KR20150112443A - Intravascular ablation balloon catheter - Google Patents

Abstract

The present invention relates to an intravascular radiofrequency ablation balloon catheter comprising: a liquid input portion connected to one end of a catheter body; a shaft configured as a long conduit and connected to the other end of the catheter body; an electrode formed on the distal end of the shaft; and a balloon formed on the distal end of the shaft, wherein when the balloon is inflated in a blood vessel, the inflated balloon only partially blocks the blood vessel so that a space capable of maintaining blood flow is formed.

Description

Intravascular ablation balloon catheter < RTI ID = 0.0 >

The present invention relates to a high frequency ablation balloon catheter capable of effectively removing various lesions difficult to access structurally in a cardiac blood vessel. More particularly, the present invention relates to an ablation electrode and a wedge balloon for removing a lesion site, The present invention relates to a high frequency ablation catheter capable of removing a lesion site while minimizing ac resistance by using a resection electrode which is in contact with a lesion located at various positions within the abdominal wall.

The heartbeat is performed by sequentially stimulating the heart muscle by an electrical signal periodically generated from a part of the heart. However, if an abnormality occurs in the flow of the electric signal, the heart can not be accurately pulsed. This abnormal signal is caused not only by the tissue in the heart but also by the abnormal electrical signal in the epicardium, causing abnormal heart beat, which is what is called arrhythmia.

The treatment of cardiac arrhythmias has changed considerably since the introduction of catheter ablation techniques with high frequency currents. In catheter ablation techniques, ablation-catheter is inserted into a single heart through the vein or artery under X-ray control, and tissue that causes cardiac arrhythmia by high-frequency current is destroyed. A precondition for successful execution of catheter ablation is to accurately detect the cause of arrhythmias within the heart. Such detection is diagnosed by electrophysiologic examinations in which electrical potentials are recorded in a spatially resolved state by a mapping-catheter inserted in the heart.

Paroxysmal supraventricular tachycardia is the most common persistent arrhythmia, which can increase heart rate from 100 to 175 or more per minute. Paroxysmal supraventricular tachycardia is a frequent occurrence of heart rhythm symptoms and is associated with a number of medical sequelae such as syncope, dizziness, dyspnea, chest pain, general weakness, and the like.

In finding the lesion causing the supraventricular tachyarrhythmia in the cardiovascular system, the heart beats precisely detect the bioelectrical signal in the heart by the practitioner, thereby determining the heart site causing the arrhythmia, and manipulating the position of the catheter . In addition, since there is no catheter for detecting and resecting electrical signals taking into consideration the characteristics in the cardiovascular system, a catheter designed to detect and ablate an electrical signal in the heart is used to make a point in contact with a part difficult to access to a cardiovascular lesion The area that caused the lesion could not be accurately detected. Especially, in the case of high frequency excision in a narrow cardiac blood vessel, the resistance value of the current suddenly increases, which makes it difficult to perform effective resection.

SUMMARY OF THE INVENTION Accordingly, the present invention has been made in view of the above problems, and it is therefore an object of the present invention to provide a cardiac pacemaker which is designed in consideration of structural features in a cardiac blood vessel, By positioning the balloon, the catheter movement can be minimized, minimizing the movement of the catheter and minimizing the movement of the catheter. Therefore, it is possible to increase the contact area of the lesion and adjust the operator precisely so as to provide a high frequency ablation catheter .

Further, in order to prevent abrupt change in the AC resistance value which may be caused in the ablation procedure in a narrow blood vessel, the wedge balloon can maintain the blood flow in the blood vessel so that the AC resistance can be stably maintained, Which is capable of stably moving a desired lesion even in a narrow vessel by designing the terminal thickness of the catheter to be thinner than that of the existing catheter, thereby improving the success rate of the catheter procedure.

Particularly, the present invention provides not only a method for removing an arrhythmogenic vital sign of a middle cardiac vein, which is a source of paroxysmal supraventricular tachycardia, but also a method of removing atrial tachycardia ), Ventricular tachycardia, and vascular intravascular rescue balloons that are useful in the removal of arrhythmia-induced vital signs of the great cardiac vein and anterior interventricular vein, which are the source of arrhythmia. And to provide a catheter.

In order to achieve the above object, the present invention provides a catheter comprising: a liquid introducing part connected to one end of a catheter body; A shaft comprising a long conduit connected to the other end of the catheter body; An electrode formed at a distal end of the shaft; And a balloon formed at the distal end of the shaft, wherein the balloon inflated when the balloon inflates in the blood vessel partially blocks the blood vessel, thereby forming a space capable of maintaining blood flow.

In the present invention, the diameter of the balloon before swelling may be 0.1 to 3 mm, and the diameter of the balloon after swelling may be 0.5 to 5 mm.

In the present invention, the balloon may be a wedge, a sphere, an egg, a cone, a step or a polyhedron.

In the present invention, a plurality of balloons may be provided, and at least two balloons may be formed at equal intervals along the circumferential direction of the shaft at the same position of the shaft.

In the present invention, a flow path for injecting liquid into the balloon can be formed inside the shaft, and the flow path can be a tube or pipe independent of the shaft.

In the present invention, a plurality of electrodes may be provided, and two to twenty electrodes may be provided.

In the present invention, the width of the electrodes may be 0.1 to 10 mm, and the electrodes may be arranged at intervals of 0.1 to 10 mm.

A catheter according to the present invention comprises: a first electrode formed at an end of a shaft and having a width of 1 to 5 mm; A second electrode formed at a distance of 0.5 to 3 mm from the first electrode and having a width of 0.5 to 2 mm; A third electrode formed at a distance of 1 to 6 mm from the second electrode and having a width of 0.5 to 5 mm; And a fourth electrode formed at a distance of 0.5 to 3 mm from the third electrode and having a width of 0.5 to 2 mm.

In the present invention, the balloon is formed between the second electrode and the third electrode, and at least two or more balloons may be formed at the same position.

In the present invention, a plurality of liquid discharge holes may be formed in the end surface of the shaft, and a plurality of liquid discharge holes may be formed in the electrode.

In the present invention, the length of the shaft is 100 to 150 mm, and the diameter of the shaft may be 0.1 to 5 mm.

In the present invention, the shaft can be bent from 0 to 180 degrees, and the bending radius can be from 10 to 100 mm.

The catheter according to the present invention can be used for cardiovascular high frequency excision.

The catheter according to the present invention is designed in consideration of the structural characteristics in the cardiovascular system and can be provided with a plurality of electrodes to apply electric stimulation to lesion parts existing in various parts of the desired cardiac blood vessel. In addition, by providing a wedge balloon with an appropriate size and shape, it is possible to stably approach the catheter by minimizing the movement of the catheter by the patient's breathing. Therefore, the contact area of the lesion is increased and the operator is precisely controlled to perform resection .

In addition, in order to prevent abrupt changes in the AC resistance value, which may be caused in a narrow vessel, a wedge balloon having an appropriate size and shape is provided so that the wedge balloon can maintain the blood flow in the blood vessel, It can help keep it stable. In addition, by designing the thickness of the distal end of the catheter to be thinner than that of the conventional catheter, it is possible to stably move the desired lesion even in a narrow vessel, thereby improving the success rate of the catheter procedure.

In particular, it is useful for the removal of arrhythmia-induced vital signs of the central intestinal vein, which is a source of paroxysmal atrioventricular arrhythmia, as well as for the treatment of atrial tachycardia, ventricular arrhythmia, Which is useful in the treatment of removing arrhythmia-induced vital signs.

1 is an overall configuration diagram of a catheter according to an embodiment of the present invention.
2 is an enlarged view of a portion A in Fig.
3 is a partial cutaway view of Fig.
4 is a view showing that the shaft of the catheter according to the present invention can be bent at various angles.
5 is a detailed view of a catheter having a liquid discharge hole in accordance with another embodiment of the present invention.

Hereinafter, the present invention will be described in detail with reference to the accompanying drawings.

FIG. 1 is an overall structural view of a catheter according to an embodiment of the present invention. The catheter according to this embodiment includes a liquid injection portion 10, a connector 12, a catheter body 20, a shaft 30, 40, 42, 44, 46, and balloons 50, 52.

In Figure 1, the left side is distal to the practitioner and the right side is the proximal side close to the practitioner.

The liquid injection portion 10 may be connected to the proximal end of the catheter body 20. The liquid is injected into the catheter through the liquid injecting section 10 and then injected into the balloons 50 and 52 so that the balloons 50 and 52 can be inflated. As the liquid, saline, a contrast agent, and the like can be used.

The connector 12 is connected to the proximal end of the catheter body 20 and can be connected to a separate catheter signal cable through the connector 12 so that the plurality of electrodes 40, 42, 44, and 46, respectively.

The catheter body 20 includes a handle capable of being held by a practitioner, and can be made of a metal or a plastic material. The handle may be configured as a push-pull control type.

The shaft 30 may be configured as a long conduit connected to the distal end of the catheter body 20. The shaft 30 may be made of metal (stainless steel, nitinol, etc.), plastic (nylon, polyether block amide, polyurethane, etc.), rubber or mixtures thereof and may be partially different in length Can be configured.

The shaft 30 may be composed of one single shaft and may also be composed of a plurality of shafts. When a plurality of shafts are constituted, they can be connected by using a connector, or by a method of fitting, welding, bonding or the like.

A space is formed in the shaft 30 like a conventional pipe or a tube. A separate flow path may be formed in the space, and liquid may flow through the space.

Hydrophilic and / or hydrophobic coatings may be applied to the inner and / or outer surface of the shaft 30 to reduce friction with, for example, the vessel wall.

The length of the shaft 30 is not particularly limited, and may be, for example, 100 to 150 mm, preferably 110 to 140 mm. If the length of the shaft 30 is too long or too short, it is inconvenient in the procedure. Usually, the length from the heart to the right thigh is most convenient for the operator.

The diameter of the shaft 30 is not particularly limited, and may be, for example, 0.1 to 5 mm, preferably 0.5 to 4 mm, and more preferably 1 to 3 mm. If the diameter of the shaft 30 is large, a thicker sheath should be used for blood vessel insertion, and the risk of thrombosis increases. On the other hand, when the electrode is too thin, the electrode is not subjected to the force when the catheter is operated, and the electrode is bent or broken.

Fig. 2 is an enlarged view of a portion A in Fig. 1, showing an enlarged distal end portion of a shaft 30 in which electrodes 40, 42, 44, and 46 and balloons 50 and 52 are formed. In the present invention, the term "end" may mean an end, and the term "end portion" may mean a portion from a terminal to a certain length. For example, the length of the distal end may be less than 30% based on the total length.

The electrodes 40, 42, 44, 46 may be formed in plural along the longitudinal direction of the shaft 30 at the distal end portion of the shaft 30.

Thus, by forming the electrodes into a plurality of multi-electrode shapes, it is possible to effectively remove a plurality of lesion parts while minimizing movement using a multi-electrode resection electrode in contact with lesion parts existing at various positions of the heart tissue. Specifically, by positioning the resection electrode in the vicinity of the resection electrode at the distal end of the catheter, the electrical signal at the lesion portion existing in various portions of the desired heart can be sensed or an electric stimulus can be applied to the lesion portion. In addition, since it is possible to approach the desired lesion while minimizing the movement of the catheter, the contact area of the lesion can be increased and the operator can precisely adjust the lesion to stably perform resection in the lesion.

In addition, since the other resection electrode is disposed at a position spaced apart from the resection electrode at the distal end of the catheter by a predetermined distance, when the distal end of the catheter inserted from the outside of the human body into the lesion passes through the lesion, Unlike conventional catheters that come and treat lesions, the ease of use of the catheter practitioner can be increased.

The electrodes 40, 42, 44, 46 are preferably all resection electrodes, and some may be mapping electrodes capable of sensing electrical signals.

The electrodes 40, 42, 44, 46 may be formed in a ring shape surrounding the outer circumferential surface of the shaft 30. The ring-shaped electrodes 40, 42, 44, 46 may be made of a conductive material, particularly a metal material. As the metal, platinum, gold, iridium, cobalt, titanium, nickel, silver, copper, zinc, tin, aluminum, chromium, manganese, magnesium and alloys thereof may be used. The method of forming the ring-shaped electrodes 40, 42, 44, and 46 is not particularly limited, and a method of fixing the ring-shaped metal material to the shaft 30 with an adhesive and a method of sputtering or ion- Thereby forming a ring-shaped electrode by film formation.

The electrodes 40, 42, 44 and 46 may be connected to lead wires (not shown), and lead wires may be inserted into the shaft 30 and connected to the connector 12 and the like via the main body 20.

The number of the electrodes 40, 42, 44, 46 is not particularly limited and may be, for example, 2 to 20, preferably 3 to 15, more preferably 4 to 10. If the number of electrodes (40, 42, 44, 46) is too small, the advantages of the multi-electrodes can be lost and the lesions can not be treated and the movement of the catheter can be increased. If the number of electrodes is too large, the electrode becomes thick and stiff .

The width of the electrodes 40, 42, 44, 46 is not particularly limited and can be, for example, 0.1 to 10 mm, preferably 0.5 to 7 mm, more preferably 0.7 to 5 mm. If the widths of the electrodes 40, 42, 44, and 46 are too small, the ablation site may be narrowed, and if too large, the normal region may be damaged.

The distance between the electrodes 40, 42, 44, 46 is not particularly limited and may be, for example, 0.1 to 10 mm, preferably 0.5 to 8 mm, more preferably 0.7 to 7 mm. If the arrangement interval of the electrodes 40, 42, 44, 46 is too narrow, the ablation site can be narrowed, and if it is too large, the accuracy and the like can be reduced.

2, the catheter according to the present invention includes a plurality of electrodes, for example, a first electrode 40, a second electrode 42, a third electrode 44, and a fourth electrode 46 can do. The number of electrodes 40, 42, 44, 46 may be more or less than that of FIG. In addition, the widths and the intervals of the respective electrodes 40, 42, 44, and 46 may be independently the same or different.

The first electrode 40 may be a tip electrode and may be formed from the distal end of the shaft 30. The width T ₁ of the first electrode 40 is preferably relatively large, and may be, for example, 0.5 to 10 mm, preferably 1 to 5 mm, more preferably 3 to 5 mm.

The second electrode 42 may be formed at a predetermined interval from the first electrode 40. The second electrode 42 may be formed in the form of a band electrode. The width T ₂ of the second electrode 42 is preferably relatively small, for example, 0.1 to 3 mm, preferably 0.5 to 2 mm, more preferably 0.5 to 1.5 mm. It is preferable that the interval S ₁ between the first electrode 40 and the second electrode 42 is relatively narrow, for example, 0.1 to 5 mm, preferably 0.5 to 3 mm, more preferably 0.5 to 3 mm, 2 mm.

The third electrode 44 may be formed at a predetermined distance from the second electrode 42. The width T ₃ of the third electrode 44 may be small or large as the case may be, for example, 0.1 to 10 mm, preferably 0.5 to 5 mm, more preferably 1 to 4 mm. The distance S ₂ between the second electrode 42 and the third electrode 44 is preferably relatively large, for example, 0.5 to 10 mm, preferably 1 to 6 mm, more preferably 3 to 6 mm, 5 mm.

The fourth electrode 46 may be formed at a predetermined interval from the third electrode 44. The width T ₄ of the fourth electrode 46 is preferably relatively small, and may be, for example, 0.1 to 3 mm, preferably 0.5 to 2 mm, more preferably 0.5 to 1.5 mm. The gap S ₃ between the third electrode 44 and the fourth electrode 46 is preferably relatively narrow and may be, for example, 0.1 to 5 mm, preferably 0.5 to 3 mm, more preferably 0.5 to 3 mm, 2 mm.

The balloons 50 and 52 may be formed at the distal end portion of the shaft 30 like the electrodes. As described above, liquid such as saline or contrast agent is injected into the catheter through the liquid injecting section 10 and then injected into the balloons 50 and 52 through the flow paths 54 and 56, Can be inflated.

The balloons 50 and 52 may be made of plastic or a fiber material such as nylon, polyether block amide (Pebax), polyurethane or the like. The balloons 50 and 52 may be of a multi-layer structure, for example, the envelope may be composed of a polyether block amide and the inner layer may be composed of nylon.

The balloons 50 and 52 may be inflatably attached to the distal end of the shaft 30 by attachment means using adhesives, heat, a laser, or the like.

In the present invention, the inflated balloons (50, 52) expand when the balloons (50, 52) expand in the blood vessels, thereby forming a space capable of maintaining blood flow by partially blocking the blood vessels.

Therefore, the size and shape of the balloons 50 and 52 are important in the present invention.

The diameter D ₁ of the balloons 50 and 52 may be 0.1 to 5 mm, preferably 0.1 to 3 mm, more preferably 0.5 to 2 mm. The diameter (D ₂ ) after expansion of the balloons 50, 52 may be 0.1 to 10 mm, preferably 0.5 to 5 mm, more preferably 1 to 4 mm. The diameter after expansion D ₂ can mean the diameter of the balloon 50, 52 that has been expanded to the maximum. When the balloons 50 and 52 are not spherical, the diameter of the balloons 50 and 52 may mean an average diameter. If the diameters of the balloons 50 and 52 are too small, the balloons 50 and 52 may not be adhered to the blood vessels. If the diameters of the balloons 50 and 52 are too large, the area of the channel space through which the blood can pass may be reduced.

The shape of the balloons 50 and 52 may be a wedge shape, a sphere shape, an egg shape, a cone shape, a step shape, a polyhedral shape, or the like, and may be spherical, as shown in the drawing. When the spherical balloons 50 and 52 are used, it is possible to secure more space for the blood to pass through.

A plurality of balloons 50 and 52 may be provided. Preferably, as shown in the figure, at least two balloons 50 and 52 may be formed at the same position. That is, the balloons 50 and 52 may be formed along the circumferential direction of the shaft 30 at any one point of the shaft 30. It is preferable that the intervals between the balloons 50 and 52 are equal to each other. For example, two balloons may be 180 degrees, three balloons may be 120 degrees, and four balloons may be 90 degrees. Preferably, as shown in the figure, when two spherical balloons 50 and 52 are formed at the same position and at intervals of 180 degrees, a maximum amount of a channel space through which blood can pass can be secured.

The balloons 50 and 52 may be formed between the second electrode 42 and the third electrode 44 as shown and the positions of the balloons 50 and 52 are not limited thereto and may be appropriately Can be changed. In addition, the balloons 50 and 52 may be formed in plural along the longitudinal direction of the shaft 30.

Fig. 3 is a partial cutaway view of Fig. 2, in which the proximal side of the balloon 50, 52 is cut to show the flow channels 54, 56.

The flow paths 54 and 56 are formed inside the shaft 30 and serve as passages for injecting the liquid into the balloons 50 and 52. [

The flow paths 54 and 56 may be formed as pipes or tubes independent of the shaft 30. [ In other words, the flow paths 54 and 56 can be formed by inserting separate pipes or tubes into the shaft 30. Alternatively, the flow passages 54 and 56 may be a space (lumen) integrally formed in the shaft 30.

When the flow paths 54 and 56 are made of tubes or pipes, the material may be made of metal (stainless steel, nitinol, etc.), plastic (nylon, polyether block amide, polyurethane, And can be made of materials that are partially different along the length direction.

The diameter of the flow paths 54 and 56 may vary depending on the diameter of the shaft 30 and may be, for example, 1 to 50%, preferably 5 to 30% of the diameter of the shaft 30.

The number of the flow paths 54 and 56 may vary according to the number of the balloons 50 and 52. For example, when two balloons 50 and 52 are formed as shown in the figure, 54, and 56 may be formed.

4 is a view showing that the shaft of the catheter according to the present invention can be bent at various angles.

The distal end of the shaft 30 is bendable from 0 to 180 degrees, as shown, and can be bent at more angles if desired. The bending of the shaft 30 can be performed by operating a handle of a push-and-pull control type. Thus, since the shaft 30 can be curved from 0 degrees to 180 degrees, it is possible not only to insert the catheter inside the intravascular cannula but also to easily access the portion where a large number of catheters are difficult to locate.

The bending radius (turning radius) of the distal end of the shaft 30 may be 10 to 100 mm, preferably 20 to 80 mm, more preferably 30 to 60 mm. If the bending radius of the shaft 30 is too small, it is impossible to perform a proper operation in a large heart, and if it is too large, operation in a small heart is difficult and dangerous.

FIG. 5 is a detailed view of a catheter having a liquid discharge hole according to another embodiment of the present invention. A plurality of liquid discharge holes 60 may be formed in the distal end surface of the shaft 30, The liquid discharge holes 62 and 64 may be formed.

As described above, since the liquid discharging holes 60, 62, 64 are sequentially arranged in the catheter ablation electrode, the lesion site can be more efficiently excluded. In particular, it can be useful for the procedure for removing the left atrium arrhythmia induced vital sign which is a source of atrial fibrillation arrhythmia.

The liquid discharged to the liquid discharge holes 60, 62 and 64 may be a liquid used for the purpose of cutting by electric stimulation (for example, heating, cooling, lubrication, contrast, blood vessel destruction, etc.). The liquid flows into the liquid discharge holes 60 and 62 and 64 while flowing through the inner space of the shaft 30 excluding the flow paths 54 and 56 .

The number of the liquid discharge holes 60 formed in the distal end surface is not particularly limited and may be, for example, 2 to 10, preferably 3 to 8. In the drawing, four liquid discharge holes 60 are formed.

The number of the liquid discharge holes 62, 64 formed in the electrodes 41, 45 is not particularly limited and may be, for example, 2 to 30, preferably 5 to 20. In the figure, twelve liquid discharge holes 62 are formed in the first electrode 41 and twelve liquid discharge holes 64 are formed in the third electrode 45. [

As described above, there is an advantage that the resection can be effectively performed through the plurality of liquid discharge holes 60, 62, and 64. [

The diameter of the liquid discharge holes 60, 62 and 64 may be 0.01 to 3 mm, preferably 0.05 to 1 mm, more preferably 0.1 to 0.5 mm. If the diameter of the liquid discharging holes 60, 62, 64 is too small, it is difficult to effectively drain the liquid, and if it is too large, the thickness of the electrode ceramics may increase and the blood may flow back into the discharging hole .

5 may also include a plurality of electrodes, for example, a first electrode 41, a second electrode 43, a third electrode 45, and a fourth electrode 47, The width and spacing of each electrode 41, 43, 45, 47 may be different from the catheter according to FIG.

The width t ₁ of the first electrode 41 may be, for example, 0.5 to 10 mm, preferably 1 to 5 mm, more preferably 3 to 5 mm.

The width t ₂ of the second electrode 43 may be, for example, 0.1 to 3 mm, preferably 0.5 to 2 mm, more preferably 0.5 to 1.5 mm. The interval s ₁ between the first electrode 41 and the second electrode 43 may be, for example, 0.1 to 5 mm, preferably 0.5 to 3 mm, more preferably 0.5 to 2 mm.

The width t ₃ of the third electrode 45 may be, for example, 0.1 to 10 mm, preferably 0.5 to 5 mm, more preferably 1 to 4 mm. The interval s ₂ between the second electrode 43 and the third electrode 45 may be, for example, 0.5 to 10 mm, preferably 1 to 6 mm, more preferably 3 to 5 mm.

The width t ₄ of the fourth electrode 47 may be, for example, 0.1 to 3 mm, preferably 0.5 to 2 mm, more preferably 0.5 to 1.5 mm. The interval s ₃ between the third electrode 45 and the fourth electrode 47 may be, for example, 0.1 to 5 mm, preferably 0.5 to 3 mm, more preferably 0.5 to 2 mm.

Table 1 shows the detailed configuration of the catheter manufactured according to one example of the present invention.

Feature Specification Type Steerable ablation catheter Catheter Diameter 5F (1.675 mm) Usable length 110 cm Number of electrode 4 (1 type and 3 bands) Tip electrode 5Fr and 4 mm in length Band electrodes 1 mm Electrode Space 2-5-2 mm Temperature sensor Thermocouple Shaft Deflection 180 ° uni-directional Handle Push-pull style

The catheter according to the present invention can be used for cardiovascular radiofrequency ablation, and is particularly useful for high frequency resection of coronary veins.

The catheter according to the present invention is capable of securing a space capable of maintaining blood flow. A liquid such as saline injected through the liquid injecting unit is injected into the balloon and the balloon is closely attached to the surface of the blood vessel. It can help to stabilize the position and can effectively perform resection.

10:
12: Connector
20: catheter body
30: Shaft
40, 41, 42, 43, 44, 45, 46, 47:
50, 52: Balloons
54, 56: Euro
60, 62, 64: liquid discharge hole

Claims (19)

A liquid inlet connected to one end of the catheter body;
A shaft comprising a long conduit connected to the other end of the catheter body;
An electrode formed at a distal end of the shaft; And
A balloon formed at the distal end of the shaft,
Wherein the balloon inflated when the balloon inflates in the blood vessel partially blocks only the blood vessel, thereby forming a space capable of maintaining blood flow.
The method according to claim 1,
Wherein the inflated diameter of the balloon is 0.1 to 3 mm.
The method according to claim 1,
Wherein the diameter of the balloon after inflation is 0.5 to 5 mm.
The method according to claim 1,
Wherein the balloon is of wedge, spherical, oval, conical, stepped or polyhedral shape.
The method according to claim 1,
And a plurality of balloons are provided.
6. The method of claim 5,
Wherein at least two balloons are formed at equal intervals along the circumferential direction of the shaft at the same position of the shaft.
The method according to claim 1,
Wherein a flow path for injecting a liquid with a balloon is formed in the shaft.
8. The method of claim 7,
Wherein the channel is an independent tube or pipe independent of the shaft.
The method according to claim 1,
Wherein a plurality of electrodes are provided.
10. The method of claim 9,
Wherein the number of electrodes is from 2 to 20.
10. The method of claim 9,
Wherein the electrode has a width of 0.1 to 10 mm.
10. The method of claim 9,
Wherein the electrodes are disposed at an interval of 0.1 to 10 mm.
10. The method of claim 9,
A first electrode formed at an end of the shaft and having a width of 1 to 5 mm;
A second electrode formed at a distance of 0.5 to 3 mm from the first electrode and having a width of 0.5 to 2 mm;
A third electrode formed at a distance of 1 to 6 mm from the second electrode and having a width of 0.5 to 5 mm; And
And a fourth electrode formed at a distance of 0.5 to 3 mm from the third electrode and having a width of 0.5 to 2 mm.
14. The method of claim 13,
Wherein the balloon is formed between the second electrode and the third electrode, and at least two balloons are formed at the same position.
The method according to claim 1,
And a plurality of liquid discharge holes are formed in the end surface of the shaft.
The method according to claim 1,
Wherein a plurality of liquid discharge holes are formed in the electrode.
The method according to claim 1,
Wherein the length of the shaft is 100 to 150 mm and the diameter of the shaft is 0.1 to 5 mm.
The method according to claim 1,
Wherein the shaft is bendable from 0 to 180 degrees and the bending radius is from 10 to 100 mm.
The method according to claim 1,
Wherein the catheter is used for cardiovascular radiofrequency ablation.

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