JP6558141B2 - Method for manufacturing stent delivery catheter and method for moving self-expandable stent between tubes - Google Patents

Description

  The present invention relates to a method for manufacturing a stent delivery catheter used for placing a medical stent in the body and a method for moving a self-expandable stent between tubes.

  For example, a medical method of placing a stent in a digestive tract where a lesion is present or a body lumen such as a blood vessel causing arteriosclerosis for the purpose of ensuring the patency of the stenosis is known. . The stent is transported to an indwelling position in the body lumen in a reduced diameter state using a medical catheter called a stent delivery catheter. Further, the stent is placed in the body by being moved out of the lumen of the stent delivery catheter at the indwelling position. In the case of a balloon expandable stent, the stent that has been moved out of the lumen is expanded in the indwelling position by expanding the balloon inside the stent, or in the case of a self-expanding stent, by expanding itself. .

  The manufacturing process of the stent delivery catheter includes a step of reducing the diameter of the stent and a step of moving the reduced diameter stent into the lumen of the stent delivery catheter (see Patent Document 1).

JP 2012-29981 A

  Conventionally, in the step of reducing the diameter of the stent, the stent is reduced in diameter using a crimping head having a receiving cavity whose diameter is changed by a mechanical operation, so that the force for reducing the diameter of the stent may be concentrated on a part. is there. When the force for reducing the diameter of the stent is concentrated on a part, the stent may be locally deformed, and such a local deformation has a problem of preventing smooth movement of the stent in a later process. Further, in the process of moving the reduced diameter stent into the lumen of the catheter, the crimping head is pressed against the catheter, which causes the catheter lumen to bend, thereby hindering the smooth movement of the stent.

  The present invention has been made in view of such a situation, and a stent delivery catheter manufacturing method capable of smoothly moving a stent into a catheter lumen, and intertube movement of a self-expanding stent used in such a manufacturing method. Regarding the method.

In order to achieve the above object, a method for producing a stent delivery catheter according to the present invention comprises:
Inserting the stent into the stock lumen of the stock tube;
A diameter reducing step of reducing the diameter of the stent in the stock lumen by deforming the stock tube and reducing the diameter of the stock lumen;
Moving the reduced diameter stent from the stock lumen of the stock tube to the catheter lumen of the catheter tube.

  In the method for manufacturing a stent delivery catheter according to the present invention, a stent is inserted into a stock tube, and the stock tube is deformed to reduce the diameter of the stent. Therefore, a force for reducing the diameter of the stent is uniformly applied to the stent. It is possible. Therefore, according to such a manufacturing method, the problem which a local deformation | transformation produces in a stent in a diameter reduction process is prevented, and the smooth movement of the stent in a subsequent movement process is implement | achieved.

  Further, for example, in the diameter reducing step, the diameter reduction jig in which a through hole having an inner diameter smaller than the outer diameter of the stock tube before deformation is formed, and the stock tube before deformation into which the stent is inserted is used. The stock tube may be deformed by passing through the through hole.

  By deforming the stock tube in this manner, it is possible to more uniformly apply a force for reducing the diameter of the stent to the stent, and it is possible to effectively prevent a problem that the stent is locally deformed.

In addition, for example, the movement of the stent in the moving step is performed by a first jig in which a first insertion hole inserted through the end of the stock tube is formed and a first jig inserted through the end of the catheter tube. Using a second jig in which two insertion holes are formed, the stock tube and the catheter tube may be connected so that the stock lumen and the catheter lumen are connected.
The opening diameter of one opening in the second insertion hole and facing the first jig is smaller than the outer diameter of the arranged stock tube, and the stock lumen in the arranged stock tube It may be larger than the diameter.

  According to the manufacturing method having such a moving step, even when a force toward the catheter lumen is generated with respect to the stock tube during the moving step, the force is applied to the end of the stock tube. It is received by 2 jigs. Therefore, it is possible to prevent a force from being transmitted from the stock tube to the catheter tube, and it is possible to prevent the problem that the catheter lumen is bent by the force and the smooth movement of the stent is inhibited.

A method for moving between tubes of a self-expanding stent according to the present invention includes:
A self-expandable stent-to-tube movement method for moving a self-expandable stent housed in a first lumen of a first tube to a second lumen of a second tube,
The 1st jig | tool in which the 1st penetration hole penetrated by the edge part of the said 1st tube is formed, and the 2nd jig | tool in which the 2nd penetration hole penetrated by the edge part of the said 2nd tube is formed. The stent is moved in a state where the first tube and the second tube are arranged so that the first lumen and the second lumen are connected to each other.
An opening diameter of one opening in the second insertion hole and facing the first jig is smaller than an outer diameter of the first tube and larger than a diameter of the first lumen. To do.

  When the self-expanding stent is moved from the first tube to the second tube, the stent is moved by connecting the first lumen and the second lumen, but the first tube and the second tube are brought into strong contact with each other. Then, the second tube and the second lumen may be bent, and the smooth movement of the stent may be hindered. However, according to the method of the present invention, the force that moves the end of the first tube toward the second tube in accordance with the moving operation of the stent is received by the second jig. Therefore, excessive contact between the first tube and the second tube is prevented, and the problem that the second lumen into which the stent is inserted is bent and hinders the smooth movement of the stent can be effectively prevented.

FIG. 1 is a schematic view of a stent delivery catheter manufactured by a manufacturing method according to an embodiment of the present invention. FIG. 2 is a schematic perspective view showing a stent housed in the stent delivery catheter shown in FIG. FIG. 3 is a flowchart showing manufacturing steps included in a method for manufacturing a stent delivery catheter according to an embodiment of the present invention. FIG. 4 is a schematic cross-sectional view illustrating a second diameter reduction process of the stent. FIG. 5 is a cross-sectional view illustrating a stent moving process. FIG. 6 is an enlarged view of a part of FIG. FIG. 7 is a schematic diagram showing a first diameter reducing device used in the first diameter reducing process.

  Hereinafter, the manufacturing method of the stent delivery catheter concerning one embodiment of the present invention is explained in detail based on the embodiment shown in a drawing.

  FIG. 1 is a schematic view of a stent delivery catheter 10 manufactured by a manufacturing method according to an embodiment of the present invention. The stent delivery catheter 10 has a catheter tube 12 that is inserted into a patient's body. The catheter tube 12 has a tube shape in which a catheter lumen 12a (see FIG. 5) is formed, and a stent 14 is accommodated in the catheter lumen 12a.

  An operation portion 16 for operating the catheter tube 12 and the stent 14 from outside the patient's body is connected to the proximal end of the catheter tube 12. The stent delivery catheter 10 is a medical instrument that is used to transport the stent 14 to an indwelling position in a patient's body and to place the stent 14 in the indwelling position. For example, the user of the stent delivery catheter 10 inserts the distal end of the catheter tube 12 to the indwelling position of the stent 14, and then operates the operation unit 16 outside the patient's body to remove the stent 14 from the catheter lumen 12 a. Release and place the stent 14 in the patient's body.

  In the stent delivery catheter 10, an inner tube (not shown) thinner than the catheter tube 12 is inserted into the catheter lumen 12 a, and the inner tube is inserted into the stent 14. The user of the stent delivery catheter 10 can expose the inner tube and the stent 14 from the distal end of the catheter tube 12 by operating the operation unit 16 and release the stent 14 from the catheter lumen 12a. However, in the stent delivery catheter 10, the method for releasing the stent 14 from the catheter lumen 12a is not particularly limited, and other methods may be adopted.

  The material of the catheter tube 12 is not particularly limited, but the catheter tube 12 is preferably manufactured using a flexible synthetic resin material. As a material of the catheter tube 12, for example, an elastomer such as a polyamide elastomer, a polyester elastomer, a polyurethane elastomer, a polystyrene elastomer, or a fluorine elastomer, or a rubber such as silicone rubber or latex rubber can be suitably used. Further, the catheter tube 12 may have a multilayer structure in which a plurality of layers of resin materials of different materials are stacked, or may have a single layer structure of a single material of resin. The operation unit 16 is also made of synthetic resin or the like, but the material is not particularly limited.

  The outer diameter of the catheter tube 12 can be, for example, about 2.5 to 3.5 mm, and the diameter of the catheter lumen 12a (the inner diameter of the catheter tube 12) can be, for example, 2.0 to 3.0 mm. . Moreover, the length of the catheter tube 12 can be 500-2500 mm, for example. However, the dimensions of the catheter tube 12 are appropriately adjusted according to the size of the stent 14 to be transported, the placement position of the stent 14, the size of the body lumen in which the stent 14 is placed, and the like.

  FIG. 2 is a schematic perspective view of the stent 14. The stent 14 has a cylindrical outer shape. The stent 14 is configured by connecting an annular wire having a periodic meandering pattern in the axial direction. The stent 14 is a mesh-like bare stent formed of metal or the like, but the stent 14 is not limited to the bare stent, and is a covered stent in which the bare stent is covered with a resin, or a tube-shaped formed of a resin. It may be a tube stent.

  The material of the stent 14 of the present embodiment is a metal such as nickel titanium (Ni—Ti) alloy, stainless steel, titanium, cobalt chromium alloy, magnesium alloy and the like. Among these, a superelastic alloy such as a nickel titanium alloy is particularly preferable. The stent 14 is a self-expanding stent 14 that expands itself by removing a member that suppresses the expansion of the stent 14 such as the catheter tube 12 that covers the periphery of the stent 14. However, the stent housed in the catheter tube 12 may be a balloon expandable stent that expands as the balloon inserted into the stent expands.

  The outer diameter of the stent 14 in the expanded state can be about 2.0 to 12 mm, for example, and the axial length of the stent 14 can be about 2.0 to 150 mm, for example. However, the dimensions of the stent 14 may be appropriately adjusted according to the size of the indwelling position where the stent 14 is placed and the stenosis state of the body lumen where the stent 14 is placed, and are not particularly limited. Note that the stent 14 shown in FIG. 2 represents the stent 14 in an expanded state (same as before the first diameter reduction described later). Therefore, when the stent 14 is housed in the catheter lumen 12a as shown in FIG. 1, the diameter of the stent 14 is reduced from the state shown in FIG.

  FIG. 3 is a flowchart showing manufacturing steps included in the method for manufacturing the stent delivery catheter 10 according to one embodiment of the present invention. In step S001 of FIG. 3, the stent 14 before the first diameter reduction is prepared, and the first diameter reduction process of the stent 14 is performed.

  The stent 14 before the first diameter reduction is prepared, for example, by laser cutting a nickel titanium alloy pipe that is a material of the stent 14. Furthermore, the prepared stent 14 before the first diameter reduction is reduced in diameter using a first diameter reduction apparatus 80 as shown in FIG. That is, after the stent before the first diameter reduction is set on the holding portion 84 of the first diameter reducing device 80, the holding portion 84 is reduced in diameter by grasping the grip 82 of the first diameter reducing device 80, so The inner stent 14 is reduced in diameter (first reduced diameter).

  Next, in step S002 of FIG. 3, the stent 14 after the first diameter reduction (before the second diameter reduction) is taken out from the holding portion 84 of the first diameter reduction device 80, and then is stored in the stock lumen 22a of the stock tube 22. Inserted. The removal of the stent 14 from the holding portion 84 and the insertion of the stent 14 into the stock lumen 22a are performed by grasping the stent 14 using tweezers or the like and moving the grasped stent 14, for example. In addition, the diameter reduction process (step S001) of the stent 14 by the first diameter reduction apparatus 80 and the process (step S002) of moving the stent 14 from the holding portion 84 to the stock lumen 22a are for preventing or delaying the expansion of the stent 14. In addition, it is preferable that the treatment is performed while the stent 14 is cooled.

  As shown in FIG. 4A, the stock lumen 22a of the stock tube 22 has a diameter larger than the outer diameter of the stent 14 after the first diameter reduction at least at the stage before the second diameter reduction process. . The length of the stock tube 22 is at least longer than the length of the stent 14 so that the entire stent 14 can be accommodated in the stock lumen 22a. The material of the stock tube 22 is not particularly limited. For example, a tube made of polytetrafluoroethylene (PTFE) resin or resin (ETFE) made of a copolymer of tetrafluoroethylene and ethylene can be used as the stock tube 22.

  In step S003 shown in FIG. 3, a second diameter reducing step for reducing the diameter of the stent 14 in the stock tube 22 is performed. In the second diameter reduction step, the stock tube 22 is deformed and the stock lumen 22a is reduced in diameter, thereby reducing the diameter of the stent 14 before the second diameter reduction stored in the stock lumen 22a (second diameter reduction). .

  In step S003, first, as shown in FIG. 4A, the core material 24 for diameter reduction is inserted into the stent 14 so that the stent 14 is inserted in the axial direction. The length of the core material 24 for diameter reduction is longer than the length of the stent 14. The position of the core material for diameter reduction 24 is adjusted in the stock lumen 22 a so that the entire stent 14 is penetrated by the core material for diameter reduction 24.

  Although the material of the core material 24 for diameter reduction is not specifically limited, it can be produced using a hard resin or metal. Moreover, the core material 24 for diameter reduction may be a single layer or a multilayer structure of a resin alone or a metal alone, or may be a multilayer structure combining a resin and a metal. As the diameter-reducing core member 24 having a multilayer structure combining a resin and a metal, for example, a polytetrafluoroethylene (PTFE) resin tube into which a stainless pipe is inserted can be used. The diameter-reducing core member 24 may be a solid rod or a hollow pipe.

  In the second diameter reducing step, the stock tube 22 into which the stent 14 and the diameter reducing core material 24 are inserted is deformed by using the second diameter reducing apparatus 30 shown in FIGS. 4 (a) and 4 (b). The second diameter reducing device 30 includes a diameter reducing jig 32 in which a through hole 32 a is formed, a clamp part 34 that holds one end of the stock tube 22, and a direction in which the clamp part 34 is moved away from the diameter reducing jig 32. And a drive unit 36 to be moved. The drive part 36 may be comprised with the linear motor, and may be comprised with transmission means, such as a rotation motor and the gear which converts the force of a rotation motor into a linear motion.

  The diameter of the through hole 32a formed in the diameter reducing jig 32 is smaller than the outer diameter of the stock tube 22 before being deformed by the second diameter reducing process. Therefore, the stock tube 22 is deformed by passing through the through hole 32 a, and the stock lumen 22 a is reduced in diameter by the second diameter reducing device 30.

  As shown in FIG. 4B, the drive unit 36 moves the clamp 14 that holds one end of the stock tube 22 in a direction away from the diameter-reducing jig 32, so that the stent 14 and the diameter-reduced diameter are reduced. The entire stock tube 22 in which the core material 24 is inserted is pulled, and the through hole 32 a is passed through the stent 14 and the stock tube 22.

  When the stock tube 22 passes through the through hole 32a, the diameter of the stock lumen 22a is reduced as shown in FIG. 4B. Therefore, the stent 14 accommodated in the stock lumen 22a has a reduced diameter that penetrates the stent 14. It is pressed toward the core material 24 to reduce the diameter. By deforming the stock tube 22 in which the stent 14 is accommodated in this manner, a force for reducing the diameter of the stent 14 can be applied to the stent 14 more uniformly. The problem of local deformation in 14 can be effectively prevented.

  In the second diameter reducing step, the number of through-holes 32a through which the stock tube 22 passes may be one or more. When the plurality of through holes 32a are passed through the stock tube 22, the through holes 32a may be arranged in the axial direction, and the plurality of through holes 32a may be passed through one movement. Further, after passing the stock tube 22 through one through hole 32a, the holding of the stock tube 22 by the clamp portion 34 may be once released and passed through the next through hole 32a. When passing through the plurality of through holes 32a, it is preferable that the diameter of the through hole 32a to be passed next is smaller than the diameter of the through hole 32a that has been passed through previously. By making the diameter of the through-hole 32a to pass smaller as it passes later, the diameter of the stent 14 can be reduced stepwise, and the problem of local deformation of the stent 14 can be effectively prevented.

  Further, the deformation that occurs when the stock tube 22 passes through the through hole 32a may be elastic deformation, plastic deformation, or both elastic deformation and plastic deformation. Whether the deformation that occurs when the stock tube 22 passes through the through hole 32a is an elastic deformation or a plastic deformation can be controlled by selecting the material of the stock tube 22. In the embodiment in which the stock tube 22 is plastically deformed by passing through the through-hole 32a, the force that presses the stent 14 against the core material 24 for diameter reduction continues to act even after passing through the through-hole 32a, so that only elastic deformation occurs. It is more preferable than an embodiment using a tube. Further, in the aspect in which the stock tube 22 is plastically deformed by the passage of the through hole 32a and the diameter of the through hole 32a through which the stock tube 22 passes is reduced stepwise, the stock tube 22 may be plastically deformed stepwise. Therefore, the stock lumen 22a and the stent 14 can be suitably reduced in diameter while avoiding breakage of the stock tube 22.

  In step S004 shown in FIG. 3, a moving step of moving the stent 14 from the stock lumen 22a of the stock tube 22 to the catheter lumen 12a of the catheter tube 12 is performed. FIG. 5 is a conceptual diagram showing the movement process of the stent 14.

  The moving process of the stent 14 is performed using a first jig 42 and a second jig 46 as shown in FIG. The first jig 42 is formed with a first insertion hole 42 a that is inserted through the end of the stock tube 22. The diameter of the first insertion hole 42a is substantially the same as or slightly larger than the outer diameter of the stock tube 22 that has undergone the second diameter reduction step, and the stock tube 22 can be inserted through the first insertion hole 42a. .

  The first insertion hole 42a is linear, and the length of the first insertion hole 42a is such that the stent 14 before the second diameter reduction accommodated in the stock tube 22 is positioned inside the first insertion hole 42a. It is preferably longer than the stent 14 before the diameter. However, the length of the first insertion hole 42a is not particularly limited, and may be long enough to accommodate the entire stock tube 22.

  The second jig 46 is used by being connected to the first jig 42 inserted through the stock tube 22. The second jig 46 is formed with a second insertion hole 46 a that is inserted through the end of the catheter tube 12. As shown in FIG. 6, the opposing side opening 46aa, which is one opening of the second insertion hole 46a, faces the first jig 42, and the second insertion hole 46a passes through the opposing side opening 46aa. The first jig 42 communicates with the first insertion hole 42a.

  The second insertion hole 46 a is linear, and the other opening of the second insertion hole 46 a faces the auxiliary jig 50 that holds the catheter tube 12. The auxiliary jig 50 is in communication with the second insertion hole 46 a and is formed with an auxiliary insertion hole 50 a through which the catheter tube 12 is inserted. The diameters of the second insertion hole 46 a and the auxiliary insertion hole 50 a are substantially the same as the outer diameter of the catheter tube 12 or slightly larger than the outer diameter of the catheter tube 12. The lengths of the second insertion hole 46a and the auxiliary insertion hole 50a are not particularly limited, but the total length of the second insertion hole 46a and the auxiliary insertion hole 50a is made longer than the length of the stent 14, so that the stock lumen can be obtained. The stent 14 can be moved more smoothly from the catheter 20a to the catheter lumen 12a.

  FIG. 6 is an enlarged cross-sectional view in which a joint portion between the first jig 42 and the second jig 46 in FIG. 5 is enlarged. As shown in FIG. 6, the second insertion hole 46 a of the second jig 46 is inserted through a catheter tube end portion 12 b that is an end portion of the catheter tube 12. The second insertion hole 46a has an inclined portion 46ab whose diameter increases toward the opposed opening 46aa. Further, a flare portion 12ba whose diameter increases toward the tube opening is formed in the catheter tube end portion 12b located in the second insertion hole 46a. The catheter tube end portion 12b is disposed in the second insertion hole 46a so that the flare portion 12ba is positioned at the inclined portion 46ab. The cross-sectional shape perpendicular to the axial direction of the second insertion hole 46a is circular including the portion where the inclined portion 46ab is formed, and this can prevent the catheter tube 12 from bending in any outer diameter direction. .

  As shown in FIG. 5, the first jig 42 and the second jig 46 have a positional relationship in which the central axis of the first insertion hole 42a and the central axis of the second insertion hole 46a are substantially coincident with each other. They are fixed to each other with bolts or the like. As shown in FIG. 6, the opening diameter D1 of the opposing side opening 46aa of the second insertion hole 46a is smaller than the outer diameter D2 of the stock tube 22 disposed in the first insertion hole 42a, and is smaller than the diameter D3 of the stock lumen 22a. It is set to be large.

  Thereby, the opening edge of the opposing side opening 46aa of the 2nd penetration hole 46a can contact the front end surface 22ba of the stock tube edge part 22b. That is, even when the stock tube end portion 22 b receives a force toward the second jig 46 in the moving process, the force is received by the opening edge of the opposing side opening 46 aa in the second jig 46. Further, since the opening diameter D1 of the facing side opening 46aa is larger than the diameter D3 of the stock lumen 22a, the stent 14 is moved to the facing side even when the opening diameter D1 of the facing side opening 46aa is smaller than the opening diameter of the first insertion hole 42a. The problem of getting caught in the opening 46aa can also be avoided. Note that the outer diameter D2 of the stock tube 22 and the diameter D3 of the stock lumen 22a, which are comparison targets with respect to the opening diameter D1 of the facing side opening 46aa, are the same as those in the case where the stock tube 22 is plastically deformed in the second diameter reducing step. These are the outer diameter of the stock tube 22 and the diameter of the stock lumen 22a after plastic deformation in the two-diameter process.

  In the moving process, as shown in FIG. 5, the stock tube 22 that has finished the second diameter reducing process (step S <b> 003 in FIG. 3) is disposed in the first insertion hole 42 a of the first jig 42, and the second jig 46. The catheter tube 12 which becomes a part of the stent delivery catheter 10 is arranged in the above. Thereby, as shown in FIG.5 and FIG.6, the stock tube 22 and the catheter tube 12 are arrange | positioned so that the stock lumen 22a and the catheter lumen 12a may be connected. However, as shown in FIG. 6, the stock lumen 22a and the catheter lumen 12a may be connected via a small gap, and the catheter tube 12 and the stock tube 22 do not necessarily have to contact each other without a gap.

  Next, in the moving process, the push rod 54 is inserted into the stock lumen 22a from the end of the stock tube 22 opposite to the end connected to the catheter tube 12. Further, the stent 14 accommodated in the stock lumen 22a is pushed in the axial direction by the push rod 54, and the stent 14 is moved toward the catheter lumen 12a.

  In the moving process, the stent 14 passes through the boundary portion between the catheter lumen 12a and the stock lumen 22a and moves to the catheter lumen 12a. At this time, as shown in FIG. 6, since the catheter tube end portion 12b has the flare portion 12ba, the problem that the stent 14 is caught by the catheter tube end portion 12b at the boundary portion is prevented. Further, since the flare portion 12ba is engaged with the inclined portion 46ab of the second insertion hole 46a, the problem of the catheter lumen 12a moving in the axial direction due to the frictional force with the stent 14 can be prevented.

  In addition, as described above, even when a force for moving the stock tube 22 toward the catheter tube 12 is generated due to the frictional force with the stent 14, the force is applied to the opposing side opening 46 aa in the second jig 46. The problem that the axial force is received from the stock tube 22 to the catheter tube 12 by the opening edge can be prevented. This prevents the problem that the force that bends the catheter lumen 12a acts on the catheter tube 12 during the movement process of the stent 14 and the problem that the catheter lumen 12a moves in the axial direction. Move can be realized.

  After the movement process of step S0004 is completed, the operation portion 16 and the like are attached to the catheter tube 12 in which the stent 14 is accommodated, whereby the stent delivery catheter 10 as shown in FIG. 1 is obtained. The flare portion 12ba of the catheter tube end portion 12b may be removed after the moving process.

  According to such a manufacturing method, the problem that local deformation | transformation arises in the stent 14 by preventing the diameter of the stent 14 by deform | transforming the stock tube 22 is prevented, and the smooth movement of the stent 14 in a subsequent movement process is prevented. Can be realized. In the second diameter reducing step, the stock tube 22 is deformed to reduce the diameter of the internal stent 14, and then the stent 14 is directly moved from the stock lumen 22a to the catheter lumen 12a. Therefore, compared to the conventional manufacturing method in which the stent 14 is reduced in diameter only by the reduced diameter device such as the first reduced diameter device 80 and the stent 14 is moved from the first reduced diameter device 80 to the catheter lumen 12a, the embodiment is compared with the embodiment. The manufacturing method shown can smoothly move the sufficiently contracted stent 14 to the catheter lumen 12a.

  In addition, the manufacturing method shown in the embodiment always applies a force to the stent 14 to reduce the diameter of the stent 14 from the outer diameter side until the moving process is completed after the second diameter reducing process is started. Manufacturing is performed while adding. Thereby, the manufacturing method shown in the embodiment makes it possible to simplify or omit the cooling operation or the like performed to prevent the expansion of the stent 14 and increase the manufacturing efficiency.

  In addition, the moving process of the stent 14 as shown in step S004 in FIG. 3 and FIG. 5 is not limited to the manufacturing method of the stent delivery catheter 10, and the stent 14 is kept in a state where the diameter of the stent 14 is reduced. However, it can be used as a method of moving between tubes. The specific manufacturing conditions and the like shown in the above-described embodiment are merely examples, and the technical scope of the present invention includes embodiments in which each manufacturing condition is changed.

DESCRIPTION OF SYMBOLS 10 ... Stent delivery catheter 12 ... Catheter tube 12a ... Catheter lumen 12b ... Catheter tube end part 12ba ... Flare part 14 ... Stent 16 ... Operation part 22 ... Stock tube 22a ... Stock lumen 22b ... Stock tube end part 24 ... Core for diameter reduction Material 30 ... Second diameter reducing device 32 ... Diameter reducing jig 32a ... Through hole 34 ... Clamp part 36 ... Drive part 42 ... First jig 42a ... First insertion hole 46 ... Second jig 46a ... Second insertion hole 46aa ... Opposite side opening 46ab ... Inclined part

Claims (4)

Inserting the stent into the stock lumen of the stock tube;
A diameter reducing step of reducing the diameter of the stent in the stock lumen by deforming the stock tube and reducing the diameter of the stock lumen;
The reduced diameter the stent, from said stock lumen of the stock tube, possess a moving step of moving the catheter lumen of the catheter tube, and
The movement of the stent in the moving step includes a first jig in which a first insertion hole inserted by an end of the stock tube is formed and a second insertion hole inserted by an end of the catheter tube. Using the second jig formed, the stock tube and the catheter tube are arranged so that the stock lumen and the catheter lumen are connected,
The opening diameter of one opening in the second insertion hole and facing the first jig is smaller than the outer diameter of the arranged stock tube, and the stock lumen in the arranged stock tube A method for producing a stent delivery catheter, wherein the diameter is larger than the diameter of the stent delivery catheter. The diameter reducing step is a diameter reducing jig in which a plurality of through holes having an inner diameter smaller than the outer diameter of the stock tube before deformation are formed in the axial direction, and the diameters of the plurality of through holes are using the reduced径治tool is formed smaller as the through hole that passes after, the stock tube before deformation the stent is inserted, by passing through a plurality of the through hole, the stock tube 2. The method for producing a stent delivery catheter according to claim 1 , wherein the diameter is reduced stepwise .   In the diameter reducing step, a plurality of the stock tubes before the deformation in which the stent is inserted are used by using a plurality of diameter reducing jigs having an inner diameter smaller than the outer diameter of the stock tube before the deformation. The diameter of the stock tube is reduced stepwise by sequentially passing through the through hole so that the diameter of the through hole to be passed next is smaller than the diameter of the through hole previously passed through. A method for producing a stent delivery catheter according to claim 1. A self-expandable stent-to-tube movement method for moving a self-expandable stent housed in a first lumen of a first tube to a second lumen of a second tube,
The 1st jig | tool in which the 1st penetration hole penetrated by the edge part of the said 1st tube is formed, and the 2nd jig | tool in which the 2nd penetration hole penetrated by the edge part of the said 2nd tube is formed. The stent is moved in a state where the first tube and the second tube are arranged so that the first lumen and the second lumen are connected to each other.
An opening diameter of one opening in the second insertion hole and facing the first jig is smaller than an outer diameter of the first tube and larger than a diameter of the first lumen. To move the self-expandable stent between tubes.

Images