WO2014056460A1

WO2014056460A1 - Multifunctional ablation catheter system for renal sympathetic denervation

Info

Publication number: WO2014056460A1
Application number: PCT/CN2013/086076
Authority: WO
Inventors: 杨攀; 宋治远; 钟理; 廖新华; 王子洪; 舒茂琴; 仝识非
Original assignee: 第三军医大学第一附属医院
Priority date: 2012-08-29
Filing date: 2013-10-28
Publication date: 2014-04-17

Abstract

A multifunctional ablation catheter system for sympathetic denervation of renal arteries. The system comprises an ablation catheter (1), a control handle (2), an ablation generation apparatus (3), and can optionally be provided with a guide cannula (7). The ablation catheter (1), from the near end to the distal end, respectively, consists of a catheter body section (4) and an ablation section (6), the front end of the catheter body section (4) further comprising a controllably bendable section (5) connected to the control handle (2) by means of said catheter body section (4); and the ablation section (6) is provided with at least two independent structures (8), at least one of which is provided with an ablation tip (9). The ablation catheter system is capable of simultaneously ablating multiple points and of real-time monitoring of ablation effects during surgery, and offers improved mechanical stability.

Description

Renal desympathetic multi-functional ablation catheter system

The present invention relates to a medical device, and more particularly to a multifunctional ablation catheter system for treating hypertension and intervening into the renal artery to block the renal sympathetic nerve.

Background technique

Hypertension is a common and frequently-occurring disease in the clinic. According to the latest data, the number of hypertensive patients in China has exceeded 200 million, and the number of cases has increased year by year, and the age of onset has gradually advanced. High blood pressure, heart, brain, kidney and other important organs are complicated by high blood pressure and disability, which seriously endangers human health. There are about 30,000 million patients with refractory hypertension in China. In the future, with the aging of the population and the increase in obesity and diabetes, the number of patients with refractory hypertension will further increase, bringing great benefits to society, families and individuals. burden. At present, there is no good treatment for refractory hypertension, and new non-pharmacological treatments are being developed to make up for the shortcomings of current drug therapy, so that it is imperative to control blood pressure safely and effectively.

A large number of studies have confirmed that the over-activated sympathetic nervous system is closely related to the formation and progression of hypertension. Among them, the renal sympathetic nervous system, especially the renal sympathetic efferent and afferent nerve closest to the renal artery wall, is considered to be the beginning of hypertension. And important factors for maintenance. In response to this mechanism, foreign scholars have proposed a new hypertension treatment strategy for the treatment of refractory high blood pressure by catheter ablation of renal artery sympathetic nerve.

In 2009, Kr Hua and others first used Ardian's Symp ic i ty ablation catheter in 45 patients with refractory hypertension in the catheter ablation renal sympathetic treatment of refractory hypertension (Symp ic ty HTN-1 ). The implementation of renal desympathetic radiofrequency ablation confirmed that the new technology has a single, safe, and early pressure effect and can be maintained for a long time. In the 2-year follow-up observation, no decreased blood pressure was found, and renal function remained stable. More than ten clinical studies on percutaneous catheter renal sympathetic therapy have been or have been completed in many foreign centers. The results of completed or ongoing clinical trials are encouraging. This technology is expected to become a revolution in the field of hypertension treatment. Sexual breakthrough.

US 2011/0264075 A1 discloses a radiofrequency ablation catheter for renal desympathetic nerves. Although such catheters produced by Ardian have certain applications in foreign countries, there are also significant deficiencies. First, the catheter can only perform single-point ablation. Because the radiofrequency ablation of the renal sympathetic nerve is generally 6-8 points of spiral ablation around the renal artery, Ardian's catheter needs to be ablated 6-8 times. , the operation time is relatively long. For the ablation catheter of Ardian, the problem of multi-point ablation is not possible, US 2012/0116392 Al, US 2012/0029510 Al, CN 201110117776. 8, CN201110327772. 2 by setting a radio frequency ablation electrode on multiple electrode rods to reach multiple points For the purpose of simultaneous ablation, CN 102198015A achieves simultaneous multi-point ablation by mounting a plurality of radio frequency electrodes on a spiral electrode rod according to a predetermined position, although the above design achieves a plurality of simultaneous ablation of the renal artery to some extent, Because the radiofrequency ablation electrode is not tightly attached to the vessel wall, the radiofrequency ablation electrode is easy to move during ablation, and the ablation range is too large, causing unnecessary damage to the patient; in order to make the plurality of radiofrequency ablation electrodes closely attached to the vessel wall at the same time , US 2012/0101413A1 uses a solution to provide an expanding balloon in a rotating electrode rod. By filling the balloon with a liquid, the radiofrequency ablation electrode can be closely attached to the vessel wall, but the renal blood flow is expanded when the balloon is dilated. Will be blocked, if the ablation time is long, it will lead to renal ischemia, causing unnecessary In order to avoid the renal blood flow being blocked US 2012/0029512 Al Replace the ball with a wire tennis ball, although the problem of renal blood flow is blocked, but the operation is far from the convenience of the ball; The arterial variability is large, and the design of these multiple radiofrequency ablation electrodes is difficult to apply when the renal artery is mutated, thus limiting the population of renal sympathetic treatment; and the design of the above multiple radiofrequency ablation electrodes is only For radiofrequency ablation, it is difficult to generalize the same design for laser ablation, microwave ablation, and the like. Secondly, Ardian's single RF electrode catheter and the above-mentioned multiple RF ablation electrode catheters require the aid of an external catheter to reach the designated ablation site and the catheter guidance is not accurate enough to meet the clinical requirements. Once again, Ardian's single RF lead and the multiple RF ablation catheters are difficult to monitor the effects of ablation in real time, so It is difficult to perform an efficacy test during surgery, which increases the risk of secondary surgery. Summary of the invention

The object of the present invention is to provide a renal sympathetic multi-functional ablation catheter system capable of achieving simultaneous multi-point ablation, real-time monitoring of ablation blocking effect, and better mechanical stability. The technical solution is such that a renal desympathetic multi-functional ablation catheter system includes:

An ablation catheter, a control handle and an ablation generating device, wherein the ablation catheter comprises a catheter body segment and an ablation segment, wherein the catheter body segment is connected to the control handle;

The ablation section includes at least two separate structures with an ablation head mounted on at least one of the separate structures; the ablation head is coupled to an energy exchange connector on the control handle via a wire, conduit, microwave antenna or fiber, the energy exchange connector Connected to the ablation device via a wire, catheter, microwave antenna or fiber;

The separate structure allows the ablation head to be fitted or removed from the designated ablation position by pulling or/and pushing one end of the traction structure that is fixed to the separate structure and controlled by the handle at the other end; or the separate structure contains a substance attracted by the magnet, the external structure is deformed by an external magnetic field to cause the ablation head to fit or leave the designated ablation position; or the independent structure (8) contains a smart material deformed by external stimulation to fit the ablation head Or leaving the designated ablation position; the control of the above independent structure also includes the independent structure setting prefabrication deformation;

Or comprising an ablation catheter, a control handle and an ablation generating device, wherein the ablation catheter comprises a catheter body segment and an ablation segment, wherein the catheter body segment is coupled to the control handle;

The separate structure allows the ablation head to be fitted or removed from the designated ablation position by pulling or/and pushing one end of the traction structure that is fixed to the separate structure and controlled by the handle at the other end; or the separate structure contains a substance attracted by a magnet, the external structure is deformed by an external magnetic field to cause the ablation head to fit or leave the designated ablation position; or the independent structure contains a smart material deformed by an external stimulus to cause the ablation head to fit or leave the designated Ablation position

The control of the above independent structure also includes the independent structure setting prefabrication deformation;

The guiding catheter is fixed to the guiding catheter head by pulling or pushing one end, and the other end is controlled to be bent by the guiding wire controlled by the handle; or the guiding catheter contains a substance capable of being attracted by the magnet, and the guiding body is guided by the external magnetic field Deformation of the guiding tube; or by controlling the smart material on the guiding catheter that senses external stimuli; or/and compliant bending of the guiding catheter; or/and guiding the prefabrication of the guiding catheter;

The guiding catheter is controlled by the guiding catheter handle or control handle and is not controlled by the handle.

The distal end of the catheter body segment further includes a controllable curved section coupled to the proximal end of the ablation section, the controllable curved section being secured to the controllable curved section by one end of the pulling or/and pushing and the handle being controlled by the handle at the other end The wire control is deformed; or the controllable bending segment is deformed by pulling or/and pushing one end of the wire to be fixed on the independent structure, and the other end is controlled by the handle; or the controllable curved section contains a magnet An attracting substance that deforms the controllable curved section by an applied magnetic field; or the controllable curved section contains a smart material that is deformed by an external stimulus; or/and a compliance bend is controlled by the control handle to control the controllable curved section; or / Pre-fabrication with the controllable bending section.

Sensors are also mounted on the ablation catheter or/and the control handle, the guiding catheter or/and the guiding catheter handle. The independent structures are connected at the proximal end, and the two independent structures comprise four forms: the distal ends of the two independent structures are integrated to form the ablation section head end; or the two independent structures are separated from each other independently of each other. Or the middle portions of the two separate structures are connected together, and the distal ends are separated from each other; or the proximal ends of the two independent structures are connected, and the distal ends are respectively connected to different positions of the traction wires. The ablation head is selected from the group consisting of a radio frequency ablation electrode head, a resistance heating ablation head, a liquid-cold perfusion radio frequency electrode head, a cryoablation head, an ultrasound ablation probe, a focused ultrasound ablation probe, a laser ablation head, a focused laser ablation head, and a photodynamic therapy ablation head. Or a child wave ablation head; wherein the radiofrequency ablation electrode head comprises a radio frequency ablation electrode.

The independent structure is provided with detection electrodes for emitting or/and receiving electrical pulses; or / and the ablation heads are also used to dispense or/and receive electrical pulses.

A detection electrode for emitting or/and receiving an electrical pulse is disposed on the controllable curved section.

The traction wire travels outside the independent structure or/and travels in a separate structure. The tip end attachment point of the traction wire is disposed at the head end of the ablation section, or is disposed on a separate structure of the independent structure head to the connection point, or is disposed on the ablation head. On a separate structure to the connection point, or a separate structure between the ablation section head end and the ablation head, or on a separate structure in the ablation head or adjacent thereto, or a connection joint provided at the connection point of two separate structures In the controllable bending section and the catheter body section, the traction wires are merged into one or respectively running on the long axis center line of the controllable bending section and the catheter body section, and finally connected with the control knob or the control panel of the control handle.

When the guiding catheter provides a fulcrum for ablation catheter deformation, the head of the guiding catheter is provided with a slanted hole or/and a side channel that communicates with the blood vessel.

When the distal end of the independent structure is integrally connected to form the ablation section head end, the leading end of the guiding catheter is provided with a necking structure or a plug, and the side wall of the guiding duct is provided with a side groove; when the independent structures are separated from each other independently When the middle portion of the guiding catheter or the side wall of the head is provided with oblique holes; when the middle portions of the independent structure are connected together, and the distal ends are separated from each other, the head end or the head side wall of the guiding catheter is arranged to communicate with the blood vessel The inclined hole, after the inclined hole, is provided with a side groove on the side wall of the guiding catheter.

According to the need to control the number of bending directions, the number of guiding wires is set, the tip end attachment point of the guiding wire is arranged at the head of the guiding catheter, and the corresponding centrifugal position is selected according to the direction of bending required, and the guiding wire travels in the guide. Guide the inside of the tube wall or / and outside the tube wall.

The guide wire travels in the controllable curved section or/and outside the controllable curved section, and the number of guiding wires is set according to the number of bending directions required. When the controllable curved section is designed with a C-shaped bending, the tip end of the guiding wire is attached. It is arranged at a position where the controllable curved section is close to the ablation section, and the corresponding centrifugal position is selected according to the direction of bending required;

When the controllable curved section is designed with an S-shaped bending, on the basis of the C-shaped curved designing guide wire, a guide wire is attached to the second curved distal end where the S-shaped bending is required to be attached, the guiding The wire is selected according to the direction in which the bending is required, or the number of the guiding wires is not increased. By adjusting the internal structure of the controllable bending section, a guiding wire can realize S-shaped bending.

The tail wall of the guiding catheter is further provided with an opening for connecting an injector or a liquid injection device for intravascular injection or injection of an intravascular contrast agent, or by guiding the catheter end opening with a syringe or/and a liquid injection device Connecting intravascularly or/and injecting an intravascular contrast agent; or/and providing a connection connector at the end of the guiding catheter, the connection connector being coupled to the syringe, the infusion device, the ablation catheter or the control handle.

The ablation catheter or/and the guiding catheter are manufactured by selecting materials of different hardness, or by selectively reducing or/and increasing the internal structure of the partial catheter segments or/and the structure of the tube wall, or by ablation catheters. Or / and the guiding catheter is implanted with a structure that is susceptible to deformation.

Marking a scale on the ablation catheter or/and the guiding catheter to indicate the depth of the ablation catheter or/and the guiding catheter into the blood vessel and to indirectly measure the length and width of the body structure under ultrasound or X-ray imaging equipment; ablation catheter or / And a different development mark on the guiding catheter for distinguishing the ablation catheter or/and the guiding catheter under the ultrasound or X-ray imaging device; or/and setting different development marks on the individual structures for the ultrasound or X-ray image Different independent structures are distinguished under the device; markers are also provided on the ablation catheter or/and the guiding catheter for distinguishing different axial rotational states under ultrasound or X-ray imaging equipment.

The ablation catheter is secured to the upper end of the control handle by a catheter body segment having an energy exchange connector at the lower or lower side of the control handle, and wires, conduits, microwave antennas or fibers from the ablation head are collected through the control handle at the energy exchange connector.

The control handle includes an operating handle and an operating handle; the operating handle is provided with a control button for controlling the deformation of the controllable curved section Or a control panel, the control button or the control panel being connected to the guide wire, controlling the controllable curved section by the up and down movement of the control knob, or by controlling the multi-directional rotation of the control disc; or/and including the ring control on the operating handle a button, the ring control button is connected to the pulling wire through a connecting rod, the connecting rod is located in a guiding groove in the control handle, and the independent structure is controlled by moving the ring control button up and down; further comprising preventing excessive pulling Buffer structure.

The guiding catheter control handle includes an operating handle and an operating handle 242, and the operating handle 211' is provided with a control button or a control panel for controlling the deformation of the guiding conduit, and the control button or the control panel is connected with the guiding wire, and is controlled by Up and down movement of the button, or control of the guiding catheter by multi-directional rotation of the control panel; further comprising a buffer structure capable of preventing excessive pulling; the guiding catheter control handle and the control handle further comprise a card slot and a hook respectively The latching teeth are separated and combined by the card slot and the hook-shaped latching teeth.

The ablation generating device is provided with a connector for energy output and a connector for inputting a sensor signal, and is also provided with a grounding connector connected to an external power source; the ablation generating device includes controlling the parameter and some or all of the information by performing touch screen control. The display and the buttons that adjust the parameters displayed on it.

The invention adopts at least two independent structures and each of the independent structures can be provided with an ablation head, so that multiple simultaneous ablation can be realized, the ablation time is shortened, the operation time is reduced, and the patient's pain is reduced. Since the ablation heads on a plurality of independent structures will simultaneously contact the blood vessel wall during ablation, the ablation head can be prevented from sliding, so that the ablation head is more stable during ablation, and the unnecessary tissue damage caused by the instability of the ablation head during ablation is prevented. , reduces complications from ablation and makes the ablation process safer. In addition, the independent structure and the controllable curved section have corresponding wire control structure, magnetic control structure or intelligent material to control their deformation, so the catheter has better handling ability, can adapt to different running renal artery, and only 艮According to the specific situation, a guiding catheter can be added to the ablation catheter to assist the positioning of the ablation catheter, so that the positioning of the entire ablation catheter system in the blood vessel will be more accurate, preventing unnecessary damage, and the entire ablation system can be applied to more. Crowd. Moreover, in order to facilitate real-time monitoring of the ablation effect during surgery, a detection electrode is also mounted on the ablation catheter to facilitate timely detection of the ablation effect and avoid the risk of secondary surgery. Finally, the design of the ablation catheter can be adapted to a variety of ablation heads, such as radiofrequency ablation, cryoablation, and ablation, which are easy to generalize.

DRAWINGS

1 is a schematic structural view of a specific embodiment of the present invention;

Figure 2 is an enlarged schematic view showing four connection modes of two independent structures as ablation sections;

FIG. 3 is an enlarged schematic view showing two independent structures as ablation segments deformed in four connection modes; FIG. 4 is a schematic view showing different arrangement modes of the ablation heads on independent structures;

Figure 5 is a schematic view of the ablation head as a radiofrequency ablation electrode tip;

6 is a schematic view of the ablation head being a liquid-cooled perfusion radiofrequency ablation electrode tip;

7 is a schematic cross-sectional view of the ablation head when it is a liquid-cooled perfusion radiofrequency ablation electrode tip;

Figure 8 is a longitudinal cross-sectional view of the ablation head disposed on the head of the independent structure;

Figure 9 is a view showing the state in which the controllable curved section 5 is in a C-shaped bending design;

Figure 10-12 is a schematic view of the guiding catheter head in the case where two separate structures are exemplified and the guiding catheter can provide a fulcrum for the deformation of the ablation catheter;

Figure 13 is a schematic view showing the working state of the independent structure of the prefabricated deformation and the controllable curved section assisted by the guiding catheter in the case of two independent structures whose distal end is connected to the head end of the ablation section;

Fig. 14 and Fig. 15 are schematic diagrams showing the wire control structure of the C-shaped bending design in the case where two independent structures are connected at the distal end of the ablation section as an example.

Fig. 16 is a schematic diagram showing the wire-controlled structure of the S-shaped curved design in the case where two independent structures separated from each other are taken as an example. Figure 17, Figure 18, Figure 19 are schematic diagrams showing the hardness distribution of the ablation catheter and the guiding catheter by structural design. Figure 20 is a schematic illustration of the two separate structures of the remote control connected to the tip end of the ablation section and the design of the deformation by adjusting the stiffness distribution of the individual structures.

Figure 21 is a schematic diagram showing the design of two separate structures of the remote control separated from each other and the design of the deformation by adjusting the hardness distribution of the individual structures.

Figure 22 is a two-wire structure with a separate structure that is connected to the far end and separated from each other in the middle. The hardness distribution of the vertical structure is a schematic diagram of the design deformation.

Figure 23 is a schematic diagram of design deformation by adjusting the hardness distribution of the controllable curved section.

Figure 24 is a cross-sectional view showing the main structure of the guide catheter tail.

Figure 25 is a cross-sectional view showing the wire-controlled structure of the guiding catheter and the design deformation by adjusting the hardness distribution of the guiding catheter. Figure 26 is a cross-sectional view showing the structure of the control handle in the case of taking the wire control structure as an example.

Fig. 27 is a cross-sectional view showing the structure of the embodiment of the control handle 2 in the case where the wire guide structure is taken as an example.

detailed description

The invention will now be further elucidated with reference to the drawings and specific embodiments. These examples are to be construed as illustrative only and not limiting the scope of the invention. A person skilled in the art can make various modifications and changes to the present invention after reading the contents of the present invention. These equivalent variations and modifications are also within the scope defined by the claims of the present invention.

Figure 1 shows a specific embodiment of the invention and the main components therein. As shown in Fig. 1, the renal sympathetic ablation system is mainly composed of an ablation catheter 1, a control handle 2 and an ablation generating device 3, and the guiding catheter 7 is set or not provided according to the situation. Referring to 1, the distal end (head end) of the ablation catheter 1 is free, and the proximal end (tail end, end) is connected to the control handle 2, and the ablation catheter 1 is composed of at least the catheter body segment 4 and the ablation segment 6 from the proximal end to the distal end. Wherein the proximal end (tail end, end) of the catheter body section 4 is connected to the control handle 1, the distal end (head end) of the ablation section 6 is free, and the front end of the catheter body section may further comprise a controllable curved section 5, depending on the situation. Additional segments are provided between the catheter body segment 4 and the ablation segment 6. Preferably, the outer rim of each section of the ablation catheter 1 is preferably circular or circular in shape, and the segments into which the ablation catheter 1 enters the blood vessel are preferably of similar or equal diameter. The length of the ablation catheter 1 must be such that the ablation segment 6 can smoothly reach the designated ablation site of the bilateral renal artery, typically 50-120 cm, and the maximum diameter of each segment of the ablation catheter 1 is preferably less than the minimum diameter of the vessel in the vessel path. 5 隐。 The diameter of the ablation catheter is generally 1. 4-2. 5 hidden. As shown in Fig. 1, the guiding catheter 7 is preferably a hollow tubular structure having openings at both ends, and the guiding catheter 7 is disposed outside the ablation catheter 1 to assist the ablation catheter 1 to reach a designated ablation position. The length of the guiding catheter 7 must be such that the guiding catheter 7 can smoothly guide the ablation catheter 1 to the designated ablation site of the bilateral renal artery, typically 50-120 cm, and the maximum outer diameter of each segment of the guiding catheter 7 is preferably less than 5 隐。 5. The hidden diameter of the guiding catheter 7 is generally 1. 4-2. 5 hidden.

Figure 1 shows the main features of the ablation section 6 in a particular embodiment of the invention. As shown in Fig. 1, the ablation section 6 is composed of at least two independent structures 8; the independent structure 8 may be cylindrical, similar cylindrical, semi-cylindrical, pyramidal, pyramidal, curved, etc., each independent structure 8 The length and cross-sectional dimensions may be equal or unequal, but preferably, the outer porch of the cross-section of the ablation section 6 surrounded by the outer porch of all the independent structures 8 is preferably adjacent to the outer porch of the cross-section of the controllable curved section 5. . As shown in Fig. 2A, the distal ends (head ends) of the two independent structures 8 are connected to the ablation section head end 17 (i.e., the ablation catheter tip end); as shown in Fig. 2B, the two independent structures 8 are separated from each other and independent of each other. As shown in FIG. 2C, the middle of the two separate structures 8 are connected together at the distal end and then separated from each other, wherein the connection point 18 is where the two separate structures 8 are connected together. The trailing end of the separate structure 8 is connected to a controllable curved section 5 at the front end of the conduit section 4. The proximal ends of the two separate structures 8 are shown in Fig. 2D, and the distal ends are respectively attached to different positions of the pulling wire 10.

Fig. 3 shows the state in which the individual structure 8 of the present invention is deformed in two different connection modes. 3A shows the deformation of the separate structure 8 distally connected to the ablation section head end 17, in which case the intermediate portion of the individual structure 8 will be swelled, generally in the middle or near the middle of the individual structure 8. Most obvious. Figure 3B shows the deformation of the individual structures 8 as they are separated from each other, in which case the individual structures 8 will be remote from each other. Generally, the head ends of the individual structures 8 and their vicinity are most distant from each other. Figure 3C shows the deformation of the independent structure 8 when it is connected to the distal end and then separated from each other. The portion from the connection point 18 to the head end of the independent structure 8 will be away from each other. Generally, 8 heads are independent structures. The ends and their vicinity are most distant from each other, and the portion from the connection point 18 to the end (end, end) of the individual structure 8 will be swelled, generally, between the connection point 18 and the end of the individual structure 8. The bulge in the middle or near the middle is most pronounced. Figure 3D is a schematic illustration of the proximal ends of two separate structures 8 connected at different locations of the traction wires 10, respectively. Figure 4 shows the different arrangement of the ablation head 9 on the individual structure 8 in the present invention. As shown in Fig. 4A, at least one of the independent structures 8 is provided with an ablation head 9; as shown in Figs. 4B and 4C, each of the individual structures 8 may be provided with more than one ablation head 9. The ablation head 9 is mainly used for ablation of the renal sympathetic nerve; the ablation head 9 should be the original ablation function, so the ablation head 9 has various types, for example: radiofrequency ablation electrode head, liquid-cooled perfusion radiofrequency ablation electrode head, A cryoablation head, an ultrasound ablation probe, a focused ultrasound ablation probe, a laser ablation head, a focused laser ablation head, a photodynamic therapy ablation head, a microwave ablation head, a resistance heating ablation head, and the like. The types of ablation heads 9 on different individual structures 8 may be the same or different, and the types of a plurality of ablation heads 9 on the same individual structure 8 may be the same or different, for example: the ablation head 9 on a separate structure 8 is a cryoablation head. And the ablation head 9 on the other independent structure 8 is a radio frequency ablation electrode head, or the ablation head 9 at the front end of the same independent structure 8 is a focused laser ablation head, and the latter ablation head 9 is a child ablation head, which makes Different forms of ablation can be accomplished without replacing the ablation catheter 1 in different situations. According to the type of the ablation head 9, the ablation head 9 is different from the connection medium of the energy exchange connector 201 on the control handle 1. For example, when the ablation head 9 is a laser ablation head, the connection medium is generally an optical fiber, and the ablation head 9 When the electrode tip is ablated for the radio frequency, the connecting medium is generally a wire, and when the ablation head 9 is a cryoablation head, the connecting medium is generally a catheter.

Fig. 5 is an example in which the distal ends of two independent structures 8 are connected to the ablation section head end 17, and the main structural features of the ablation head 9 as a radio frequency ablation electrode tip are shown. 5毫米的接触为 contact with the vessel wall, the radiofrequency ablation electrode 91 is slightly protruded from the surface of the individual structure 8 0. 05-0. 2mm, in order to contact the blood vessel wall, the radiofrequency ablation electrode 91 is provided. . As shown in FIG. 5A, the radio frequency conductor 101 traveling in the independent structure 8 will be connected to the radio frequency ablation electrode 91 to supply energy to the radio frequency ablation electrode 91. The wire connection point 191 is the connection position of the radio frequency conductor 101 and the radio frequency ablation electrode 91. As shown in FIG. 5A, the signal line 102 is coupled to a sensor 192 disposed on or adjacent to the radio frequency ablation electrode 91 for transmitting a signal transmitted by the sensor 192 (shown in FIG. 5B); the sensor 192 can be of a different type. For example: temperature sensor, impedance sensor, pressure sensor, etc.; the same type of sensor 192 may be more than one on the independent structure 8 (Fig. 5 is an example of a sensor 192); the sensor 192 is for the radio frequency ablation electrode 91 and the human body. Parameter monitoring helps to understand the real-time situation and adjust the treatment plan in time. Figures 5B and 5C show, in perspective, the main structural features of the RF ablation electrode head 9 and its surrounding independent structure 8. As shown in FIG. 5B, the radio frequency ablation electrode 91 (the portion indicated by oblique lines in the figure) may surround only the curved side of the semi-cylindrical body without wrapping the flat side surface 90 of the semi-cylindrical body; as shown in FIG. 5C, the radio frequency ablation electrode 91 (The oblique line indicates the portion) may surround both the curved side of the semi-cylindrical body and the flat side 90 of the semi-cylindrical body; of course, the RF ablation electrode 91 may also adjust the range of its wrapping depending on the situation. The ablation head 9 is designed to be a resistance heating ablation head. FIG. 5 illustrates the design of the ablation head 9 with the distal end of the two independent structures 8 connected to the ablation section head end 17 as an example. Therefore, the design of the ablation head 9 illustrated in FIG. 5 is also applicable to the independent structure 8 . Other connection methods and the case of a plurality of independent structures 8; in addition, the skilled person can also adjust the position of the ablation head 9 on the independent structure 8 as needed; for the case where the independent structure 8 is not semi-cylindrical and for RF The shape of the individual structure 8 at the position where the ablation electrode 91 is disposed may be changed, and the design may be designed in accordance with the design scheme illustrated in FIG.

Figure 6 and Figure 7 show the main structural features of the ablation head 9 when it is a liquid-cooled perfusion radiofrequency ablation electrode head. Figure 7 is a schematic cross-sectional view of the liquid-cooled perfusion radiofrequency ablation electrode tip. As shown in FIG. 6A, the liquid-cooled perfusion radiofrequency ablation electrode head includes a radio frequency ablation electrode 91. Preferably, the surface of the radio frequency ablation electrode 91 has a plurality of small holes 193 connected to the catheter 103, and the catheter 103 will be connected to the control handle 1. The cooling liquid connected to the liquid filling joint 202 (shown in FIG. 54) is sprayed through the small hole 193 to the surface of the liquid RF ablation electrode 91 for cooling; as shown in FIG. 6A, the conduit 103 may be connected to each of the small holes, or Using the design of Figure 6B, the conduit 103 is connected to a cavity 69 below the aperture 193 through which liquid is delivered from each aperture. As shown in Fig. 6C, the cooling can also be performed by using a circulating liquid line around the ablation head 9, preferably by making the catheter 103 spiral, and pouring the coolant from the inlet indicated by the arrow aol, from the arrow ao2. Flow out. The coolant is usually cold brine. The above two types of cooling methods can be used in combination, and can also be used for rewarming, as long as the temperature of the perfusate is adjusted. Other types of ablation heads 9 that require simultaneous cooling or rewarming may also employ the above design. Figure 7A shows the main structural features of the cross section of a liquid-cooled perfusion radiofrequency ablation electrode head in the case where the radiofrequency ablation electrode 91 only surrounds the curved side of the semi-cylindrical body without wrapping the flat side 90 of the semi-cylinder; The semicircle shows the case where the radio frequency conductor 101, the signal line 102, and the duct 103 travel in the independent chamber 60, that is, the three structures are moved in separate chambers in the independent structure 8. In order to prevent interference from other structures; the lower semicircle of Fig. 7A shows the case where the radio frequency conductor 101, the signal line 102 and the duct 103 travel in the separate structure 8, at which point the above three structures will be mixed with other structures. Figure 7B shows the main structural features of the cross-section of the liquid-cooled perfusion radiofrequency ablation electrode head with the radiofrequency ablation electrode 91 wrapped around the curved side of the semi-cylindrical and the flat side 90 of the semi-cylinder; the upper semicircle of Figure 7B shows the radio frequency The case where the wire 101, the signal line 102, and the conduit 103 travel in the independent cavity 60; the lower semicircle of FIG. 7B shows the case where the radio frequency wire 101, the signal line 102, and the duct 103 travel in the independent structure 8, at which time the above three The structure will be mixed with other structures. The separate chamber 60 can be divided into a plurality of separate chambers for running different members, and the design of the different members for the different chambers can be used for other types of ablation heads 9, other portions of the ablation catheter 1 and the guiding catheter 7. For the case where the shape of the individual structure 8 is not semi-cylindrical and the shape of the independent structure 8 at the position where the liquid-cooled perfusion radiofrequency ablation electrode head 9 is disposed, the design shown in FIG. 6 and FIG. 7 can also be used. The plan is designed.

8 is an example of a longitudinal section of the longitudinal section of the ablation head 9 as a radio frequency ablation electrode head, showing the ablation head 9 disposed at the distal end of the two independent structures 8; wherein, FIG. 8A shows the ablation The head 9 only surrounds the curved side of the semi-cylindrical body without wrapping the flat side 90 of the semi-cylindrical body, and FIG. 8B shows the ablation head 9 surrounding the curved side of the semi-cylindrical body and the flat side 90 of the semi-cylindrical body. Happening. The design of the RF ablation tip illustrated in Figure 8 is similar to the design of the RF ablation tip illustrated in Figure 5. As shown in FIG. 8A and FIG. 8B, the distal ends of the independent structures 8 can be separated from each other. Similarly, the radio frequency wires 101 traveling in the independent structure 8 will be connected to the radio frequency ablation electrodes 91 to provide energy, wires for the radio frequency ablation electrode heads 9. The connection point 191 is a position where the radio frequency wire 101 is connected to the radio frequency ablation electrode 91. As shown in FIGS. 8A and 8B, similarly, the signal line 102 is connected to a sensor 192 disposed on the radio frequency ablation electrode 91 or/and adjacent to the radio frequency ablation electrode 91 for transmitting a signal transmitted by the sensor 192; similarly, the sensor 192 It can be of different types, for example: temperature sensor, impedance sensor, pressure sensor, etc.; the same type of sensor 192 can be more than one on the independent structure 8 (Fig. 8 is an example of one sensor 192); sensor 192 is a pair of radio frequency ablation electrodes The monitoring of the parameters of the head 9 and the human body helps to understand the real-time situation and adjust the treatment plan in time. As shown in FIG. 8A, the radio frequency ablation electrode 91 may only surround the curved side of the semi-cylindrical body without wrapping the flat side 90 of the semi-cylindrical body; as shown in FIG. 8B, the radio frequency ablation electrode 91 may surround the semi-cylindrical body. The curved side also surrounds the flat side 90 of the semi-cylinder; of course, the RF ablation electrode 91 can also be adjusted to encompass the extent of the individual structure 8 as appropriate. Since the design shown in FIG. 8 is described by taking the ablation head 9 as a radio frequency ablation electrode head as an example, the design is also applicable to the case where the ablation head 9 is another type of ablation head, and the radiofrequency ablation electrode is required. The head is replaced with other types of ablation heads, such as a liquid-cooled perfusion radiofrequency ablation electrode head, a resistance heating ablation head, etc.; for the case of a plurality of individual structures 8, for a case where the shape of the individual structure 8 is not semi-cylindrical, and for the ablation head 9 The case where the shape of the individual structure 8 at the set position is changed may also be designed in accordance with the design scheme illustrated in FIG.

Figure 9 shows the situation in which the controllable curved section 5 is in the C-shaped bending design. The main function of setting the controllable curved section 5 is to facilitate the ablation section 6 to more easily reach the designated ablation position, for example, to ablate Segment 6 is easier to bend through the blood vessel, making it easier for the ablation segment 6 to deflect in a specified direction, and the like. The controllable curved section 5 preferably has a cylindrical or cylindrical design, and the length of the controllable curved section 5 varies according to different designs. The controllable curved section 5 is shown in the working state of the C-shaped bending design. As shown in FIG. 9, the shape of the controllable curved section 5 is C-shaped, and the controllable curved section 5 of the solid line part represents one. In the case of a C-shaped bend, in this shape, the controllable curved section 5 preferably has a length of 60-120 hidden, and the controllable curved section 5 will have two places cl and c2 in contact with the inner wall of the blood vessel, wherein cl and the renal artery The inner side wall of a is in contact, and c2 is in contact with the inner side wall of the abdominal aorta b, which is advantageous for stabilizing the ablation head 9 during ablation, and the controllable curved section 5 is preferably in the same plane as one of the independent structures 8 at this time, Thus, for the case where only the ablation head 9 is used as the detecting electrode on the independent structure 8, the detecting electrode 19 can be disposed in the cl such that the detecting electrode 19 on the ablation head 9 or the independent structure 8 and the detecting electrode 19 on the controllable curved section 5 will Forming a discharge pulse, a receiving electrical pulse, of course, to accommodate renal artery of different diameters, a plurality of annular receiving detection electrodes 19 may be disposed near the cl; as shown in FIG. 9, the controllable curved segment 5 of the broken line portion indicates Another C-shaped bending situation, In this case, the controllable curved section 5 preferably has a length of 40-100 invisible, the controllable curved section 5 may not be in contact with the inner side wall of the artery, or only one place c2 may be in contact with the inner side wall of the artery, such that the ablation head 9 is Stabilization will primarily rely on the support points formed by the individual structures 8 in contact with the inner sidewalls of the artery. Depending on the circumstances, the skilled person can combine, improve and cross-use the design of the above-described ablation section 6 and the controllable bending section 5, and these equivalent variations and modifications also fall within the scope defined by the claims of the present invention.

The controllable bending section 5, the independent structure 8 and the guiding duct 7 can take the form of active control deformation or passive control deformation. The active control deformation of the controllable curved section 5, the independent structure 8 and the guiding duct 7 means that the controllable curved section 5, the independent structure 8 and the guiding duct 7 can be controlled by indirect real-time without external force direct action or transmission. The deformation of the curved section 5, the independent structure 8 and the internal force of the guiding catheter ,, for example: the controllable curved section 5, the independent structure 8 and the guiding catheter 7 contain a smart material (such as a shape memory alloy), through ablation The control of the temperature of the smart material and the like outside the catheter 1 and the guiding catheter 7 enables real-time transformation of the deformable shape of the controllable curved section 5, the independent structure 8 and the guiding catheter 7 in vivo and in vitro. The passively controlled deformation of the controllable curved section 5, the separate structure 8 and the guiding catheter 7 refers to the controllable bending section 5 by direct or indirect real-time control of external forces acting on the controllable curved section 5, the independent structure 8 and the guiding catheter 7. The deformation of the independent structure 8 and the guiding catheter 7; for example, by pulling the guiding wire 11 fixed on the controllable bending section 5 to deform the controllable bending section 5, by pulling the traction wire fixed on the independent structure 8 10 causes the independent structure 8 to be deformed, and the guiding catheter 7 is deformed by pulling the guiding wire 70 fixed on the guiding catheter 7; for example, during the pushing process, the ablation section head end 17 touches the blood vessel wall to enable Controlling the bending of the bending section 5; for example, the controllable bending section 5, the independent structure 8 and the guiding duct 7 contain substances capable of being attracted by the magnet, and the controllable bending section 5, the independent structure 8 and the guide by the external magnetic field The guide tube 7 is bent. Both the ablation catheter 1 and the guiding catheter 7 can be prefabricated. For example, in the in vitro manufacturing, the controllable curved segment 5 can be preliminarily bent in a certain direction, so that the ablation segment 6 can smoothly enter the renal artery; prefabrication deformation It is also possible to adjust the prefabrication deformation in vitro by adding a material having a shape memory function to the ablation catheter 1 and the guiding catheter 7, for example: adding a shape memory alloy to the controllable bending section 5, which can be firstly in vitro The curved shape is pre-formed into a C-shaped bend. When the controllable curved section 5 is required to change the curved shape, it can be taken out of the body again to make the controllable curved section 5 into a curved shape of other shapes by temperature change.

For the independent structure 8, the controllable curved section 5 and the active control deformation of the guiding catheter 7, the smart material is currently preferred, wherein the shape memory alloy with more mature technology is better, and of course, the electroactive polymer and the magnetic activity can be selected according to the technical requirements. Smart materials such as polymers. The shape memory alloy is designed into a spiral shape, a "Z" shape, a "G" shape, etc., and is implanted in the independent structure 8 and the controllable curved section 5 or in their tube walls, and in the wall of the guiding conduit 7, through the current The temperature of the shape memory alloy is adjusted to achieve the purpose of controlling the independent structure 8, the controllable curved section 5 and the guiding catheter 7.

For the passive control deformation of the independent structure 8, the controllable curved section 5 and the guiding duct 7, the linear control structure design and the magnetic control structure design are preferably used. On the ablation catheter 1, the wire-controlled structure is designed such that the tension or/and the stress of the guide wire 11 connected to the individual structure 8 or the guide wire 11 connected to the controllable curved section 5 causes a separate structure 8 or a controllable curved section. 5 passive control deformation occurs, but preferably by increasing the tension of the traction wire 10 or/and the guide wire 11, that is, pulling the traction wire 10 and pushing the ablation catheter 1 other than the traction wire 10 or/and the pulling guide wire 11 and Pushing the ablation catheter 1 except for the guide wire 11; similarly, the wire control structure on the guiding catheter 7 is a change in tension or/and stress of the guide wire 70 that travels in the wall of the guiding catheter 7, such that The guide tube 7 undergoes passive control deformation, but it is preferable to increase the tension of the guide wire 70, that is, to pull the guide wire 70 and push the guide catheter 7 except for the guide wire 70. The traction wire 10 is mainly responsible for controlling the deformation of the independent structure 8, and sometimes can also be directed to the ablation catheter 1, and the traction wire 10 can travel in the independent structure 8 in the ablation section 6, or can travel outside the independent structure 8, but in the ablation section. In other portions of the ablation catheter 1 other than 6, the traction wire 10 preferably travels within the ablation catheter 1 and is ultimately coupled to the traction wire retaining disk 205 on the control handle 2. The function of the guide wire 11 is mainly to adjust the direction of travel of the ablation catheter 1 in the blood vessel. The guide wire 11 preferably travels within the controllable curved section 5, and other portions of the ablation catheter 1 other than the controllable curved section 5 are preferably also traversed. The catheter 1 is ablated and ultimately connected to a guide wire retaining disk 204 on the control handle 2. The purpose of the guide wire 70 is primarily to adjust the direction of travel of the guiding catheter 7 within the blood vessel. The guide wire 70 preferably travels in the wall of the guiding catheter 7 and is ultimately coupled to the guiding catheter handle 27 or the control handle 2. The number of the guide wires 11 is mainly determined according to the bending direction to be controlled and the presence or absence of the preset deformation of the controllable curved segments 5. The number of the guide wires 11 is preferably less than or equal to the number of bending directions to be controlled, and Table 1 lists the guide wires. 11 number and control direction and the relationship between preset deformation. In the case where the main functions of the pulling wire 10, the guiding wire 11, and the guiding wire 70 are satisfied, it is preferable to minimize the number of the pulling wire 10, the guiding wire 11, and the guiding wire 70. The main structure of the magnetron structure is The independent structure 8, the controllable curved section 5 and the guiding catheter 7 are passively activated by the magnetic attraction or repulsion of the independent structure 8, the controllable curved section 5 and the substance capable of being attracted by the magnet in the guiding duct 7 under the action of an external magnetic field. Control deformation, from

Wire 11 Preset Control Direction Point 111 Preferred Settings Remarks

Quantity bending quantity position

With the preset bending direction, preset one direction of bending, pull the guide wire 11 and then turn

1 has > 2

Relative to the opposite direction of the preset bend

The two are respectively bent in one direction with the preset preset, and each of the pulling wires 11 is bent in a direction opposite to the pulling guide wire 11 to realize two directions, and simultaneously

2 have > 3

Different angles of 120 degrees. Pulling the two guide wires 11 to achieve one direction, changing the position of the pulling force can adjust the bending direction.

Pulling and pushing the guide wire 11 achieves two directions in total,

1 none > 1

Only the pulling or pushing of the guiding wire 11 realizes the same direction in one direction. Each pulling of one guiding wire 11 realizes two directions in total.

2 None > 2 or different cross-sections Pulling two guide wires at the same time to achieve one direction (when the upper end fixed point 111 is on a different cross section)

Each pulling of a guide wire pulls the guide wire to achieve three directions, and simultaneously pulls two guide wires to achieve three

3 no > 3 two into a 120 degree angle

Direction, varying the amount of pulling force can adjust the bending direction

Each pulling of a guide wire pulls the guide wire to achieve a total of four adjacent two into 90 degrees, while pulling the adjacent two guide wires together

4 no > 4

The angle is in four directions, and the magnitude of the pulling force can be adjusted to the bending direction. Referring to Figures 10-12, for the case where the guiding catheter 7 can provide a fulcrum for the deformation of the ablation catheter 1, the head of the guiding catheter 7 is guided. It is preferable to provide an inclined hole 74 or/and a side groove 76 that communicates with the blood vessel. The inclined hole 74 and the side groove 76 mainly serve as a separate structure 8 to guide the outwardly extending passage of the guide tube 7, and the independent structure 8 is brought into contact with the blood vessel wall. Of course, the oblique hole 74 and the side groove 76 can also be used as an injection into the blood vessel or/and The channel into which the contrast agent is injected. The manner in which the inclined holes 74 and the side grooves 76 of the head of the guiding catheter 7 are different according to the number of the independent structures 8 and the interconnection of the two independent structures 8 is also different. 10A, 10B, and 10C are schematic longitudinal cross-sectional views, and Figs. 10D and 10E are perspective views. As shown in FIG. 10, when the individual structures 8 are separated from each other, a plurality of inclined holes 74 corresponding to the individual structures 8 are formed on the head end (distal end) or the head side wall of the guiding catheter 7; As shown in FIG. 10D, the inclined hole 74 can be opened at the head end of the guiding catheter 7, as shown in FIG. 10B and FIG. 10C, and the inclined hole 74 can also be opened on the side wall of the guiding catheter 7, each oblique hole. The inner diameter of 74 is greater than the outer diameter of the independent structure 8, generally 1.4 - 2. 4mm, the angle of inclination of each inclined hole 74 is generally 30 - 50 degrees, and the number of inclined holes 74 is preferably equal to the number of independent structures 8, oblique The connecting portion 75 between the holes 74 is preferably tapered, and the connecting portion 75 not only limits the ability of the controllable curved section 5 to be pushed out of the guiding catheter 7 but also helps guide the independent structure 8 to be pushed forward from the inclined hole 74. If the ablation catheter 1 or the retraction guide catheter 7 is pushed, as shown in Fig. 10C, the independent structure 8 will be diverged into the blood vessel from the inside of the oblique hole 74, and the ablation head 9 of the head of the independent structure 8 will preferentially The blood vessel wall contact; by controlling the distance between the push ablation catheter 1 or the retraction guide catheter 7 and the inclination of the oblique hole 74, the distance separating the distal ends of the independent structures 8 from each other and the pressure at which the ablation head 9 is in contact with the blood vessel wall can be controlled. 11A, 11B are longitudinal cross-sectional views, and Fig. 11C is a perspective view. As shown in FIGS. 11A and 11C, when the distal end of the independent structure 8 is collected at the ablation section head end 17, the head end opening of the guiding catheter 7 preferably limits the ablation section head end 17 to be pushed forward by a structural design. Catheter 7, preferably can be set to shrink The structure 73 allows the opening of the tip end of the guiding catheter 7 to be smaller than the outer diameter of the ablation section head end 17 (shown in Fig. 11A), or to close the head end opening of the guiding catheter 7 with the plug 72 (Fig. 11B, Fig. 11C) As shown in FIG. 11, the side wall of the leading end of the guiding catheter 7 is preferably provided with a side groove 76 which is close to the length of the independent structure 8 and communicates with the blood vessel, and the length of the side groove 76 is generally 11-13 mm. The side groove 76 preferably corresponds to the independent structure 8 in parallel. The width of the side groove 76 is slightly larger than the outer diameter of the individual structure 8, generally 1. 4 - 2. 4 hidden, and the number of side grooves 76 is preferably equal to the number of the independent structures 8. If the ablation catheter 1 or the retraction guide catheter 7 is pushed, as shown in FIG. 11B, the ablation section head end 17 will cause the individual structures 8 to bulge from the respective side grooves 76 due to the restriction of the plug 72, which will cause the ablation head to be ablated. 9 preferentially in contact with the vessel wall; by controlling the distance between the ablation catheter 1 or the retraction guide catheter 7, the distance between the intermediate portion of the independent structure 8 and the pressure at which the ablation head 9 is in contact with the vessel wall can be controlled. For the case where the middle of the independent structure 8 is connected to the distal end and then separated from each other, the design of the head of the guiding catheter 7 is combined with the design shown in Figs. As shown in Fig. 12A, a plurality of oblique holes 74 communicating with the blood vessel are provided on the side wall of the guiding catheter 7, or a plurality of small oblique holes 74 are provided at the head end of the guiding catheter 7 (similar to Fig. 10A, Fig. 10D). The side groove 76 corresponding to the inclined hole 74 and parallel to the independent structure 8 is disposed on the side wall of the guiding duct 7 at a certain distance after the inclined hole 74, and the spacing between the inclined hole 74 and the side groove 76 is provided. The distance is generally between 2. 5 and 5. 5 mm, the inner diameter of each inclined hole is slightly larger than the outer diameter of the independent structure 8, generally 1. 4 - 2. 4 hidden, the inclined angle of each inclined hole 74 is generally 30 - 50 The connecting portion 75 between the inclined holes is preferably tapered, and the connecting portion 75 can not only restrict the connection point 18 and the controllable curved portion 5 from being pushed out of the guiding duct 7 but also help guide the independent structure 8 from the inclined hole 74. The length of the side groove 76 is preferably slightly larger than the outer diameter of the independent structure 8, generally 1. 4 - 2. 4 hidden, the length of the side groove 76 is similar to the length of the portion of the proximal end of the independent structure 8 to the connection point 18, Typically 10-22 mm, the number of inclined holes 74 and side grooves 76 is preferably equal to the number of individual structures 8. If the ablation catheter 1 or the retraction guide catheter 7 is pushed, the portion of the distal end of the independent structure 8 from the connection point 18 will be divergently pushed into the blood vessel from the inside of the oblique hole 74, and the ablation head of the head of the independent structure 8 9 will preferentially contact the vessel wall, and the portion between the proximal end of the independent structure 8 and the junction 18 will bulge from the corresponding side groove 76, and the most prominent place of the ridge will preferentially contact the vessel wall; the ablation catheter is controlled by push 1 or the distance of the retracting guide catheter 7 and the inclination of the oblique hole 74 can control the distance separating the distal ends of the individual structures 8 from each other and the pressure at which the ablation head 9 is in contact with the vessel wall. The oblique holes 74 and the side grooves 76 in the above design also have the effect of injecting a drug into a blood vessel or injecting a contrast agent. In order to facilitate the formation of the design deformation of the individual structure 8, the design shape change can be easily realized by adjusting the structural design of the individual structure 8 or by changing the hardness of the manufactured material. 10, FIG. 11, and FIG. 12 illustrate the design of two independent structures 8 as an example, and thus are not limited to the case of two independent structures 8. For more than two independent structures 8, only the map is required. 10. The design concept illustrated in FIG. 11 and FIG. 12 adjusts the number and arrangement positions of the inclined holes 74 and the side grooves 76.

Referring to Figure 13, for the case where the guiding catheter 7 cannot provide a fulcrum for the deformation of the ablation catheter 1, the independent structure 8 can also be provided with a pre-formed deformation, the controllable curved section 5 can be prefabricated, and then the ablation catheter 1 can be pressed In the guiding catheter 7, after the head end of the guiding catheter 7 reaches the designated position, the ablation catheter 1 can be pushed out from the opening of the leading end of the guiding catheter 7 to restore the prefabrication deformation. As shown in Figure 13, the two separate structures 8 that collect the distal end at the head end 17 of the ablation section are preformed into a spindle-like shape, and the ablation catheter 1 is pressed into the guiding catheter 7, due to the limitation of the guiding catheter 7, The intermediate portions of the two separate structures 8 pre-formed into a spindle shape will be brought closer together; when the guiding catheter 7 reaches the opening of the renal artery a at the aorta b, the ablation section 6 is opened from the opening of the leading end of the guiding catheter 7. Pushed out, the two separate structures 8 will now return to a prefabricated spindle-like shape, with the protruding portion of the attached ablation head 9 preferentially contacting the vessel wall. When the controllable curved section 5 is pre-formed into a C-shape, the guiding catheter 7 can push the ablation section 6 out of the opening of the guiding end of the guiding catheter 7 when approaching the opening of the renal artery a at the aorta b, since By controlling the presence of the C-bend of the curved section 5, the ablation section 6 can also smoothly enter the renal artery a from the aorta b. The two independent structures 8 connected at the distal end to the ablation section head end 17 are taken as an example for design, and thus are not limited to the case of two independent structures 8, and are not limited to the independent structure 8 distal end connected to the ablation section head. The connection mode of the two-independent structure 8 of the end 17 is also applicable to the case of more than two independent structures 8 and the other connection modes of the two independent structures 8. For example, for the separate structures 8 separated from each other, it is necessary to be independent. The structure 8 is prefabricated in such a manner that the head end and its vicinity are far from each other in the most obvious state, and then pressed into the guiding duct 7, and for example, in the case where the middle of the independent structure 8 is connected to the distal end and then separated from each other, it is necessary to The portion of the individual structure 8 between the distal end and the attachment point 18 is prefabricated in a state in which the head end and its vicinity are far apart from each other, and the portion between the proximal end of the individual structure 8 and the connection point 18 is pre-formed into a spindle shape. , The guiding catheter 7 is then pressed into it. Furthermore, it is also possible to provide an oblique hole 74 or/and a side groove 76 corresponding to the individual structure 8 at the head of the guiding catheter 7, so that independence can also be achieved without pushing the guiding catheter 7 before the ablation section 6 is pushed out. Structure 8 restores the prefabricated deformation.

14 and 15 show the wire-controlled structure when the controllable curved section 5 is a C-shaped curved design. As shown in FIG. 14, when the controllable curved section 5 is designed by a C-shaped bending, the tip end of the guiding wire 11 is fixed. The point 111 is preferably disposed where the controllable curved section 5 is adjacent to the ablation section 6, and the corresponding centrifugally fixed position should be selected according to the direction in which the bend is desired. The guide wire 11 preferably travels within the controllable curved section 5 and has at least one guide. The wire 11 is coplanar with a pulling wire 10. As shown in Fig. 15A, when the controllable curved section 5 is designed with a C-shaped curved portion of a broken line portion, the pulling wire 10 can be used to function as the guiding wire 11, and the head end fixing point 110 of the pulling wire 10 is set at the ablation. The tip end 17 of the segment; of course, the C-shaped curved structure shown in FIG. 15 can also be fixed by the guiding wire 11 shown in FIG. 14, and the arrangement and running of the pulling wire 10 can also be designed according to FIG. Ways to arrange.

Figure 16 shows the wire-controlled structure of the controllable curved section 5 in the S-shaped curved design. As shown in Fig. 16A, when the controllable curved section 5 is designed with an S-shaped curve, the C-shaped curved design shown in Fig. 14A is shown. On the basis of the arrangement of the guide wire 11, a guide wire 1 may be attached to the distal end of the second bend which needs to form an S-shaped bend, and the guide wire 1 should be selected according to the direction of bending required to select the corresponding centrifugal attachment. The position is preferably coplanar with at least one of the guide wires 11; as shown in Fig. 16B, the number of the guide wires 11 may not be increased, by adjusting the running path of the guide wire 11, and by adjusting the hardness distribution of the controllable curved segment 5, The "S"-shaped bending can be achieved by one of the guide wires 11.

Figures 17, 18 and 19 show the deformation of the ablation catheter 1 and the guiding catheter 7 in a manner designed by the present invention. This manner of structurally facilitating the deformation of the ablation catheter 1 and the guiding catheter 7 does not require the hardness of the material of the respective parts to be different.

As shown in Figs. 17A and 17B, the chicken rib-like structure shown in Figs. 17A and 17B is disposed inside the ablation catheter 1, i.e., a cross-sectional distance d5 is provided as a structure shown in Fig. 17B, and the structure is indicated by oblique lines. Partially filled with a material having a certain elasticity, preferably a high molecular polymer, the blank area a1 will form a chamber in the ablation catheter 1, mainly for the running of the traction wire 10 and the poor bending resistance or the easy traction with the wire 10 Or the running of the structure in which the guiding wire 11 is entangled, such as a wire, a conduit, an optical fiber, etc., of course, the blank area a1 is not limited to a circular shape, nor is it limited to only one chamber, and may be set to other shapes according to the situation ( For example, elliptical, rectangular, etc., it is also possible to provide more chambers to travel different components. As shown in Fig. 17A and Fig. 17B, the blank region bl will also form a chamber in the ablation catheter 1, mainly for guiding the guide wire 11 or/and the traction wire 10, and of course the blank region a1 is not limited to a semicircle. It is not limited to only one chamber, and may be set to other shapes (for example, elliptical, rectangular, etc.) depending on the situation. It is also possible to provide more chambers to travel different members separately, if it is desired to pull the wire 10 or the guide wire 11 Without affecting each other, the pulling wire 10 and the guiding wire 11 can respectively travel in different chambers. As shown in Fig. 17A, since the area included in d5 lacks the curved structure in the area included in d3 and d4 in Fig. 17B, the area included in each d5 will be easily bent in the longitudinal direction, all d5 The bending of the included area will cause the structure shown in Fig. 17A to be integrally curved; taking the controllable curved section 5 as an example, if the pre-formed bending direction of the controllable curved section 5 is the direction indicated by the arrow in Fig. 17A, then the pulling The guide wire 11 running from the blank area bl near d4 will cause the controllable curved section 5 to be bent in the opposite direction as indicated by the arrow in Fig. 17A, so that the bending in both directions is achieved by one guide wire 11. Similarly, as shown in FIG. 17C, two blank regions bl, b2 in FIG. 17B are disposed in the region included in d3, d4, d3', and d4', and the blank region a1 is located in the blank region. Between b1 and b2, in the region covered by dl (mainly in the region surrounded by d2 and d2'), the structure in the region included in d6 in Fig. 17A will be replaced by the structure shown in Fig. 17C. The structure in the region included in d5 of 17A will be an extension of the structure in the region included by dl in Fig. 17C; the blank region a1 will form a chamber in the ablation catheter 1 for pulling the wire 10, which is resistant to bending deformation. The structure or the structure which is easy to be entangled with the pulling wire 10 or the guiding wire 11 is of course not limited to an elliptical shape, nor is it limited to only one chamber; the blank areas bl and b2 are also in the ablation catheter 1 Two chambers will be formed, mainly for guiding the wire 11 or/and the pulling wire 10, of course, the blank areas bl and b2 are not limited to a semicircular shape, nor are they limited to only one chamber, if it is desired to pull the wire 10 and the guide wire 11 do not affect each other, the traction wire 10 and the guide wire 11 can be divided Take different rows chamber; FIG lack in the region of 17C included in d5 d3, d4, d3 ', d4' The arcuate structure in the area contained in the area, so in the direction of the longitudinal axis, the area included in each d5 will easily bend under the action of the pulling wire 10 or the guiding wire 11, and the bending of all the areas included in the d5 will make The structure shown in Fig. 17A forms an overall curvature, and since the support structure is lacking on both sides of d5, bidirectional bending can occur, and the difficulty of bending in two directions is different by adjusting the sizes of the blank areas bl and b2; Similarly, three bl-like blank regions as illustrated in Fig. 17B can be disposed in three different directions to achieve bending in at least three directions, and such a design structure can be deduced by analogy. As shown in Figs. 17D and 17E, when the cross section of some portions of the ablation catheter 1 is not circular, the chicken rib-like structure can also be realized in the ablation catheter 1 portions, and Figs. 17D and 17E are in a semicircular configuration. The example illustrates the implementation of the chicken rib-like structure in shapes other than a circle, and the positions of the different blank areas a1 and bl are different depending on the direction of the bending. For example, as shown in Fig. 17D, the blank area bl is arranged to the left of the blank area a1, and the structure in the area included in d6 in Fig. 17A will be replaced by the structure shown in Fig. 17D, and the area included in d5 in Fig. 17A The structure will be an extension of the structure in the region covered by dl in Fig. 17D, so that the entire three-dimensional structure will be easily bent or weakened toward the blank area bl side under the pulling of the pulling wire 10 or the guiding wire 11 running in the blank area bl. The degree of bending of the region a side; as shown in Fig. 17E, the blank region bl is arranged to the right of the blank region a1, and the structure in the region included in d6 in Fig. 17A will be replaced by the structure shown in Fig. ,, and the region included in d5 The inner structure will be an extension of the structure in the area covered by dl in Fig. 17E, so that the entire three-dimensional structure will easily bend or weaken toward the blank area bl side under the pulling of the pulling wire 10 or the guide wire 11 running in the blank area bl. The degree of bending to the blank area a side. In the structure shown in FIG. 17, by changing the size and number of the blank areas a1, bl, b2, and by changing the sizes of dl, d2, d3, d4, d5, d6, the hardness of each section can be different, for example, In Figure 17A, a certain section is widened by dl. If d3 or d4 is reduced, the segment will not be easily deformed. For example, if a segment is widened by d5, the segment will be easier to deform. By changing the relative positions of the blank regions a1 and bl in different segments. The position can achieve different segments of non-co-directional bending, for example, horizontally rotating the lower half of the structure shown in Fig. 17A by 180 degrees, so that the lower half blank area bl is on the side of the arrow in Fig. 17A, so that the improved structure will help To achieve S-shaped bending. In summary, the essence of the chicken rib-like structure is to selectively reduce or/and increase the resistance to bending on one side or sides of certain catheter segments by reducing or/and increasing the internal structure of certain catheter segments so that the catheter It is easier to bend or/and form certain curved forms in certain directions.

Fig. 18 shows another design of the present invention which changes the hardness distribution by means of structural design to promote the multi-directional bending of the ablation catheter 1 and the guiding catheter 7. This structural design is preferably used in situations where it is desirable to control the multi-directional bending of the controllable curved section 5. 18A is a schematic perspective view of the structure, and FIG. 18B is a schematic cross-sectional view of the horizontal center line of the structure included in the structure d6, that is, a cross-sectional view of the cc2 cross section in FIGS. 18C and 18D, and FIGS. 18C and 18D are the structure. A schematic longitudinal section, that is, a cross-sectional view of the ccl cross section in Fig. 18B. The design structure is similar to the chicken rib-like structure, and is also a structure included in a d6 region at a distance d5. As shown in Figs. 18A, 18C, and 18D, the entire three-dimensional structure is a double convex disk overlap. As shown in Fig. 18, the portion indicated by the oblique line or the horizontal line in the structure is filled with a material having a certain elasticity, and a polymer is preferable. As shown in Figs. 18A and 18B, the disc center blank area a1 will form a chamber in the ablation catheter 1, mainly for the traction wire 10, a structure resistant to bending deformation or a structure easily entangled with the guide wire 11. The walking area, of course, the blank area a1 is not limited to a circle, nor is it limited to only one chamber, and may be set to other shapes (for example, elliptical, rectangular, etc.) depending on the situation, or more chambers may be provided separately. Different components; the blank areas bl, b2, b3, b4 around the disc will form four interrupted pipes in the ablation duct 1, mainly for guiding the wire 11, the diameter of the pipe is d3, when the double convex disk When the overlapping structure is used for other parts, the blank areas bl, b2, b3, b4 can also travel the pulling wire 10, etc.; if the pulling wire 10 and the guiding wire 11 are not affected by each other, the pulling wire 10 and the guiding wire 11 can respectively travel in different chambers. In the room. As shown in Fig. 18C, since the adjacent two lenticular discs are opposite slopes in the region covered by d4, there is a certain distance d7, so that under the action of the guide wire 11 or the pulling wire 10 in a certain direction, The overall structure will be prone to bending. Under the action of several guiding wires 11 or pulling wires 10, the overall structure will easily bend in more directions; of course, the whole design is not limited to four bl-like blank areas (bl, b2) , b3, b4), can be increased and decreased according to the need of the bending direction; the setting position of the bl-like blank area can also be different, so that the tension and stress of the guiding wire 11 or the pulling wire 10 required for the deformation of the overall structure can be adjusted. For example, some bl-like blank areas may be closer to the blank area a1, so that the tension in the direction of the guide wire 11 or the pulling wire 10 will be greater; the bl-like blank area is in each The position of the double convex disc may also be different, or the same guiding wire 11 or the pulling wire 10 can travel in different bl-like blank areas in the whole structure, so that the bending shape of the entire structure can be adjusted, and distortion can be realized. . At the same time, as shown in Fig. 18D, adjacent two UFO-like disks can be provided with a d5 region, so that the overall structure is more susceptible to bending. By changing the size and number of the blank areas a1, bl, b2, b3, b4, and changing the sizes of dl, d2, d3, d4, d5, d6, d7, the hardness of each segment can be made different, for example, in Fig. 17A. If a segment is widened by dl, reducing d4 will make this segment not easy to deform. For example, if a segment is widened by d5, this segment will be easier to deform. In addition, this structural design is equally applicable to other cross-sectional non-circular structures, such as semi-circles, etc., but in this case, the influence of the asymmetrical structure on the hardness of the guide wire 11, the pulling wire 10, and the structure itself needs to be considered. Similarly, the essence of the lenticular disc overlap structure is also to selectively reduce or/and increase the resistance to bending on one or both sides of certain duct segments by reducing or/and increasing the internal structure of certain duct segments. To make it easier for the catheter to bend in some directions and/or to form certain curved forms.

Fig. 19 shows another design of the present invention which makes the bending easier to achieve by changing the structural design and thereby changing the hardness distribution. The design structure is an implementation of a chicken rib-like structure in a hollow tubular structure, which is preferably used for a hollow tubular structure (e.g., guiding catheter 7, etc.). The structure is achieved by changing the arrangement of the wire mesh in the tube wall of the ablation catheter 1 and the guiding catheter 7 in different catheter segments or by varying the thickness of the ablation catheter 1 and the guiding catheter 7 wall in different catheter segments. Of course, the wire mesh described herein should be understood as a design structure for reinforcing the wall hardness of the pipe wall, for example, a polymer material mesh, etc., so the essence of the design is to reduce or/and increase certain conduit segments. The structure of the wall, in turn, selectively reduces or/and increases the resistance to bending of one or both sides of certain conduit segments to make the catheter more susceptible to bending or forming certain curved configurations in certain directions. Fig. 19 is an illustration of changing the arrangement of the wire mesh in the tube wall of the ablation catheter 1 or the guiding catheter 7 in different catheter segments. As shown in Fig. 19A, the wire in the figure indicates a wire mesh. As can be seen from the lower left view of Fig. 19A, the wire mesh in the wall of the catheter tube completely covers the wall of the catheter tube, as can be seen from the upper left diagram of Fig. 19A. There is no wire mesh in one side of the pipe wall, and the two ducts are stacked at a small interval to form the structure shown in the right figure of Fig. 19A, because there is no wire mesh in one side wall of a small section of the upper pipe. Therefore, the catheter is more likely to bend to the side without the wire mesh. Of course, it is not limited to the design of the wire mesh in the side wall of the pipe. As shown in Fig. 19D, there are four S-shaped wires fl, f between the two small sections of the pipe with the complete wire mesh. 2, f 3, f 4 , can set the wire mesh between fl, f 2 and f 3, f4, and no wire mesh between f 2, f 3 and fl, f 4, so that the catheter is easier to There is no bending on both sides of the wire mesh. Similarly, only half of the wire mesh can be placed between each adjacent two S-shaped wires, so that the pipe is more easily bent in four directions without the wire mesh, and only four can be bent. The S-shaped wire without the wire mesh, so that the entire pipe will be easily bent in a plurality of directions, if the guide wire 70, the pulling wire 10 or the guide wire 11 in the four directions is matched, it is possible to control the multi-directional bending. In addition, it is not limited to the case where there is no wire mesh on one side or some sides of some small pipe walls. This can be achieved by changing the aperture, density, width and width of the wire mesh. One side or some sides of the duct wall are softer or harder than the other duct walls; the number of S-shaped wires can be adjusted according to the situation, and the S-shaped wire can also be in other forms, such as "Z" shape. The structure of Fig. 19A can be arranged in a side view as shown in Fig. 19B, so that the bending direction of the entire duct section will be uniform; the structure of Fig. 19A can be arranged in accordance with the side view shown in Fig. 19C, so that the entire duct section Inconsistent bending directions of the upper and lower portions, in this way, a complicated bending can be achieved by means of a guide wire 70, for example, passing the guide wire 11 through the region where d3 and d3' intersect in Fig. 19C will effect S-shaped bending. As shown in Fig. 19B and Fig. 19C, it is also possible to change the difficulty of bending each section of the catheter by adjusting the widths of dl, d3, d3', d4, d5. In addition, the entire structure is not limited to the case where the cross section of the conduit is circular. When the cross section of the conduit is semicircular, square or the like, the design can still be designed according to the idea, but in this case, the shape of the traction wire 10 and the guide wire 11 need to be considered. The influence of the hardness of the guide wire 70 and the chicken rib-like structure itself.

The manner in which the ablation catheter 1 and the guiding catheter 7 are hardened by the structural design shown in Figs. 17, 18, and 19 can also be achieved by changing the hardness of the manufactured material. For example, the cross sections of the segments of the catheter can be The design of Figure 17B, but the cross-section d3, d4 of some segments of the region of the manufacturing material is harder than the other segments, then these segments will not easily bend, for example, in the structure shown in Figure 33D, the second The material of the lenticular disc is softer than the first and third, so the bend will be more likely to occur in the second UFO-like disc.

Figure 20, Figure 21, and Figure 11 show the ablation of the present invention by taking two independent structures 8 as an example and combining the hardness division adjustment. The wire control structure of segment 6. The blank portion on the individual structure 8 in Figs. 20, 21, and 11 should be understood as a decrease in the hardness of the structure of the independent structure 8 at a certain distance. This hardness reduction can be achieved not only by changing the structural design but also by changing the hardness of the material. Way to achieve. For the case where only the prefabricated deformation is set, only the line control structure in Fig. 20, Fig. 21, Fig. 22 needs to be removed.

Figure 20 is a diagram showing the remote control of the ablation section 6 of the present invention with the distal end of the two separate structures 8 attached to the ablation section head end 17 as an example. As shown in Fig. 20D, when the pulling wire 10 travels outside the independent structure 8, the head end fixing point 110 of the pulling wire 10 is preferably disposed at the ablation section head end 17 and travels along the long axis center line of the ablation section 6, pulling Preferably, the filament 10 also travels in the ablation catheter 1 other than the ablation section 6 on the long axis centerline, in which case only one traction wire 10 is preferred. As shown in FIGS. 20A, 20B, and 20C, when the pulling wire 10 travels in the independent structure 8, the head end fixing point 110 of the pulling wire 10 is preferably disposed between the ablation section head end 17 and the ablation head 9 independently. 8 (including the end points), shown in the figure is fixed to the ablation section head end 17, the traction wire 10 can travel along the independent structure 8 by the ablation section 6 long axis centerline, as shown in the figure In the case of two separate structures 8, one traction wire 10 is provided in each of the individual structures 8, and for more than two separate structures 8, at least two traction wires 10 may be respectively disposed in the opposite independent structure 8 or in each Each of the individual structures 8 is provided with a pulling wire 10 which is preferably combined into one in the ablation catheter 1 other than the ablation section 6, and preferably travels to the long axis centerline of the ablation catheter 1 section. As shown in Fig. 15, the pulling wire 10 can also travel along the portion of each of the independent structures 8 away from the center line of the long axis of the ablation section 6, at which time the pulling wire 10 can function as the guiding wire 11; for the two independents shown in Fig. 15. In the case of structure 8, one traction wire 10 is provided in each individual structure 8, and for more than two separate structures 8, at least two traction wires 10 may be respectively in the opposite independent structure 8, or in each Each of the individual structures 8 is provided with a pulling wire 10; as shown in Fig. 15, the pulling wire 10 serving as the guiding wire preferably travels separately in the ablation catheter 1 except for the ablation section 6, does not merge into one, and preferably travels. In the section of the ablation catheter 1 corresponding to the center line of the long axis, if the tension of all the traction wires 10 is simultaneously increased or the independent structure 8 is prefabricated, the traction wire of the traction wire 10 is exerted. The effect of each of the traction wires 10 is increased or the stress of each traction wire 10 is increased to play the role of the guide wire. In combination with the structural design, as shown in FIG. 20A, the two independent structures 8a, 8b are symmetrical with each other, and in order to facilitate the outward bulging of the two independent structures 8a, 8b of the semi-cylindrical shape, FIG. 17 or/and The chicken rib-like structure illustrated in Fig. 19, when the chicken rib-like structure illustrated in Fig. 17 is used, the independent structure 8 can adopt the design shown in Fig. 17D, wherein the shape of the cross section indicated by the broken line cc is preferably Fig. 17D. As shown, at this time, if the pulling wire 10 travels in the independent structure 8, it travels to the blank area bl shown in Fig. 17D; when the chicken rib-like structure shown in Fig. 19 is used, the blank portion in the independent structure 8 should be understood. The structural rigidity of the wall of the independent structure 8 is separated by a certain distance, for example, by removing the wire mesh, changing the density of the wire mesh, and the like. As shown in Fig. 20B, Fig. 20C, and Fig. 20D, the bending forms of the two independent structures 8 can also be asymmetric, which is necessary for more than two independent structures 8, which helps to make the ablation points different. The renal artery cross-section; similar to the chicken-ribbed structure shown in Fig. 19, the design shown in Fig. 20B, Fig. 20C, and Fig. 20D can also be designed with the chicken rib-like structure shown in Fig. 17 or/and Fig. 19, To achieve different bending modes, the hardness of each segment can be different by adjusting the arrangement of the chicken rib-like structure on each individual structure 8. In the place where the curvature is large, the hardness is preferably small, and the bending is more easily realized. The blank portion of the individual structures 8a, 8b in Fig. 20 indicates the portion having a small hardness on each of the individual structures 8, so that the size of the blank portion on the individual structures 8a, 8b, the shape, the density of the portions, etc. can be adjusted to change the structure of the chicken rib-like structure. The hardness distribution, which in turn changes the bending shape. As shown in Fig. 20B, the portion of the ablation head 9 to the end of the individual structure 8a in the independent structure 8a and the portion of the ablation head 9 to the ablation section head end 17 in the independent structure 8b have a larger curvature, so that the blank portion is also larger and denser. . Similarly, in Fig. 20C, in order to achieve the equal distance between the two ablation heads 9 and the long axis centerline of the ablation section 6 after the deformation of the independent structure 8, the independent structure 8b is designed to be nearly the same when the lengths of the two independent structures 8 are equal. The end is not easily bent and the distal end and the intermediate portion are susceptible to bending, so that the distal end and the intermediate portion of the separate structure 8b are also denser, making it more flexible. In Fig. 20D, the center line distances of the two ablation heads 9 to the long axis of the ablation section 6 after the deformation of the independent structure 8 are not equal. In the case where the lengths of the two independent structures 8 are equal, the most obvious part of the intermediate ridge of the independent structure 8 is The lengths of the two separate structures 8 are different, and the most obvious portion of the intermediate structure 8b is longer, which requires that the other portions of the independent structure 8b have a larger curvature and are more flexible, so the distal end and the proximal end of the independent structure 8b are blank. The parts are also larger and denser. As shown in FIG. 20, the shape of the blank portion may also be The shape may be as shown in FIG. 20B, or may be the shape shown in FIG. 20A, FIG. 20C, and FIG. 20D. Of course, the skilled person may design other shapes according to specific conditions. In addition, it is also possible to achieve that the ablation head 9 is disposed at different positions of the symmetrical two independent structures 8 to achieve an ablation point that is not coplanar. Fig. 20 illustrates the design of two independent structures 8 as an example, and therefore is not limited to the case of two independent structures 8, and the same applies to the case of more than two independent structures 8. For the case where the technician needs the separate structure 8 to form other curved forms, the blank portion of the independent structure 8 in Fig. 20 can be adjusted accordingly.

Fig. 21 shows an example in which the distal ends of the two independent structures 8 are separated from each other, and combined with the hardness division adjustment, the wire-controlled structure of the ablation section 6 of the present invention is shown. As shown in Fig. 21C, when the pulling wire 10 travels outside the separate structure 8, the pulling wire 10 preferably travels along the long axis centerline of the ablation section 6, in which case each individual structure 8 preferably requires a pulling wire 10, a pulling wire The head end fixing point 110 of 10 is preferably disposed on the ablation head 9 or the adjacent independent structure 8, and the head end fixing point 110 is located on the long axis center line of the ablation section 6, generally at 0-8 in the ablation head 9, for no setting The independent structure 8 of the ablation head 9, the head end fixing point 110 of the pulling wire 10 is preferably disposed on the head end of the independent structure 8 or the adjacent independent structure 8 thereof, and the head end fixing point 110 is located on the long axis center line of the ablation section 6, generally The distance between the 8 ends of the independent structure is 0-8; as shown in Fig. 21, the traction wires 10 are preferably combined into one in the ablation catheter 1 except the ablation segment 6, and preferably travels to the ablation catheter 1 segment. The long axis centerline. As shown in FIG. 21A, FIG. 21B, and FIG. 21D, when the pulling wire 10 travels in the independent structure 8, the head end fixing point 110 of the pulling wire 10 is different depending on the traveling path of the pulling wire 10; 21A and 21B, when the pulling wire 10 travels within the independent structure 8 of the long axis centerline of the ablation section 6, the head end fixing point 110 is preferably disposed on the ablation head 9 or the adjacent independent structure 8, the head end. The fixed point 110 is located on the long axis centerline of the ablation section 6, generally at 0-8 in the ablation head 9, and for the independent structure 8 without the energy contacts, the head end fixed point 110 is preferably disposed at the end of the independent structure 8 or On the adjacent independent structure 8, the head end fixing point 110 is located on the long axis center line of the ablation section 6, and generally the head end of the independent structure 8 is hidden at 0-8; as shown in Fig. 21D, when the pulling wire 10 is away from the ablation section 6 When traveling in the independent structure 8 of the long axis center line, the head end fixing point 110 is preferably disposed on the ablation head 9 or the adjacent independent structure 8, and the head end fixing point 110 is away from the long axis center line of the ablation section 6, generally ablated Head 9 is hidden at 0-8, for independent structure 8 without energy contacts The head end fixing point 110 is preferably disposed on the independent structure 8 at the head end of the independent structure 8, or the head end fixing point 110 is away from the long axis center line of the ablation section 6, and the distance from the head end of the independent structure 8 is generally 0-8. As shown in Fig. 21, the traction wires 10 are preferably combined into one in the ablation catheter 1 section other than the ablation section 6, and preferably travels to the long axis centerline of the ablation catheter 1 section. 21A, 21B, and 21C will mainly rely on increasing the stress of the traction wire 10 (i.e., pushing the traction wire 10 or the portion of the retraction ablation catheter 1 other than the traction wire 10) to achieve independent structure 8 away from each other and finally ablation head 9 and blood vessel. Wall contact, while Figure 41C will rely primarily on increasing the tension of the traction wire 10 (i.e., pulling the traction wire 10 or the portion of the ablation catheter 1 other than the traction wire 10) to achieve independent structure 8 away from each other and ultimately ablation head 9 and vessel wall Contact; of course, if the initial deformation of the independent structure 8 is made to be away from each other, FIGS. 21A, 21B, and 21C will mainly rely on increasing the tension of the pulling wire 10 to realize that the distal ends of the independent structures 8 are close to each other such that the ablation head 9 and the blood vessel wall Separating; and Fig. 21D will mainly rely on increasing the stress of the pulling wire 10 to achieve the separation of the distal ends of the independent structures 8 so that the ablation head 9 is separated from the blood vessel wall. If the ablation head 9 is brought into closer contact with the blood vessel wall, the pulling wire 10 can also be increased. The tension. As shown in Fig. 21, in order to make the independent structure 8 more susceptible to bending under the action of the pulling wire 10 and to facilitate the contact of the ablation head 9 with the blood vessel wall, it is similar to the aforesaid independent structure 8 connected to the ablation section head end 17, preferably using a chicken rib-like shape. The structure, the chicken rib-like design shown in FIG. 17 or/and FIG. 19 can be used; wherein the blank portion is arranged on the independent structure 8 shown in FIGS. 21A, 21B, and 21C in the ablation section of the independent structure 8 6 part of the centerline, and in the portion of the independent structure 8 shown in Fig. 21D where the head end is fixed at a point 110 to the proximal end of the individual structure 8, the blank portion will be arranged in a portion of the separate structure 8 away from the centerline of the ablation section 6; In the illustrated separate structure 8 on the portion of the tip end fixed point 110 to the distal end of the separate structure 8, the primary purpose of the blank portion is to protect the vessel wall by making the portion susceptible to bending buffering the pressure of the ablation head 9 in contact with the vessel wall. . 21B, 21C, and 21D illustrate two different structures 8 as an example of how to achieve ablation points on different renal artery cross sections. As shown in Fig. 21B, at this time, the lengths of the two independent structures 8a, 8b are equal, and the internal structure is substantially mirror-symmetrical, except that the fixing position of the ablation head 9 is different, and the ablation head 9a on the independent structure 8a is closer. In this way, the ablation point can be achieved on different renal artery cross-sections. As shown in FIG. 21C and FIG. 21D, two independent structures 8a, 8b of unequal length may also be used, as two The lengths of the individual structures 8 are different and the ablation heads 9 are disposed at the head of each individual structure 8, so that the ablation points can also be realized on different renal artery cross-sections; FIG. 21C differs from FIG. 21D mainly in FIG. 21C. The lengths of the traction wires 10 are shown to be equal, while the lengths of the traction wires 10 shown in Fig. 21D are not equal. Fig. 21 is an illustration of two independent structures 8 as an example. Therefore, it is not limited to the case of two independent structures 8, and the same applies to the case of more than two independent structures 8. Further, for the case where the technician needs the independent structure 8 to form other curved forms or the case where the control of the pulling wire 10 to the independent structure 8 is required, the blank portion of the independent structure 8 in Fig. 21 can be adjusted accordingly.

Fig. 22 is an illustration of two independent structures 8 combined with hardness section adjustment, showing the characteristics of the wire control structure in the middle of the independent structure 8 in the present invention when the middle portion is connected to the distal end and then separated from each other. As shown in FIG. 22A, when the pulling wire 10 travels outside the independent structure 8, the head end fixing point 110 of the pulling wire 10 is preferably disposed on the head end of each independent structure 8 or its adjacent independent structure 8, the head end fixing point. 110 depends on the long axis centerline of the ablation section 6, generally at a distance of 0-8 from the head end of the independent structure 8. If the ablation head 9 is disposed at the head of the independent structure 8, the head end fixed point 110 is preferably located at the ablation head 9 or On the adjacent independent structure 8, the head end fixing point 110 is located on the long axis center line of the ablation section 6, generally 0 to -8 mm from the ablation head 9, and each of the independent structures 8 is preferably provided with a pulling wire 10, and these pulling wires are provided. 10 reversing at the distal end of the head end fixed point 110 into a traction wire that travels along the long axis centerline of the ablation section 6, through the attachment point 18 of the separate structure 8, and ultimately in the controllable curved section. 5 Enters the ablation catheter 1 and thereafter travels along the long axis centerline of the ablation catheter 1. As shown in FIG. 22B, when the pulling wire 10 travels in the independent structure 8, the head end fixing point 110 of the pulling wire 10 is preferably disposed on the independent structure 8 disposed at or adjacent to the head end of each of the independent structures 8, the head The end fixing point 110 is away from the long axis center line of the ablation section 6, and is generally hidden from 0 to 8 at the head end of the independent structure 8. If the ablation head 9 is disposed at the head of the independent structure 8, the head end fixing point 110 is preferably located at the ablation head. 9 or its adjacent independent structure 8, the head end fixed point 110 is away from the long axis centerline of the ablation section 6, generally at 0-8 hidden from the ablation head 9; the traction wire 10 is along the individual structures 8 as far as possible before the connection point 18. Moving away from the portion of the long axis centerline of the ablation section 6, the traction wire 10 travels along the portion of the long axis centerline of the ablation section 6 along each of the individual structures 8 as far as possible after the connection point 18, preferably in each individual structure 8 A traction wire 10 is provided which preferably merges into one of the ablation catheters 1 except for the ablation section 6, and preferably travels the longitudinal axis of the ablation catheter 1 section. As shown in Fig. 22C, when the portion of the pulling wire 10 travels within the separate structure 8 and partially travels outside of the individual structure 8, it is preferred to run within the separate structure 8 at a portion prior to the point of attachment 18 of the individual structure 8, and along each The independent structure 8 travels away from the portion of the long axis centerline of the ablation section 6, and then merges into a pulling wire 10 at the joint 18, travels outside the independent structure 8, and travels along the long axis centerline of the ablation section 6, ultimately in controlled bending. The segment 5 enters the ablation catheter 1 and thereafter preferably travels along the long axis centerline of the ablation catheter 1; as shown in Figure 22C, the tip end fixation point 110 of the traction wire 10 is preferably placed at the tip end of each individual structure 8 or On the adjacent independent structure 8, the head end fixing point 110 is away from the long axis center line of the ablation section 6, and is generally hidden from 0 to 8 at the head end of the independent structure 8. If the ablation head 9 is disposed at the head of the independent structure 8, the head The end fixation point 110 is preferably located on the ablation head 9 or its adjacent independent structure 8, the head end fixation point 110 being remote from the long axis centerline of the ablation section 6, generally at 0-8 from the ablation head 9. Figure 22 will rely primarily on increasing the tension of the traction wire 10 (i.e., pulling the traction wire 10 or the portion of the forward ablation catheter 1 other than the traction wire 10) to achieve that the distal ends of the individual structures 8 are remote from each other and that the middle and the tail are similarly spindle-shaped, and Eventually the ablation head 9 is brought into contact with the vessel wall. As shown in Fig. 22A, Fig. 22B, and Fig. 22C, in order to make the independent structure 8 more susceptible to bending in the case where the stress of the pulling wire 10 is increased to facilitate the contact of the ablation head 9 with the blood vessel wall, it is preferable to use a chicken rib-like structure, independent of the foregoing. The structure 8 is similar to the ablation section head end 17 and is similar to the chicken rib-like structure shown in FIG. 17 or/and FIG. 19; wherein the connection point 18 to the head end fixing point 110 shown in FIG. 22A is independent. The blank portion of the structure 8 is arranged in the portion of the independent structure 8 which is centered on the ablation section 6, and on the independent structure 8 of the connection point 18 to the head end fixed point 110 illustrated in Figs. 22B and 22C, the blank portion is arranged independently. The portion of the structure 8 that is away from the centerline of the ablation section 6; the portion of the independent structure 8 illustrated in Figures 22A, 22B, and 22C that is fixed to the distal end of the individual structure 8 and the blank portion disposed adjacent to the ablation section 6 The main purpose of the portion of the centerline is to protect the vessel wall by exposing the portion to the pressure of the bending buffer ablation head 9 in contact with the vessel wall. 22D, 22E, and 22F illustrate how the ablation points are on different renal artery cross-sections by taking two separate structures 8 and pulling the wire 10 in the separate structure 8 as an example. As shown in Fig. 22D, at this time, the lengths of the two independent structures 8a, 8b are equal, the structure is substantially mirror-symmetrical, except that the fixed position of the ablation head 9 is different, and the ablation head 9a on the independent structure 8a is closer to independence. The distal end of structure 8, through this The way to achieve ablation points in different renal artery cross sections. As shown in FIG. 22E and FIG. 22F, two independent structures 8a, 8b of unequal lengths may also be used, and the portions of the two independent structures 8 at the distal end of the connection point 18 to the independent structure 8 are preferably unequal lengths, and the connection points are The portion of the proximal end of the individual structure 8 is preferably of equal length; since the lengths of the portions of the two separate structures 8 at the distal end of the joint 18 are different and the ablation heads 9 are disposed at the head of each individual structure 8, it is also possible The ablation points are on different renal artery cross-sections; Figure 22E differs from Figure 22F primarily in that the lengths of the two traction wires 10 shown in Figure 22E are equal, while the lengths of the two traction wires 10 shown in Figure 22F are not equal. Figure 11 illustrates the design of two separate structures 8 and is therefore not limited to the case of two separate structures 8, as is the case for more than two independent structures 8. 22D, 22E, and 22F are illustrated by taking two independent structures 8 and the pulling wire 10 running in the independent structure 8 as an example, and thus are not limited to the case of two independent structures 8, for more than two The same applies to the case of the individual structure 8, and is also not limited to the case where the pulling wire 10 travels within the individual structure 8, as is the case with the pulling wire 10 running outside the partial structure 8 or partially running outside the independent structure 8. Further, for the case where the technician needs the separate structure 8 to form other curved forms, the blank portion of the cross-sectional view in Fig. 47 and the blank portion of the independent structure 8 in Fig. 48 can be adjusted accordingly.

Depending on the circumstances, the skilled artisan may incorporate, modify and cross-use the design of the traction wire 10 and the blank portion described above, and such equivalent variations and modifications are also within the scope defined by the claims of the present invention.

Fig. 23 is an example of a structure in a C-shaped curved design, showing how the present invention can easily realize the design change by adjusting the hardness distribution of the controllable curved section 5. The blank portion of the controllable curved section 5 in Fig. 23 is understood to mean that the structural hardness of the controllable curved section 5 is reduced by a certain distance. This hardness reduction can be achieved not only by changing the structural design but also by changing the hardness of the material. Therefore, the hardness distribution of the controllable curved section 5 can be changed to make it more flexible by adjusting the size, shape, and partial density of the blank portion on the controllable curved section 5. When the controllable curved section 5 is of a C-shaped curved design, it is preferable to design the structure of the controllable curved section 5 according to the number of required bending directions, and FIGS. 23A, 23B, and 23C control the direction by the tension wire 11 by increasing the tension. The bending is taken as an example, wherein FIG. 23B and FIG. 23C are enlarged side views of the chicken rib-like structure of the controllable curved section 5. As shown in Fig. 23A, the tip end fixing point 111 of the guide wire 11 is preferably disposed at a position where the controllable curved section 5 is near the ablation section 6 and is located at the centrifugation side on the side of the bending direction, which is independent of the meaning shown in Figs. 20, 21, and 22. The design of the structure 8 is similar, and the controllable curved section 5 is also preferably a chicken rib-like structure; when the chicken rib-like structure shown in Fig. 17 is used, the controllable curved section 5 can adopt the design shown in Figs. 17A and 17B. The cross-sectional shape of the cross section indicated by the broken line ccl in FIG. 23B is preferably as shown in FIG. 17B. In this case, if the guide wire 11 travels within the controllable curved section 5, it is preferable to travel as shown in FIGS. 17A and 17B. The blank area bl, that is, the part d3 in FIG. 23B and FIG. 23C, of course, the guide wire 11 can also travel outside the controllable curved section 5 or partially outside the controllable curved section 5 according to the situation; In the chicken rib-like structure, the blank portion of the controllable curved section 5 in FIGS. 23A, 23B, and 23C should be understood as a decrease in the hardness of the structure of the controllable curved section 5 at a certain distance from the wall, for example, by removing the wire mesh and changing the metal. The density of the screen, etc., the guide wire 11 preferably walks On the curved side of the controllable curved section 5; if the direction of the bend is opposite to the direction indicated by the arrow aol in Fig. 23B (i.e., the direction indicated by the arrow ao2), the design shown in Fig. 23C can be used, and the guide is used. The wire 11 also travels in the d3 part. If the controllable bending section 5 is bent by pushing the guiding wire 11 or the retracting ablation catheter 1, that is, increasing the stress of the guiding wire 11, the direction in which the bending occurs in the same design will be caused by the increase of the tension of the guiding wire 11. The bending direction of the controllable curved section 5 is opposite. If it is required that the controllable curved section 5 is relatively easy to bend to both sides, the design shown in FIG. 23D can be used, that is, the opposite sides of the controllable curved section 5 are preferably disposed respectively as shown in FIG. 17 or/and FIG. Chicken rib-like structure; When the rib-like structure shown in Fig. 17 is used, the design is similar to that shown in Fig. 17C, except that the size of each area is slightly adjusted (as shown in the middle of Fig. 23D), and the two guide wires 11 are preferably Moving the blank areas bl and b2 shown in the middle section of Fig. 23D respectively, since the hardness of both sides of the bendable curved section 5 is relatively small, increasing the tension of the side guide wire 11 will cause the controllable curved section 5 to the side. Bending, while increasing the stress of a certain side guide wire 11 will bend the controllable curved section 5 to the opposite side; when the chicken rib-like structure shown in Fig. 19 is used, the blank portion of the controllable curved section 5 in Fig. 23D should be understood as The structural rigidity of the controllable curved section 5 at a certain distance from the wall is reduced, for example, by removing the wire mesh, changing the density of the wire mesh, etc., the guide wire 11 preferably travels on the curved side of the controllable curved section 5. As shown in the left and right side views of Fig. 23D, the arrangement of the chicken rib-like structures on both sides is not necessarily completely symmetrical, and may have a certain misalignment. For the traction wire 10 shown in Figure 29 The controllable curved section 5 in the design of the swinging wire 11 can be designed as shown in Fig. 23D. If the chicken rib-like structure shown in Fig. 17 is used, the two pulling wires 10 preferably travel in blank areas respectively. Bl and b2, if the chicken rib-like structure shown in Fig. 19 is used, the two pulling wires 10 preferably travel on the curved side of the controllable curved section 5. For the design of the multi-directional control bending (greater than or equal to 3 directions), the hollow curved section 5 can adopt the design of the double convex disk overlapping structure illustrated in FIG. 18, and the guiding wire 11 travels through the bl-like blank area (bl, B2, b3, b4), the number of bl-like blank areas can be increased as needed. Of course, the hollow curved section 5 can also use the chicken rib-like structure shown in Fig. 19D to help control the multi-directional bending. When the controllable curved section 5 is S-shaped curved design, it can be similar to the C-shaped curved design. The technician can adjust the size, shape, and partial density of the blank portion on the controllable curved section 5 according to the actual situation to change the bending shape.

Figure 24 shows the main design features of the tail of the guiding catheter 7 of the present invention. As shown in Fig. 24A, according to actual needs, the end (tail end, proximal end) of the guiding catheter 7 can be provided with a side hole 77, which is connected with a section of the catheter 20 and connected to a syringe or a liquid injection device, a syringe or a syringe. The fluid device can be intravascularly injected or injected with an intravascular contrast agent through the side hole 77, and the catheter 20 is closed when the side hole 77 is not in use. As shown in Figures 24A, 24B, and 24C, the tail of the guiding catheter 7 is preferably sealed, such as a sealing jaw or sealing sleeve 79, to prevent blood from leaking through the guiding catheter 7 and to be injected intravascularly through the guiding catheter 7. The drug or the injected contrast agent leaks out, wherein Figs. 24A and 24B show the case where the ablation catheter 1 is not inserted, Fig. 24C shows the case where the ablation catheter 1 is inserted, and Fig. 24B and Fig. 24C show the tail of the guide catheter 7. In addition, there is preferably a reinforcing sleeve 78 around the tail of the guiding catheter 7, so that the tail portion of the guiding catheter 7 is not easily deformed, is easy to operate, and is also convenient to be connected or attached to other structures.

The guiding catheter 7 itself can also undergo one-way or multi-directional active control deformation or/and passive control deformation, as well as prefabrication deformation. As shown in FIG. 24A, in the case where the guiding catheter 7 is only prefabricated, it is preferable not to provide the guiding catheter control handle 27 (described later), and only the connecting joint 76 is provided at the end, and the connecting joint 76 can be combined with the syringe and the liquid filling device. , ablation catheter 1 and other connections. The active control deformation of the guiding catheter 7 is preferably achieved by incorporating a smart material (e.g., a shape memory alloy) on the wall of the guiding catheter 7, for example: 形状 Designing a distribution scheme using a shape memory alloy. The passive control deformation of the guiding catheter 7 is preferably achieved by a wire-controlled structural design and a magnetron structure design; wherein the wire-controlled structure is designed to penetrate the guiding wire 70 in the wall of the guiding catheter 7 (similar to the ablation catheter 1) The guide wire 11) is realized; in addition, in order to facilitate the formation of the designed deformation shape of the guiding catheter 7, the hardness distribution of the guiding catheter 7 can also be changed. Fig. 25 shows the main structural features of the guiding structure design of the guiding catheter 7 in the present invention and how to optimize the formation of the guiding catheter 7 by adjusting the hardness distribution of the guiding catheter 7. A guide wire 70 is provided in one side wall of the guiding catheter 7, when the tension of the guiding wire 70 is increased (the pulling guide wire 70 or the other portion of the feeding guide catheter 7 except the guiding wire 70) ), the guiding catheter 7 will be bent toward the side where the guiding wire 70 is disposed, that is, the direction indicated by the arrow aol in the figure, and if the multi-directional control bending is required, the guiding can be separately set in several directions of the guiding catheter 7. Silk 70. In order to facilitate the formation of the desired deformation mode of the guiding catheter 7, the hardness distribution of the guiding catheter 7 can be changed. This change in hardness distribution can be achieved not only by changing the structural design but also by changing the hardness of the material.

FIG. 26 is a schematic diagram showing the main structural features of the control handle 2 in the case where the control handle 1 can control the bending of the controllable curved section 5 in one direction, wherein FIG. 26B and FIG. 26C are respectively the broken line ccl in FIG. 26A. , cc2 cross section enlarged view. As shown in Fig. 26A, the control handle 2 is preferably designed in a shape, mainly composed of an operating handle 211 and an operating handle 257, wherein the operating handle 211 is generally located at the front of the control handle 1, and is mainly responsible for controlling the controllable curved section 5. The deformation, and the operating handle 257 is generally located at the rear of the control handle 1, and is mainly responsible for controlling the deformation of the independent structure 8. The operating handle 211 and the operating handle 257 are preferably hollow structures. As shown in Fig. 26A, the ablation catheter 1 is connected to the operating handle 211 via a catheter body section 4 (shown in Fig. 1), similar to the reinforcing sleeve 78 of the guiding catheter 7, and a reinforcing sleeve 48 is also provided at the proximal end of the ablation catheter 1, The place where the ablation catheter 1 is connected to the control handle 2 is not easily deformed and is easy to handle. As shown in FIG. 26A, the operating handle 211 is provided with a control button 230 for controlling the deformation of the controllable curved section 5. The control button 230 surrounds a part of the operating handle 211 and can slide on the operating handle 211, since the control button 230 is stuck. The handle 211 is operated so that the control knob 230 does not slide out of the operating handle 211. As shown in Fig. 26A, the guide wire 11 is connected to the guide wire fixing disk 204 on the control knob 230 via the connecting passage 217 on the operating handle 211, and when the control button 230 slides in the direction indicated by the arrow aol, the guide wire can be pulled. 11. As shown in FIGS. 26A and 26C, the wire fixing disk 205 is located at the intersection of the connecting rods 258 which are radially expanded in cross section, and the connecting rod 258 is connected. A plurality of guiding grooves 258 passing through the operating handle 257 are connected to the ring control button 257. The ring control button 257 surrounds the operating handle 257 to facilitate control of the ring control button 257 while rotating. Since the guiding groove 258 can restrict the rotation of the connecting rod 258, Therefore, the ring control button 257 and the operating handle 21 3 can be rotated together; the number of the connecting rod 258 and the guiding groove 258 is not necessarily four, and can be adjusted according to actual needs. As shown in Fig. 26A, the energy exchange joint 201 is preferably disposed at the tail of the control handle 2, and the energy exchange joint 201 is connected to the ablation generating device 3 via a cable 23 (including a wire, a catheter, an optical fiber, etc., as shown in Fig. 1), and is responsible for receiving The energy transmitted by the ablation generating device 3 and transmitted to the ablation head 9 through the wires, catheters, optical fibers ac, etc. in the control handle 2, the other portions of the ablation catheter 1 that require energy supply, and the control handle 1 require energy supply. part. As shown in Fig. 26A, a liquid perfusion joint 202, which is connected to a catheter in the ablation catheter 1 for providing cooling fluid, contrast agent or the like to the ablation catheter 1, may also be provided at a position adjacent to the energy exchange joint 201, as the case may be. As shown in Fig. 26A, the operating handle 211 and the operating handle 257 are connected by a slot sliding structure indicated by a broken-line rectangular frame ar in the figure. The slot sliding structure is formed by the annular hook-shaped structure 212 at the rear of the operating handle 211 and the handle 257. The annular hook-like structures 256 are formed to coincide with each other, so that the two can be relatively rotated after the connection. In order to prevent the guide wire 11 from being excessively pulled to cause bending of the ablation catheter 1 and the blood vessel wall, it is preferable to provide a cushioning structure, for example, to replace the middle portion of the guide wire 11 traveling in the connecting passage 217 with a spring or a thin elastic wire. 26 is an example of the spring 208; as shown in FIG. 26A, the connecting passage 217 at the spring 208 is slightly thicker than the spring 208, and the control button 230 slides the pulling guide 11 in the direction indicated by the arrow aol. When the spring 208 can be extended, the buffering force can be buffered, and since the diameter of the spring 208 is larger than the diameter of the connecting channel 217, the spring 208 does not extend beyond the bulk of the connecting passage 117. This makes the tension of the guide wire 11 not exceed the tensile force generated by the maximum extension distance of the spring 208, which is equivalent to setting a tensile limit; similarly, such a design idea can also be applied to other wire-controlled structures. For example, the middle section of the pulling wire 10 in the control handle 1 is replaced by a spring or a thin elastic wire. As shown in Fig. 26A, the pulling wire 10 is placed inside the small chamber 207. A section of the front portion of the handle 1 is replaced by a spring 209. When the ring control button 257 slides the pulling wire 10 in the direction indicated by the arrow ao2, the spring 209 can be extended, which can buffer the pulling force, and the like. Since the diameter of the spring 209 is larger than the diameter of the opening at both ends of the small chamber 207, the spring 208 does not extend beyond the small chamber 207. Of course, in order to prevent the traction wire 10 and the guide wire 11 from being excessively pulled or/and pushed to cause bending of the ablation catheter 1 to damage the vessel wall, a tension sensor may be connected to the traction wire 10 and the guide wire 11. In order to control the rotation of the ablation catheter 1 through the control button 230, it is preferable that the control knob 230 and the operating handle 211 can be rotated together. At this time, it is preferable to provide a groove sliding structure between the control button 230 and the operating handle 211; as shown in Fig. 26B, The small dashed rectangular frame rc indicates the slot sliding structure. The position of the slot sliding structure is different from the position of the groove 216 and the groove 284. Preferably, the slot sliding structure is evenly distributed on the circumference; the large dotted line in FIG. 26B The rectangular frame shows an enlarged view of the groove sliding structure, and the groove sliding structure is composed of a groove 285 and a protruding tooth 286. FIG. 26B is an example in which the groove 285 and the protruding tooth 286 are respectively disposed on the control button 230 and the operating handle 211. For example, the groove 285 and the protruding tooth 286 can be respectively disposed on the operating handle 211 and the control button 230 according to a specific situation; such a slot sliding structure ensures that the control button 230 can freely slide on the operating handle 211. At the same time, the control button 230 can also drive the operating handle 211 to rotate. For convenience of operation, the control button 230 can be marked on the operating handle 211 or/and the control button 230 by the moving distance and the moving direction. The operating handle 211 can be marked on the operating handle 211, the operating handle 257 or/and the control button 230. The relative rotation angle and the direction of rotation of the operating handle 257 indicate the movement distance and the moving direction of the ring control button 257 on the operating handle 257 or/and the ring control button 257. For the case where the controllable curved section 5 is formed into an S-shaped bend by adding a guide wire 11' at the second bend, the guide wire 11' can be connected to the guide wire fixing disk 204 of the guide wire 11 on the control knob 230, Thus pulling the guide wire 11 will simultaneously pull the guide wire 11', and of course, the degree of tightness of the guide wire 11' and the guide wire 11 can be adjusted, so that the guide wire 11 or the guide wire 11' can be pulled first; The guide wire 11' can also be finally fixed to a separate position on the control button 230 via a separate connecting channel. For the case where the controllable curved section 5 or/and the independent structure 8 are controlled by the magnetron structure design, the corresponding line control structure in the design scheme of the control handle 1 illustrated in FIG. 26 is removed, and the control button 230 is changed for control. The passive control deformation of the magnetron structure design of the controllable curved section 5 changes the ring control knob 257 to a passive control deformation for controlling the design of the magnetron structure of the individual structure 8. For the case where the controllable curved section 5 or/and the independent structure 8 are deformed by actively controlling the deformation, the corresponding wire control structure in the design of the control handle 2 illustrated in FIG. 26 is removed, and the control button 230 is changed for control. Controlled bending The active control deformation of segment 5 changes the ring control knob 257 to control the active control deformation of the individual structure 8.

27 is an example of a wire control structure in which the guiding catheter control handle 27 can control the guiding catheter 7 to bend in one direction, and shows the main structural features of the guiding catheter control handle 27 and how to separate from the control handle 2. And bonding, FIGS. 27B and 27C are schematic cross-sectional views showing enlarged cross sections of the broken lines ccl and cc2. As shown in FIG. 27A, the guiding catheter control handle 27 is mainly composed of an operating handle 211', an operating handle 242 and a control button 230', wherein the design of the operating handle 211' and the control button 230' and the operating handle 211 and the control button 230 are shown. The design is similar, except that the guide wire 11 is replaced with a guide wire 70. As shown in Fig. 27A, the guide wire fixing plate 279 is disposed on the control button 230', and the guide wire 70 is connected to the guide wire fixing plate 279 on the control button 230' via the connecting passage 217' on the operating handle 211'. Similarly, a cushioning structure can be provided on the guide wire 70, for example, a section of the guide wire 70 is replaced by a spring 278, or a tension sensor is connected to the guide wire 70; when the control knob 230' slides in the direction indicated by the arrow ao The guide wire 70 will be pulled. In order to enable the control knob 230' to rotate together with the operating handle 211', it is preferable to provide a groove sliding structure as illustrated by the broken rectangular frame rc in Fig. 27B. As shown in Fig. 27A, similarly, the operating handle 211' and the operating handle 242 are connected by a slot sliding structure shown by a dashed rectangular frame arl, which is formed by an annular hook-like structure 212' on the operating handle 211' and The annular hook-like structures 241 on the operating handle 242 are formed to coincide with each other, so that the operating handle 211' and the operating handle 242 are relatively rotatable. In order to achieve engagement between the guiding catheter handle 27 and the control handle 2, the front end of the control handle 2 needs to be improved; as shown in Fig. 27D, the front end of the control handle 2 is provided with two hook-shaped latches 210a of inverted "L" shape. 210b, the two hook-shaped latches 210a, 210b are preferably disposed at opposite positions of the circumference; of course, the number and position of the hook-shaped latches 210 can be adjusted according to actual conditions. As shown in Fig. 27A, Fig. 27B, and Fig. 27C, the end of the operating handle 242 is provided with a card slot 243 for catching the hook-shaped latch 210. The card slot 243 has two slots, preferably disposed at opposite positions of the circumference, of course, if the hook The number and distribution of the shaped teeth 210 are adjusted, and the number and distribution of the slots 243 should be adjusted accordingly so that the hook-shaped latch 210 and the slot 243 can be smoothly engaged; the slot 243 is close to the handle The end of 242 is narrower (shown in Fig. 27C), and can pass through the hook-shaped latch 210; the slot 243 is wider away from the end of the handle 242 (shown in Fig. 27B), so the hook-shaped latch 210 is in the slot. 243 is far from the end of the operating handle 242 has a certain movable space; the inner diameter of the operating handle 211' is preferably just enough for the ablation catheter 1 to pass, the inner diameter of the operating handle 242 is slightly larger than the outer diameter of the ablation catheter 1, but slightly smaller than the ablation catheter 1 The outer diameter of the sleeve 48 allows the reinforcement sleeve 48 to snap into the handle 242. As shown in Figures 27A, 27B, 27C, and 27D, when the guiding catheter handle 27 and the control handle 2 are required to be engaged, the ablation catheter 1 penetrates into the empty conduit in the guiding catheter control handle 27 and then enters the guide. In the catheter 7, when the front end of the control handle 2 approaches the end of the guiding catheter handle 27, the hook-shaped latch 210 is aligned with the slot 243, and then the control handle 2 is pushed forward so that the hook-shaped latch 210 contacts the slot 243. The bottom of the control handle 2, the hook-shaped latch 210 will be locked in the wider position of the slot 243 away from the end of the operating handle 242, and then the reinforcing sleeve 48 has been snapped into the operating handle 242, thus guiding The guiding tube handle 27 and the control handle 2 can be stably engaged; when the guiding catheter control handle 27 and the control handle 2 are required to be separated, the control handle 2 is reversely rotated to make the hook-shaped engaging teeth 210 align with the narrowing of the card slot 243. Place, roll back the control handle 1. For the design of the guiding catheter control handle 27 illustrated in FIG. 27, the guiding catheter control handle 27 is replaced with the design of the front part of the control handle 2 illustrated in FIGS. 27 and 54 and the guide wire 11 is replaced with a guide. The wire 70 enables control of bidirectional or multi-directional bending of the guiding catheter 7. In order to facilitate the operation of the guiding catheter handle 27, the movement distance and movement of the control button 230' or the control panel 231' may be marked on the control knob 230' or the control panel 231' of the control guide wire 70, the operating handle 211'. Direction or rotation distance and direction of rotation, on the control button 230' or the control panel 231', on the operating handle 211', the operating handle 142 indicates the relative rotation angle and rotation direction of the operating handle 211' and the operating handle 242; The catheter handle 27 is engaged with the control handle 2, and the alignment line, the alignment mark, and the like, which are engaged with each other, can be respectively indicated on the guiding catheter control handle 27 and the control handle 2. For the case where the guiding guide 7 is deformed by the magnetron structure design, the corresponding wire control structure in the guiding catheter control handle 27 is removed, and the control knob 230' or the control panel 231' is changed to the magnetic force for controlling the guiding catheter 7. The passive control of the structural design is controlled, and an energy exchange joint for guiding the guide tube 7 and the guide catheter handle 27 to provide energy is provided at the guide catheter handle 27. For the case where the deformation of the guiding catheter 7 is controlled by the active control, the corresponding wire control structure in the guiding catheter control handle 27 is removed, and the control button 230' or the control panel 231' is changed to control the active control of the guiding catheter 7. Deformation, and an energy exchange joint for guiding the guide tube 7 and the guide catheter handle 27 to provide energy is provided at the guide catheter handle 27. The ablation catheter 1 and the outer surface of the guiding catheter 7 may be marked with a development scale to indicate the depth of the ablation catheter 1 and the guiding catheter 7 into the blood vessel and to facilitate indirect measurement of the length of the human body structure under imaging equipment such as ultrasound and X-ray, Width and so on. Different development marks may be provided on the ablation catheter 1 and the guiding catheter 7 for distinguishing different catheters under imaging devices such as ultrasound and X-ray. Different development marks are preferably provided on each of the individual structures 8 for distinguishing different independent structures 8 under ultrasound, X-ray, etc., for example, a separate structure 8 is marked with a triangle, and the other independent structure is marked with a square, or One independent structure 8 is labeled with three bands, and the other independent structure 8 is labeled with two bands. In addition, a development mark may be disposed on the ablation catheter 1 and the guiding catheter 7 for distinguishing different axial rotation states under imaging devices such as ultrasound and X-ray, for example, an ultrasound, X-ray is disposed on the left side of the ablation catheter 1. A short line that can be developed under the imaging device, and another short line that can be developed under the imaging device such as ultrasound or X-ray on the right side of the ablation catheter. When the ablation catheter 1 is in the horizontal position, the two short lines coincide, when the ablation catheter 1 When the axis rotates at a certain angle, the short lines are separated by a certain distance. In order to reduce the possibility of damage to the blood vessel by the ablation catheter 1 and the guiding catheter 7, preferably, the ablation catheter 1 and the guiding catheter 7 should be as smooth as possible in contact with the blood vessel wall, and the shape should be as smooth as possible, and the ablation catheter 1 Preferably, the head of the guiding catheter 7 is relatively soft.

The parts of the ablation catheter 1 and the guiding catheter 7 that may directly or indirectly contact the body fluid or tissue of the human body must meet the national standards for contacting the human body fluid or tissue, and may directly or indirectly be in contact with the human body fluid for failing to meet the above requirements. Or the portion of the ablation catheter 1 and the guiding catheter 7 that are in contact with the tissue, the outside of which must be wrapped with a material that meets the national standards for materials in contact with human body fluids or tissues. The material from which the ablation catheter 1 and the guiding catheter 7 may be in direct or indirect contact with the human body should be able to withstand at least one medical sterilization method. The ablation catheter 1 and the guiding catheter 7 may be insulatively in direct or indirect contact with the human body, and the insulating material may be overwrapped where insulation requirements are not met.

When the controllable curved section 5 is not provided with the controllable curved section 5, the catheter body section 4 can be used for exercise, and only the design of the controllable curved section 5 is applied to the catheter body section 4 can.

The skilled person can combine, improve and cross-use the design of the above-mentioned ablation catheter 1 and the guiding catheter 7 according to actual requirements, and these equivalent variations and modifications also fall within the scope defined by the claims of the present invention.

The skilled person can combine, improve and cross-use the design of the above-mentioned control handle 1 and the guiding catheter control handle 27 according to actual requirements, and these equivalent variations and modifications also fall within the scope defined by the claims of the present invention.

As shown in Figure 1, the ablation generating device 3 provides a corresponding form of energy for the ablation catheter 1, the guiding catheter 7, the control handle 2, and the portion of the guiding catheter handle 27 that requires energy supply, such as when the guiding catheter 7 is needed. When the smart material changes shape, the ablation generating device 3 can provide the energy required to induce the smart material to change shape. At the same time, the ablation generating device 3 can receive and process the information from the ablation catheter 1, the guiding catheter 7, the control handle 1, and the guiding catheter control handle 27. The processed information can be partially or completely displayed on the display 320 of the ablation generating device 3. And the processed information can also feedback adjust the energy output of the ablation generating device 3. The ablation generator comprises a radio frequency ablation generator, a resistance heating generator, a cryoablation generator, an ultrasound ablation generator, a laser ablation generator, and light. The power treatment generator or the microwave ablation generator may be one of the above generators or a combination of the above two or more generators. The control parameters of the ablation generating device 3 can be controlled by the display 320 of the ablation generating device or by the parameter setting button 330; the ablation generating device 3 should be provided with a connector for energy output and a connector 311 for sensor signal input, and A connector 321 is connected to the external power supply for receiving electrical energy transmitted by the power supply circuit. For the ablation catheter 1, the control handle 2, the guiding catheter 7 and the guiding catheter handle 27, an energy supply is provided without a device having a working switch on the control handle 1 or the guiding catheter handle 27, in the ablation generating device 3 A working switch is preferably provided. For the case of the ablation catheter 1 or/and the coolant, rewarming agent and perfusate required for the guiding catheter 7, the ablation generating device 3 or/and the guiding catheter 7 may be provided with a perfusion device for automatic or manual perfusion of the ablation catheter 1 The coolant, the rewarming agent and the perfusate, at which point the ablation generating device 3 should have a corresponding line communicating with a container providing a coolant, a rewarming agent and a perfusate material or finished product. The infusion device for connecting the distal end opening 77 of the guiding catheter 7 is provided in the ablation generating device 3, and the ablation generating device 3 should control the infusion device and set a corresponding control panel or control button. The ablation generating device 3 may be a whole machine that integrates the above functions, or may be a separate machine that performs different functions respectively, for example, the part that supplies the ablation head 9 is independently an extension, and the perfusion device is independently another extension. .

Claims

Rights request

1. A renal sympathetic denervation multifunctional ablation catheter system, characterized by including:

Ablation catheter (1), control handle (2) and ablation generating device (3), where the ablation catheter (1) includes a catheter body segment (4) and an ablation segment (6), where

The catheter body section (4) is connected to the control handle (2);

The ablation section (6) includes at least two independent structures (8), and an ablation head (9) is installed on at least one independent structure (8); the ablation head (9) passes through a wire, catheter, microwave antenna or optical fiber Connected to the energy exchange joint (201) on the control handle (2), the energy exchange joint (201) is connected to the ablation generating device (3) through wires, catheters, microwave antennas or optical fibers; the independent structure (8) is connected through Pull or/and push one end to be fixed on the independent structure (8), and the other end is deformed by the pulling wire (10) controlled by the handle to make the ablation head (9) fit or leave the designated ablation position; or the independent structure The structure (8) contains substances that can be attracted by magnets, and the independent structure (8) is deformed by an external magnetic field to cause the ablation head (9) to fit or leave the designated ablation position; or the independent structure (8) contains materials that pass through the external The smart material that deforms due to stimulation causes the ablation head (9) to fit into or leave the designated ablation position;

The control of the above independent structure (8) also includes the prefabricated deformation of the independent structure setting (8);

Or it includes an ablation catheter (1), a control handle (2), an ablation generating device (3), and a guiding catheter (7) that can be placed outside the ablation catheter (1), where the ablation catheter (1) includes a catheter body segment (4 ), and ablation segment (6), where:

The catheter body section (4) is connected to the control handle (2);

The ablation section (6) includes at least two independent structures (8), and an ablation head is installed on at least one independent structure (8).

(9); The ablation head (9) is connected to the energy exchange joint (201) on the control handle (2) through wires, catheters, microwave antennas or optical fibers, and the energy exchange joint (201) is connected through wires, catheters, microwaves The antenna or optical fiber is connected to the ablation generating device (3); the independent structure (8) is fixed on the independent structure (8) by pulling or/and pushing one end, and the other end is controlled by a pulling wire (10) controlled by a handle to deform. The ablation head (9) is made to fit or leave the designated ablation position; or the independent structure (8) contains substances that can be attracted by magnets, and the independent structure (8) is deformed by applying an external magnetic field to cause the ablation head (9) to be deformed. Fit or leave the designated ablation position; or the independent structure (8) contains smart materials that are deformed by external stimulation to cause the ablation head (9) to fit or leave the designated ablation position;

The guide catheter (7) is fixed on the head of the guide catheter (7) by pulling or pushing one end, and the other end is bent by a guide wire (70) controlled by a handle; or the guide catheter (7) contains Substances that can be attracted by magnets deform the guiding catheter (7) by applying an external magnetic field; or by controlling smart materials on the guiding catheter (7) that can sense external stimuli; or/and deforming the guiding catheter (7) Compliant bending; or/and the guide catheter (7) is provided with prefabricated deformation;

The guide catheter (7) is controlled by a guide catheter control handle (27) or a control handle (2) or not by a handle.

2. The renal sympathetic denervation multifunctional ablation catheter system according to claim 1, characterized in that: the distal end of the catheter body segment (4) also includes a controllable bending segment (5) connected to the proximal end of the ablation segment. , the controllable bending section (5) is fixed on the controllable bending section (5) by pulling or/and pushing one end, and the other end is controlled by a guide wire (11) controlled by a handle to deform; or the controllable bending The segment (5) pulls or/and pushes a traction wire with one end fixed on the independent structure (8) and the other end controlled by a handle.

(10) Control the deformation; or the controllable bending section (5) contains substances that can be attracted by magnets, and the controllable bending section (5) is deformed by applying an external magnetic field; or the controllable bending section (5) contains A smart material that deforms through external stimulation; or/and controls the controllable bending section (5) to undergo compliant bending through the control handle (2); or/and sets the prefabricated deformation of the controllable bending section (5).

3. The renal sympathetic denervation multifunctional ablation catheter system according to claim 1, characterized in that: the ablation catheter (1) or/and the control handle (2), the guiding catheter (7) or/and the guiding A sensor (92) is also installed on the conduit control handle (27).

4. The renal sympathetic denervation multifunctional ablation catheter system according to claim 1, characterized in that: the independent structures (8) are connected at the proximal end, and there are four forms between the two independent structures (8) : The distal ends of the two independent structures (8) are connected into one body to form the head end of the ablation segment (17); or the distal ends of the two independent structures (8) are independent and separated from each other; or the middle part of the two independent structures (8) are connected together, and the distal ends are separated from each other; or the proximal ends of the two independent structures (8) are connected, and the distal ends are connected to different positions of the pulling wire (10).

5. The renal sympathetic denervation multifunctional ablation catheter system according to claim 1, characterized in that: the ablation head (9) is selected from the group consisting of radiofrequency ablation electrode head, resistance heating ablation head, liquid-cooled infusion frequency electrode head, and frozen Ablation head, ultrasonic ablation probe, focused ultrasound ablation probe, laser ablation head, focused laser ablation head, photodynamic therapy ablation head or microwave ablation head; wherein the radiofrequency ablation electrode head includes a radiofrequency ablation electrode (91).

6. The renal sympathetic denervation multifunctional ablation catheter system according to claim 1, characterized in that: the independent structure (8) is provided with a detection electrode (19) for emitting or/and receiving electrical pulses; or/ The ablation head (9) is also used to send out or/and receive electrical pulses.

7. The renal sympathetic denervation multifunctional ablation catheter system according to claim 2, characterized in that: the controllable bending section (5) is provided with a detection electrode (19) for issuing and/or receiving electrical pulses.

8. The renal sympathetic denervation multifunctional ablation catheter system according to claim 1, characterized in that: the pulling wire (10) runs outside the independent structure (8) or/and runs inside the independent structure (8) , the head end attachment point (110) of the pulling wire (10) is set at the head end of the ablation segment (17), or is set on an independent structure (8) from the head of the independent structure (8) to the connection point (18), or is set on On the independent structure (8) from the ablation head (9) to the connection point (18), or on the independent structure (8) between the ablation segment head (17) and the ablation head (9), or set on the ablation head ( 9) or its adjacent independent structure (8), or is provided on the connecting joint provided at the connecting point (18) of the two independent structures (8), the traction wire (10) is in the controllable bending section (5) , the catheter body section (4) is merged into one or runs along the controllable bending section (5), the long axis center line of the catheter body section (4), and finally connects with the control button (230) or the control handle (2) The disk (231) is connected.

9. The renal desympathetic denervation ablation catheter system according to claim 1, characterized in that: when the guiding catheter (7) provides a fulcrum for the deformation of the ablation catheter (1), the head of the guiding catheter (7) is arranged in line with the The oblique hole (74) or/and the side groove (76) that the blood vessels communicate with.

10. The renal desympathetic denervation ablation catheter system according to claim 1 or 5, characterized in that: when the distal ends of the independent structures (8) are connected into one body to form the ablation segment head (17), the guiding catheter head A shrinking structure (73) or a plug (72) is provided at the end, and a side groove (76) is provided on the head side wall of the guide catheter (7); when the independent structures (8) are independent of each other and separated from each other, the guide catheter (7) An inclined hole (74) is provided on the head end or head side wall of 7); when the middle parts of the independent structures (8) are connected together and the distal ends are separated from each other, the head end or head of the guide catheter (7) The side wall is provided with an oblique hole (74) communicating with the blood vessel. After the oblique hole (74), a side groove (76) is provided on the side wall of the guide catheter (7).

11. The kidney desympathetic denervation multifunctional ablation catheter system according to claim 1, characterized in that: the number of guide wires (70) is set according to the number of bending directions required to control, and the number of guide wires (70) is The head end attachment point is set at the head of the guide catheter (7), and the corresponding centrifugal position is selected for attachment according to the desired bending direction. The guide wire (70) runs in the wall of the guide catheter (7) or/and the tube. outside the wall.

12. The renal sympathetic denervation multifunctional ablation catheter system according to claim 1, characterized in that: the guide wire (11) runs within or/and the controllable bending section (5) ), the number of guide wires (11) is set according to the number of bending directions needed to be controlled. When the controllable bending section (5) adopts a C-shaped bend design, the head end attachment point (111) of the guide wire (11) is set at a controllable bending section (5). Control the bending section (5) close to the ablation section (6), and select the corresponding centrifugal position for attachment according to the required bending direction;

When the controllable bending section (5) adopts an S-shaped bend design, on the basis of the C-shaped bend design guide wire (11), an additional guide wire is added to the distal end of the second bend that needs to form an S-shaped bend. (11') is attached here, and the guide wire (11') is attached at the corresponding centrifugal position according to the desired bending direction; or without increasing the number of guide wires (11), by adjusting the internal structure of the controllable bending section (5) So that a guide wire (11) can achieve S-shaped bending.

13. The renal sympathetic denervation multifunctional ablation catheter system according to claim 1, characterized in that: The tail side wall of the guide catheter (7) is also provided with an opening (77) for connecting a syringe or an injection device for intravascular injection of medicine or intravascular contrast agent, or through the end of the guide catheter (7) The opening is connected to a syringe or/and an injection device for intravascular injection of medicine or/and intravascular contrast agent; or/and a connecting joint (76) is provided at the end of the guide catheter (7), and the connecting joint (76) is connected to the syringe , the injection device, the ablation catheter (1) or the control handle (2) are connected.

14. The renal sympathetic denervation multifunctional ablation catheter system according to claim 1, characterized in that: the ablation catheter (1) or/and the guiding catheter (7) is manufactured by selecting materials with different hardnesses, or By selectively reducing or/and increasing the internal structure of part of the catheter section or/and the structure of the tube wall, or by implanting a structure that is prone to deformation in the ablation catheter (1) or/and the guiding catheter (7).

15. The renal sympathetic denervation multifunctional ablation catheter system according to claim 1, characterized in that: the ablation catheter (1) or/and the guiding catheter (7) is marked with a scale to indicate the ablation catheter (1) Or/and the depth of the guide catheter (7) entering the blood vessel and indirect measurement of the length and width of the human body structure under ultrasound or X-ray imaging equipment; Different imaging devices are set on the ablation catheter (1) or/and the guide catheter (7) The mark is used to distinguish the ablation catheter (1) or/and the guiding catheter (7) under ultrasound or X-ray imaging equipment; or/and different development marks are set on each independent structure (8) for use in ultrasound or X-ray imaging equipment. Different independent structures (8) are distinguished under the equipment; marks are also provided on the ablation catheter (1) and/or the guiding catheter (7) for distinguishing different axial rotation states under the ultrasound or X-ray imaging equipment.

16. The renal sympathetic denervation multifunctional ablation catheter system according to claim 1, characterized in that: the ablation catheter (1) is fixed to the upper end of the control handle (2) through the catheter body section (4), and the control handle (2) The lower end or lower side has an energy exchange joint (201), and the wires, catheters, microwave antennas or optical fibers from the ablation head (9) pass through the control handle (2) and converge at the energy exchange joint (201).

17. The renal sympathetic denervation multifunctional ablation catheter system according to claim 1 or 16, characterized in that: the control handle (2) includes an operating handle (211) and an operating handle (247); the operating handle (211) There is a control button (230) or a control panel (231) for controlling the deformation of the controllable bending section (5). The control button (230) or the control panel (231) is connected to the guide wire (11). Through the control button (230) moves up and down, or controls the controllable bending section (5) through multi-directional rotation of the control panel (231); or/and includes a ring-shaped control button (257) on the operating handle (247), the The annular control button (257) is connected to the traction wire (10) through a connecting rod (258). The connecting rod (258) is located in the guide groove (248) in the control handle (2). By moving the annular control button (257) up and down ) to achieve control of independent structures; also includes a buffer structure to prevent excessive pulling;

The guiding catheter control handle (27) includes an operating handle (211') and an operating handle (242). The operating handle (211') is provided with a control button (230') for controlling the deformation of the guiding catheter (7) or Control panel (231'), the control button (230') or the control panel (231') is connected to the guide wire (70), through the up and down movement of the control button (230'), or through the control panel (231') The multi-directional rotation of the guide catheter (7) realizes the control of the guide catheter (7); it also includes a buffer structure that can prevent excessive pulling; the guide catheter control handle (27) and the control handle (2) also include a slot (243) respectively. ), hook-shaped teeth (210), are disassembled and combined through the slot (243) and hook-shaped teeth (210).

18. The renal sympathetic denervation multifunctional ablation catheter system according to claim 1, characterized in that: the ablation generating device (3) is provided with a joint for energy output and a joint for sensor signal input (311), and is also provided with a joint for energy output and a joint for sensor signal input (311). There is a connector (321) connected to an external power supply; the ablation generating device (3) contains a display (320) on which parameters can be controlled through touch screen control and part or all of the information can be displayed, and buttons (320) for adjusting parameters ( 330).