジー社製FTS7000e/赤外顕微鏡UMA600
測定法:顕微透過法
積算:128回
分解能:4cm-1
温度条件:室温から230℃まで昇温してIR測定し、その後に十分に結晶化が生じる速度で室温まで徐冷した後にIR測定した。なお、IR測定は窒素中で行った。
樹脂2:ポリアミドエラストマー(Grilflex ELG5660、EMS社製:バルーン内層および外層用材料)のペレット
樹脂3:ポリアミド(Grilamid L25、EMS社製:バルーン中層用材料)のペレット
樹脂4:シャフト外層用材料からなるチューブ
樹脂5:シャフト内層用材料からなるチューブ
チューブは、各樹脂を加熱しながら押し出して成形した。
樹脂1~5を用いて以下のように波長に対する吸光度を測定し、結晶バンドおよび非晶バンドを選定した。
・樹脂1(先端チップ)
1)樹脂1(チューブ状)をカッターで10μmの薄片に加工した。
2)上記薄片を230℃に加熱・冷却した溶融前後のIRスペクトル(図7)より、結晶バンド(溶融上では消失するバンド)として13本(C1からC13)を確認した(図7上段)。結晶性の評価に使用するバンドは、ピークの重なりやベースラインの変動がすくないC9を選定した。
3)非晶バンド(溶融状態でも残存するバンド)として5本(A1からA5)を確認した(図7下段)。結晶性の評価に使用するバンドは、ピークの重なりやベースラインの変動が少ないA3を選定した。
4)結晶性の評価は、結晶バンドC9と非晶バンドA3のピーク強度比を指標とした。
・樹脂2(バルーン内層および外層)
1)樹脂2(ペレット状)をミクロトームで10μmの薄片に加工した。
2)上記薄片を230℃に加熱・冷却した溶融前後のIRスペクトル(図8)より、結晶バンド(溶融上では消失するバンド)として11本(C1からC11)を確認した(図8上段)。結晶性の評価に使用するバンドは、ピークの重なりやベースラインの変動がすくないC7を選定した。
3)非晶バンド(溶融状態でも残存するバンド)として5本(A1からA5)を確認した(図8下段)。結晶性の評価に使用するバンドは、ピークの重なりやベースラインの変動が少ないA3を選定した。
4)結晶性の評価は、結晶バンドC7と非晶バンドA3のピーク強度比を指標とした。
・樹脂3(バルーン中層)
1)樹脂3(ペレット状)をミクロトームで10μmの薄片に加工した。
2)上記薄片を230℃に加熱・冷却した溶融前後のIRスペクトル(図9)より、結晶バンド(溶融上では消失するバンド)として13本(C1からC13)を確認した(図9上段)。結晶性の評価に使用するバンドは、ピークの重なりやベースラインの変動がすくないC7を選定した。
3)非晶バンド(溶融状態でも残存するバンド)として7本(A1からA7)を確認した(図9下段)。結晶性の評価に使用するバンドは、ピークの重なりやベースラインの変動が少ないA3を選定した。
4)結晶性の評価は、結晶バンドC7と非晶バンドA3のピーク強度比を指標とした。
・樹脂4(シャフト外層)
1)樹脂4(チューブ状)をカッターで10μmの薄片に加工した。
2)上記薄片を230℃に加熱・冷却した溶融前後のIRスペクトル(図10)より、結晶バンド(溶融上では消失するバンド)として13本(C1からC13)を確認した(図10上段)。結晶性の評価に使用するバンドは、ピークの重なりやベースラインの変動がすくないC7を選定した。
3)非晶バンド(溶融状態でも残存するバンド)として6本(A1からA6)を確認した(図10下段)。結晶性の評価に使用するバンドは、ピークの重なりやベースラインの変動が少ないA3を選定した。
4)結晶性の評価は、結晶バンドC7と非晶バンドA3のピーク強度比を指標とした。
・樹脂5(シャフト内層)
1)樹脂5(チューブ状)をカッターで10μmの薄片に加工した。
2)上記薄片を230℃に加熱・冷却した溶融前後のIRスペクトル(図11)より、結晶バンド(溶融上では消失するバンド)として13本(C1からC13)を確認した(図11上段)。結晶性の評価に使用するバンドは、ピークの重なりやベースラインの変動がすくないC7を選定した。
3)非晶バンド(溶融状態でも残存するバンド)として7本(A1からA7)を確認した(図11下段)。結晶性の評価に使用するバンドは、ピークの重なりやベースラインの変動が少ないA3を選定した。
4)結晶性の評価は、結晶バンドC7と非晶バンドA3のピーク強度比を指標とした。
2-1.条件
装置名:アジレントテクノロジー製Cary600/赤外顕微鏡Cary670
測定法:顕微透過法
測定範囲:700μm角(128ピクセル角)
素子サイズ:5.5μm角
積算:128回
スペクトル分解能:4cm-1
前処理:試料をエポキシ樹脂に包埋し、ミクロトームで厚さ約10μmの薄片に加工した。
1)上記で作製したバルーンカテーテル(実施例)と、上記実施例と同じ材料を特開2001-191412号公報に記載の方法にて作製したバルーンカテーテル(比較例)をそれぞれ試料として準備した。
2)先端チップからバルーンとシャフトが融着されている部分までが測定範囲になるように上記前処理をした薄片を作製した。
3)上記1-2にて特定した結晶バンドと非晶バンドとをピクセル毎に測定し、試料厚みのバラツキの影響を抑えるために非晶バンドを分母、結晶バンドを分子としてその比をその試料の「結晶性」として算出した(式1)。試料の結晶性分布を明確にするためにカラー画像とした。上記1-2にて特定した各樹脂の結晶バンドと非晶バンドは次のように選定した。結晶バンドは各樹脂共通の1161cm-1を選定した。非晶バンドは、溶融時(図7~11下段)は1366から1359cm-1と幅があったが、冷却後(図7~11上段)のバンドはほぼ1369cm-1であったために非晶バンドを1369cm-1とした。
イメージングIRによるバルーンカテーテル軸方向の結晶性分布の測定結果を図12に示す。図12以降の測定結果は、バルーンカテーテルの先端部の径方向の片側を表している。図12において、比較例のバルーンカテーテルにおけるバルーン先端(左側)およびシャフト先端(右側)を矢印にて示す。図12において、左下がバルーンカテーテルの先端側であり、右上がバルーンカテーテルの基端側である。また、図12において、結晶性は、色で表現され、赤(約60%)、橙色、黄色、緑、水色、青、紫(0%)へと連続的に移り変わっている。
1.片持ち曲げ試験
1-1.条件
速度:5mm/min
挟む治具と板の距離:0.5mm
ストローク:0.3mm
測定箇所:先端チップ(B部を治具に挟んで、A部に板を押し込む)
融着しろ(C部を治具に挟んで、B部に板を押し込む)。
B部:先端チップ(青色)とシャフト(黒色)との界面
A部:B部から先端側に0.5mm
C部:B部から基端側に0.5mm。
先端チップ:B点(0.0054/0.0039)
融着しろ:C点(0.0159/0.0116)。
片持ち曲げ試験の結果を図15に示す。
1.材料
1-1.先端チップ用材料2
配合量が5重量%となるように顔料(DAIREN ORANGE PPD-3865、DIC社製、ペリレンレッド8.57重量%、縮合アゾイエロー8.57重量%含有)をポリアミドエラストマー(Griflex ELG6260、EMS社製)に配合して混合物を得た。混合物とポリアミドエラストマー(Griflex ELG5660、EMS社製)とを7:3(重量比)で混合して、先端チップ用材料2を作製した。
配合量が20重量%となるように顔料(DAIREN Black PPB-0491、DIC社製、カーボンブラック25重量%含有)をポリアミド(ダイアミド(登録商標)L1940W、ポリプラ・エボニック株式会社製)に配合してシャフト内層用材料2を作製した。
ポリアミド(ダイアミド(登録商標)L1940W、ポリプラ・エボニック株式会社製)とポリアミドエラストマー(Grilflex ELG6260、EMS社製)とを8:2(重量比)で混合して、シャフト外層用材料2を作製した。
バルーン内層用材料2および外層用材料2として、ポリアミドエラストマー(Grilflex ELG6260、EMS社製)を使用した。バルーン中層(基材層)用材料2として、ポリアミド(Grilamid L25、EMS社製)を使用した。いずれもレーザー光吸収材料を含まない透明な部材であった。
2-1.先端チップ
先端チップ用材料2を加熱しながら押し出して先端チップ用チューブ2を成形した。
シャフト内層用材料とシャフト外層用材料とを共押出しによりシャフト用チューブ2を成形した。
バルーン内層用材料、バルーン中層用材料およびバルーン外層用材料を加熱しながら共押出しでチューブに成形後、二軸延伸にてバルーン2を成形した。
レーザー加工機および加圧装置は、上記先端チップ付きカテーテルおよびバルーンカテーテルの作製と同様の融着装置を使用した。
先端チップ用チューブ2とシャフト用チューブ2を芯材に挿通し、両チューブを突き合せた状態で中空弾性体内に通した。中空弾性体の内径は、加工対象物の外径より大きく、加工対象物と中空弾性体とは押圧前には接していない。両チューブ(加工対象物)を芯材の軸を中心に回転させ、中空弾性体に外力を与えるとともにレーザー光を照射することにより、加工対象物に径方向内向きの力を加えると共にレーザー光が照射された部分の部材を加熱した。特にレーザー光吸収性の材料が配合された先端チップとシャフトの内層は他の部材よりも先に部材の温度が上昇した。所定の時間経過後にレーザー光照射と中空弾性体による加圧を停止した。加工対象物の熱が取れたところで芯材から外した。このようにして、先端チップ付きカテーテル2(内径:0.41mm、外径:0.58mm)を作製した。
上記4-1にて製造した先端チップ付カテーテル2を芯材に挿通し、バルーン2の先端の溶着予定位置を先端チップとシャフトの境界部分を跨ぐように配置した。中空弾性体が溶着予定位置を覆うように弾性体内に通した。中空弾性体の内径は、加工対象物の外径より大きく、加工対象物と中空弾性体とは押圧前には接していない。加工対象物を芯材の軸を中心に回転させ、弾性体を外部から加圧するとともにレーザー光を照射することにより、加工対象物に径方向内向きの力が加わると共にレーザー光が照射された部分の部材が加熱された。特にレーザー光吸収性の材料が配合された先端チップとシャフトの内層は他の部材よりも先に部材の温度が上昇した。所定の時間経過後にレーザー光照射と中空弾性体による加圧を停止した。加工対象物の熱が取れたところで芯材から外した。このようにして、バルーンカテーテル2(内径:0.41mm、外径:0.57mm)を作製した。
上記バルーンカテーテルと同様の方法により、バルーンカテーテル2の結晶性を評価した。
3A バルーンカテーテルの先端部、
10、110 シャフト、
130 弾性体、
20、320 先端部材、
150 芯材、
320H 先端部材の内表面、
60 バルーン、
60A バルーンの先端部
60A1 楔部、
60A2 平行部、
60D バルーンの先端、
65 バルーンの基端部、
66 バルーンの内層、
67 バルーンの基材層、
68 バルーンの外層、
69 混和層、
270 X線造影マーカー、
280 ガイドワイヤ、
310 シャフト、
310H シャフトの内腔、
311 外管シャフト、
311A 外管シャフトの先端部、
311H 外管シャフトの内腔、
312 内管シャフト、
312A 内管シャフトの先端部、
312R 内管シャフトの基端開口部、
313 内管シャフトの外層、
313A 内管シャフトの外層の先端部、
314 内管シャフトの内層、
314A 内管シャフトの内層の先端部
315 ガイドワイヤルーメン、
340 ハブ、
341 ハブのポート。
Claims (8)
- 軸方向に延在するシャフトと、
前記シャフトの外周に配置されるバルーンと、を有し、
前記バルーン先端部の先端側の結晶性が基端側の結晶性よりも低い、バルーンカテーテル。 - 前記バルーン先端部の結晶性が、基端側から先端側に向けて徐々に低くなる、請求項1に記載のバルーンカテーテル。
- 前記バルーン先端部の前記先端側の結晶性は、前記基端側と比較して1.5~6%低い、請求項1または2に記載のバルーンカテーテル。
- 前記軸方向の断面視において、
前記バルーン先端部は、
楔形状を備える楔部を有し、
前記楔部は前記軸方向と平行な平行部を有する、請求項1または2に記載のバルーンカテーテル。 - 前記バルーンが内層、基材層および外層を有し、
前記平行部における前記外層の結晶性は、前記内層の結晶性よりも低い、請求項4に記載のバルーンカテーテル。 - 前記内層および前記外層がエラストマーを含む、請求項5に記載のバルーンカテーテル。
- 前記シャフトの先端側に融着され、前記シャフトよりも柔軟な先端部材を含み、前記先端部材の基端部と、前記バルーン先端部の先端領域の結晶性が各々40%未満である、請求項1または2に記載のバルーンカテーテル。
- 前記シャフトと融着している部分に位置する前記バルーンの先端における厚さは、前記バルーンが前記シャフトに接合している部分よりも基端側に隣接する部位における前記シャフトの厚みと同等かそれよりも小さく、かつ、前記バルーンと接合している部分の前記シャフトの厚みよりも大きい、請求項1または2に記載のバルーンカテーテル。
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| JPS5919582A (ja) | 1982-07-09 | 1984-02-01 | マルコス・ピネル・ヒメネス | 磁気共鳴による液体精製システム |
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| JP2012143381A (ja) * | 2011-01-12 | 2012-08-02 | Goodman Co Ltd | カテーテル及びカテーテルの製造方法 |
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| JP2022020124A (ja) * | 2020-07-20 | 2022-02-01 | 朝日インテック株式会社 | バルーンカテーテル |
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| US4963313A (en) * | 1987-11-30 | 1990-10-16 | Boston Scientific Corporation | Balloon catheter |
| US5316706A (en) * | 1992-08-05 | 1994-05-31 | Advanced Cardiovascular Systems | Method of manufacturing jointless catheter |
| US7727442B2 (en) * | 2003-07-10 | 2010-06-01 | Boston Scientific Scimed, Inc. | Medical device tubing with discrete orientation regions |
| WO2005065735A1 (en) * | 2003-12-31 | 2005-07-21 | Boston Scientific Limited | Medical device with varying physical properties and method for forming same |
| US8500797B2 (en) * | 2004-09-08 | 2013-08-06 | Boston Scientific Scimed, Inc. | Medical devices |
| US11684748B2 (en) * | 2017-12-27 | 2023-06-27 | Kaneka Corporation | Catheter and method for producing same |
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2023
- 2023-09-26 WO PCT/JP2023/034940 patent/WO2024071117A1/ja not_active Ceased
- 2023-09-26 EP EP23872340.7A patent/EP4582130A4/en active Pending
- 2023-09-26 JP JP2024549423A patent/JPWO2024071117A1/ja active Pending
-
2025
- 2025-03-14 US US19/080,063 patent/US20250213829A1/en active Pending
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| US4100309A (en) | 1977-08-08 | 1978-07-11 | Biosearch Medical Products, Inc. | Coated substrate having a low coefficient of friction hydrophilic coating and a method of making the same |
| JPS5919582A (ja) | 1982-07-09 | 1984-02-01 | マルコス・ピネル・ヒメネス | 磁気共鳴による液体精製システム |
| JPH05192410A (ja) | 1991-09-16 | 1993-08-03 | Cook Inc | バルーンカテーテル |
| JPH1024098A (ja) * | 1996-07-10 | 1998-01-27 | Terumo Corp | バルーン及びバルーンカテーテル |
| JP2001191412A (ja) | 2000-01-11 | 2001-07-17 | Asahi Intecc Co Ltd | 熱溶融性合成樹脂の溶着方法 |
| JP2005538744A (ja) * | 2001-10-24 | 2005-12-22 | ボストン サイエンティフィック リミテッド | バルーンの先端くびれ部の材料レリーフ及び製造方法 |
| JP2005160536A (ja) | 2003-11-28 | 2005-06-23 | Nippon Sherwood Medical Industries Ltd | バルーンカテーテル |
| JP2012143381A (ja) * | 2011-01-12 | 2012-08-02 | Goodman Co Ltd | カテーテル及びカテーテルの製造方法 |
| WO2013111700A1 (ja) * | 2012-01-23 | 2013-08-01 | テルモ株式会社 | 医療用チューブ、カテーテルおよび医療用チューブの製造方法 |
| JP2017055859A (ja) * | 2015-09-15 | 2017-03-23 | 朝日インテック株式会社 | バルーンカテーテル |
| JP2020039376A (ja) * | 2017-01-23 | 2020-03-19 | テルモ株式会社 | バルーンカテーテル |
| JP2022020124A (ja) * | 2020-07-20 | 2022-02-01 | 朝日インテック株式会社 | バルーンカテーテル |
| JP2022156478A (ja) | 2021-03-31 | 2022-10-14 | 住友大阪セメント株式会社 | セメント組成物、及び、セメント組成物の製造方法 |
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| EP4591915A1 (en) * | 2024-01-29 | 2025-07-30 | TERUMO Kabushiki Kaisha | Balloon catheter |
Also Published As
| Publication number | Publication date |
|---|---|
| US20250213829A1 (en) | 2025-07-03 |
| EP4582130A4 (en) | 2025-12-10 |
| EP4582130A1 (en) | 2025-07-09 |
| JPWO2024071117A1 (ja) | 2024-04-04 |
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