Non-contact pressure regulated radiofrequency ablation catheter

Abstract

The application discloses a non-contact pressure regulating radio frequency ablation catheter, which comprises an electrode base and a catheter electrode axially slidingly installed on the electrode base, a magnet is installed at the tail end of the catheter electrode, a semi-conductive coil assembly and a driving coil electrically connected with the semi-conductive coil assembly are installed on the electrode base, the semi-conductive coil assembly with semi-conductive characteristics is placed in an external alternating electromagnetic field and uses electromagnetic induction principle to supply the driving coil with induced current with consistent direction, so that the catheter electrode is pushed by the electrode base through the repulsive force between the driving coil and the magnet, and the catheter electrode at the head of the radio frequency ablation catheter can be driven to press the lesion tissue, so that the catheter electrode can efficiently heat and ablate the deep tissue of the lesion tissue, and the pressing pressure of the catheter electrode on the lesion tissue can be regulated by regulating the magnetic field strength of the external alternating electromagnetic field, so that the radio frequency ablation can be accurately completed.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, specifically to a non-contact pressure-regulated radiofrequency ablation catheter. Background Technology

[0002] Radiofrequency ablation is a minimally invasive interventional therapy. Its principle is to introduce a radiofrequency ablation catheter with electrodes into the lesion site in the patient's body under the guidance of imaging equipment (such as ultrasound, CT, etc.). Then, the radiofrequency ablation device transmits radiofrequency pulse energy to the lesion tissue through the electrodes and generates local high temperature, thereby achieving the purpose of drying and necrosis of the diseased tissue.

[0003] Because some lesions are located "deep" during ablation, they are difficult to ablate. To address this issue, the temperature of the radiofrequency ablation catheter is usually increased and the contact time between the catheter and the lesion is extended, so that the "deep" lesions are heated.

[0004] However, due to the increased temperature of the radiofrequency ablation catheter and the prolonged contact time with the lesion tissue, normal tissue surrounding the lesion tissue may also be damaged.

[0005] Although it is possible to cause the lesion tissue to be depressed by increasing the pressure of the radiofrequency ablation catheter on the lesion tissue, the density of the depressed lesion tissue will increase, which will help improve the efficiency of heat conduction to the "deep" lesion tissue. It will also bring the radiofrequency ablation catheter closer to the "deep" lesion tissue, thereby further improving the efficiency of heat conduction to the "deep" lesion tissue.

[0006] However, current radiofrequency ablation catheters lack the ability to adjust the pressure applied to the lesion. Doctors can only adjust the pressure by moving the catheter using experience and touch. Furthermore, when the bending angle of the radiofrequency ablation catheter is large, it severely affects the feedback of the pressure applied to the lesion, thus causing inconvenience and difficulties in efficiently and accurately completing the radiofrequency ablation procedure. Summary of the Invention

[0007] The purpose of this invention is to provide a non-contact pressure-adjustable radiofrequency ablation catheter to solve the technical problem in the prior art that radiofrequency ablation catheters do not have the function of adjusting the pressure applied to the lesion tissue, which makes it difficult to complete radiofrequency ablation efficiently and accurately.

[0008] To solve the above-mentioned technical problems, the present invention specifically provides the following technical solution:

[0009] A non-contact pressure-modulated radiofrequency ablation catheter, characterized in that it comprises:

[0010] The catheter electrode receives radiofrequency pulse energy from the radiofrequency ablation device and generates local high temperature to ablate the lesion.

[0011] An electrode base is slidably inserted into the catheter electrode, and the electrode base and the catheter electrode are arranged with their ends facing each other.

[0012] A magnet is disposed at the tail end of the conduit electrode;

[0013] An electromagnetic force drive assembly is disposed on the electrode base and the catheter electrode, and the electromagnetic force drive assembly is used to generate an induced current to drive the magnet to push the catheter electrode to slide on the electrode base to adjust the pressure applied to the lesion.

[0014] Furthermore, the electromagnetic force drive assembly includes a semiconductor coil assembly, a drive coil, and a magnet. The semiconductor coil assembly is disposed on the side of the electrode base, the drive coil is disposed on the front end of the electrode base near the conduit electrode, the semiconductor coil assembly is electrically connected to the drive coil, and the magnet is disposed on the tail end of the conduit electrode near the drive coil.

[0015] The semiconductor coil assembly uses an external alternating electromagnetic field to generate a unidirectional induced current, and the drive coil uses the unidirectional induced current to generate an electromagnetic field, so that the magnet is interacted with by the electromagnetic field generated by the drive coil and drives the conduit electrode to move.

[0016] Furthermore, the semiconductor coil assembly includes an induction coil and a micro diode. The induction coil is disposed on the side of the electrode base. One end of the induction coil is electrically connected to one end of the drive coil, and the other end of the induction coil is electrically connected to the other end of the drive coil through the micro diode.

[0017] Furthermore, the plurality of driving coils are electrically connected to the driving coils in parallel via the plurality of micro diodes, and the plurality of induction coils are circumferentially distributed on the side of the electrode base;

[0018] The electrode base has multiple embedding slots on its side for embedding the induction coil, so that the induction coil can be stably mounted on the electrode base while increasing the number of turns.

[0019] Furthermore, the electrode base has a cavity inside for mounting the micro diode. The ends of the induction coil and the drive coil pass through the side wall of the electrode base and are connected to the micro diode in the cavity, so that the side of the electrode base can be used to accommodate more of the induction coil because it is not occupied by the micro diode.

[0020] Furthermore, the electrode base has a plug-in portion facing the front end of the conduit electrode, the conduit electrode has a plug hole for the plug-in portion to slide into, the drive coil is installed at the end of the electrode base and sleeved on the plug-in portion, and the magnet is ring-shaped and slidably sleeved on the plug-in portion.

[0021] Furthermore, the electromagnetic force drive assembly also includes a tubular annular iron core, the insertion part is inserted into the annular iron core, and the annular iron core is disposed at the front end of the electrode base;

[0022] The toroidal iron core is inserted into the driving coil, and the front end of the toroidal iron core is positioned directly opposite the end of the magnet. The toroidal iron core is magnetized by the driving coil through which the unidirectional induced current is passed, so that the driving coil enhances its repulsive effect on the magnet by passing through the toroidal iron core.

[0023] The front end of the electrode base is provided with a tubular annular yoke wall. The driving coil is located inside the annular yoke wall, and the annular iron core extends outward from the front end near the magnet and connects to the annular yoke wall. The annular yoke wall is used to shield or reduce the interference of the external alternating electromagnetic field on the induction coil.

[0024] Furthermore, the electrode base and the conduit electrode are connected by a flexible tubular elastic sleeve, and the semiconductor coil assembly, the drive coil, and the magnet are all located inside the tubular elastic sleeve;

[0025] The tubular elastic sleeve is stretched when the drive coil, which is supplied with the unidirectional induced current, drives the conduit electrode away from the duct, and the tubular elastic sleeve pulls the conduit electrode to reset after the drive coil is de-energized.

[0026] Furthermore, both ends of the tubular elastic sleeve are fixedly mounted on the electrode base and the conduit electrode by positioning clamps, and the side walls of the electrode base and the conduit electrode are provided with clamp grooves, and the tubular elastic sleeve is clamped in the clamp grooves at the location of the positioning clamp.

[0027] Furthermore, the wall of the insertion hole is provided with a protruding ridge, and the side of the insertion part is provided with a limiting groove that slides and engages with the protruding ridge. The protruding ridge restricts the relative rotation between the electrode base and the conduit electrode by inserting into the limiting groove.

[0028] Compared with the prior art, the present invention has the following advantages:

[0029] This invention utilizes the principle of electromagnetic induction to deliver a consistently induced current to the drive coil via a semiconducting coil assembly placed in an external alternating electromagnetic field. This allows the electrode base, on which the drive coil is located, to be pushed by the repulsive force between the drive coil and the magnet on the catheter electrode, thereby enabling the catheter electrode at the tip of the radiofrequency ablation catheter to apply pressure to the lesion tissue in a non-contact manner. This facilitates efficient heating and ablation of deep tissue within the lesion by the catheter electrode. Furthermore, the pressure applied by the catheter electrode to the lesion tissue can be adjusted by regulating the intensity of the external alternating electromagnetic field, thus ensuring precise completion of the radiofrequency ablation procedure. Attached Figure Description

[0030] To more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are merely exemplary, and those skilled in the art can derive other embodiments based on the provided drawings without creative effort.

[0031] Figure 1 This is a schematic diagram of the radiofrequency ablation catheter of the present invention;

[0032] Figure 2 This is a schematic diagram of the structure of the catheter electrode of the present invention;

[0033] Figure 3 This is a schematic diagram of the electrode base of the present invention;

[0034] Figure 4 This is a schematic diagram of the structure of the elastic reset component of the present invention;

[0035] Figure 5 This is a schematic diagram of the annular yoke wall structure of the present invention.

[0036] The labels in the diagram represent the following:

[0037] 1-Electrode base; 2-Conduit electrode; 3-Magnet; 4-Semiconductor coil assembly; 5-Drive coil; 6-Elastic reset assembly; 7-Cavity; 8-Groove; 9-Socket; 10-Plug-in part; 11-Annular yoke wall; 12-Annular iron core; 13-Protruding ridge; 14-Limiting groove;

[0038] 401 - Induction coil; 402 - Miniature diode;

[0039] 601 - Tubular elastic rubber sleeve; 602 - Positioning clamp. Detailed Implementation

[0040] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0041] During radiofrequency ablation, the ablation electrode is inserted subcutaneously to the designated location, deployed, and the ablation process begins. However, subcutaneous puncture is a vertical procedure, which may result in a slight deviation from the tumor location for some punctures. Therefore, a slight lateral movement of the ablation electrode is necessary to bring it closer to the tumor during visualization, thus improving the accuracy of radiofrequency ablation. However, conventional methods make it difficult to adjust the ablation electrode laterally.

[0042] Therefore, as Figures 1 to 4 As shown, the present invention provides a non-contact pressure-modulated radiofrequency ablation catheter, comprising:

[0043] The catheter electrode 2 ablates the lesion by receiving radiofrequency pulse energy from the radiofrequency ablation device and generating local high temperature.

[0044] Electrode base 1 is slidably inserted into conduit electrode 2, and electrode base 1 and conduit electrode 2 are arranged with their ends facing each other;

[0045] Magnet 3 is disposed at the tail end of the conduit electrode 2;

[0046] An electromagnetic force drive assembly is disposed on the electrode base 1, and the electromagnetic force drive assembly is used to generate an induced current to drive the magnet 3 to push the catheter electrode 2 to slide on the electrode base 1 to adjust the pressure applied to the lesion.

[0047] The electromagnetic force drive assembly includes a semiconducting coil assembly 4, a drive coil 5, and a magnet 3. The semiconducting coil assembly 4 is disposed on the side of the electrode base 1, and the drive coil 5 is disposed on the front end of the electrode base 1 near the conduit electrode 2. The semiconducting coil assembly 4 and the drive coil 5 are electrically connected.

[0048] The application implementation steps of this embodiment are as follows:

[0049] The first step is that the semiconductor coil assembly 4 uses an external alternating electromagnetic field to generate a unidirectional induced current, which drives the coil 5 to generate an electromagnetic field using the unidirectional induced current.

[0050] The second step involves the interaction between the magnet 3 and the electromagnetic field generated by the drive coil 5, which in turn drives the conduit electrode 2. Specifically, to bring the magnet 3 closer to the electromagnetic field generated by the drive coil 5, the magnet 3 is positioned at the end of the conduit electrode 2 near the tail end of the drive coil 5.

[0051] The magnet 3 can be integral or distributed at the tail end of the catheter electrode 2. There are various ways to fix it, such as by embedding or by snapping. It slides synchronously with the catheter electrode 2, thereby receiving continuous push to promote the movement of the catheter electrode 2.

[0052] Based on the foregoing, the electromagnetic force drive component in this embodiment is equivalent to a pressure control device, and the magnitude of the pressure applied by the catheter electrode 2 to the lesion tissue increases with the increase of the magnetic field strength and the frequency of change of the external alternating magnetic field.

[0053] The magnitude of the applied pressure is achieved through changes in the external alternating magnetic field, such as the strength of the magnetic field, the rate of change of the magnetic field (equivalent to the speed at which the conductor moves while cutting the magnetic field lines), and the angle at which the conductor cuts the magnetic field lines.

[0054] Since the length of the semiconductor coil assembly 4 is constant, the greater the strength of the magnetic field and the speed of change of the magnetic field (equivalent to the speed at which the wire cuts the magnetic field lines), the greater the induced current generated, and thus the greater the force acting on the magnet 3, and vice versa.

[0055] In addition, in order to facilitate the adjustment of the magnitude of the alternating electromagnetic field and avoid errors in the thrust applied by the drive coil 5 to the catheter electrode 2 due to the difference in the relative angle between the semiconductor coil assembly 4 and the alternating electromagnetic field, a miniature pressure sensing element can be installed on the head of the catheter electrode 2 to provide feedback on the pressure exerted by the catheter electrode 2 on the lesion tissue, thereby facilitating the pressure control device to flexibly adjust the alternating magnetic field.

[0056] Specifically, the external alternating magnetic field generates an alternating electromagnetic field on the semiconductor coil assembly 4 on the electrode base 1. The semiconductor coil assembly 4 uses diodes or semiconductors to ensure that the direction of the current supplied to the drive coil 5 is always consistent, so that the magnetism of the end of the drive coil 5 near the magnet 3 is the same as the magnetism of the end of the magnet 3 near the drive coil 5. Thus, the magnet 3 pushes the catheter electrode 2 under the repulsive force of the drive coil 5, thereby increasing the pressure applied by the catheter electrode 2 to the lesion tissue.

[0057] Under the thrust, the catheter electrode 2 will gradually approach the lesion tissue, and the lesion tissue will be compressed and become tight under the pressure of the catheter electrode 2. This allows the catheter electrode 2 to heat and ablate the deep tissue of the lesion tissue in a short time, thereby saving surgical time and avoiding damage to the surrounding normal tissue.

[0058] The semiconductor coil assembly 4 includes an induction coil 401 and a micro diode 402. One end of the induction coil 401 is electrically connected to one end of the drive coil 5, and the other end of the induction coil 401 is electrically connected to the other end of the drive coil 5 through the micro diode 402.

[0059] In this embodiment, as mentioned earlier, the micro diode 402 ensures that the current in the induction coil 401 has a fixed direction, meaning the effect is also directional. Therefore, in this embodiment, the catheter electrode 2 can only act in one direction, and re-puncture is required when acting in the opposite direction. However, in actual operation, due to guidance from methods such as CT scans, the puncture site cannot be on the other side of the tumor. Therefore, in actual operation, it is only necessary to determine the direction of the force applied by the catheter electrode 2 and the location of the tumor to achieve accurate puncture.

[0060] Furthermore, multiple induction coils 401 are provided, and the multiple induction coils 401 are circumferentially distributed and embedded in the side of the electrode base 1 so that the semiconductor coil assembly 4 can make full use of the external alternating electromagnetic field to generate induced current.

[0061] Specifically, the electrode base 1 is positioned on its side, with its major axis as the central axis and arranged circumferentially around this central axis. This allows the external alternating magnetic field to generate an induced current in the induction coil 401 even if it deviates from the electrode base 1. This reduces the requirements for the orientation of the external alternating magnetic field, simplifying practical operation (i.e., reducing the difficulty in locating the external alternating magnetic field). The specific arrangement is as follows: Figure 3 As shown.

[0062] Preferably, the electrode base 1 has a cavity 7 inside for mounting the micro diode 402. The ends of the induction coil 401 and the drive coil 5 pass through the side wall of the electrode base 1 and are connected to the micro diode 402 inside the cavity 7, so as to avoid the micro diode 402 being exposed and affecting the aesthetics of the radiofrequency ablation electrode base 1, and to facilitate the installation and fixation of the micro diode roller.

[0063] At the same time, the aforementioned components can be precisely installed through the cavity and other structures. That is, some components (such as the micro diode 402) can be placed on the electrode base 1. In addition, the induction coil 401 and the drive coil 5 can also be installed in the same way, thereby reducing the increase in the size of the entire device due to the addition of corresponding components, which would make it inconvenient to operate.

[0064] The electrode base 1 is provided with a plug-in part 10 facing the front end of the conduit electrode 2. The conduit electrode 2 is provided with a plug hole 9 for the plug-in part 10 to be slidably plugged in. The drive coil 5 is installed at the end of the electrode base 1 and sleeved on the plug-in part 10. The magnet 3 is ring-shaped and slidably sleeved on the plug-in part 10.

[0065] A ring-shaped magnet 3 is fixedly installed at the tail end of the conduit electrode 2 and is coaxial with the insertion hole 9. The insertion part 10 passes through the magnet 3 and is inserted into the insertion hole 9 at the tail end of the conduit electrode 2.

[0066] Furthermore, the electrode base 1 and the conduit electrode 2 are connected by an elastic tubular elastic sleeve 601. The semiconducting coil assembly 4, the drive coil 5, and the magnet 3 are all located inside the tubular elastic sleeve 601. The tubular elastic sleeve 601 is a thin-walled tubular object made of elastic rubber material.

[0067] The two ends of the tubular elastic sleeve 601 are respectively fitted and connected to the adjacent ends of the motor base 1 and the catheter electrode 2. Both ends of the tubular elastic sleeve 601 are clamped onto the electrode base 1 and the catheter electrode 2 by positioning clamps 602. The side walls of the electrode base 1 and the catheter electrode 2 are provided with clamp grooves 8 that cooperate with the positioning clamps 602 to enhance the fixing effect of the positioning clamps 602 and to prevent the positioning clamps 602 from being too protruding and affecting the aesthetics and passage performance of the ablation catheter.

[0068] The tubular elastic sleeve 601 is stretched when the drive coil 5, which is supplied with a unidirectional induced current, drives the catheter electrode 2 away from the point of origin. After the drive coil 5 is de-energized, the tubular elastic sleeve 601 pulls the catheter electrode 2 to reset, so that the catheter electrode 2 can apply pressure to the ablated tissue again in the direction away from the electrode base 1 when ablation is performed on the next ablation point.

[0069] In this embodiment, the electromagnetic force driving the conduit electrode 2 does not completely move it to the designated position, but rather improves the microwave ablation effect through its own fine-tuning action. Therefore, the electromagnetic force driving component does not require a large force from the conduit electrode 2.

[0070] Furthermore, the tubular elastic sleeve 601 is clamped to the positioning clamp 602 on the motor base 1 and the conduit electrode 2 by the positioning clamp 602, and the side walls of the electrode base 1 and the conduit electrode 2 are provided with clamp grooves 8 that cooperate with the positioning clamp 602.

[0071] In addition, in order to increase the magnetic force of the drive coil 5 and avoid the drive coil 5 being affected by the external alternating electromagnetic field, the electromagnetic force drive assembly also includes a tubular annular iron core 12, the insertion part 10 is inserted into the annular iron core 12, and the annular iron core 12 is disposed at the front end of the electrode base 1.

[0072] The toroidal iron core 12 is inserted into the drive coil 5. The front end of the toroidal iron core 12 is positioned directly opposite the end of the magnet 3. The toroidal iron core 12 is magnetized by the drive coil 5, which is supplied with a unidirectional induced current, so that the drive coil 5 enhances its repulsive effect on the magnet 3 through the toroidal iron core 12.

[0073] The front end of the electrode base 1 is provided with a tubular annular yoke wall 11. The drive coil 5 is located inside the annular yoke wall 11, and the annular iron core 12 extends outward from the front end near the magnet 3 and connects to the annular yoke wall 11. The annular yoke wall 11 is used to shield or reduce the interference of external alternating electromagnetic fields on the induction coil 2.

[0074] The wall of the insertion hole 9 is provided with a protruding ridge 13, and the side of the insertion part 10 is provided with a limiting groove 14 that slides and engages with the protruding ridge 13. The protruding ridge 13 restricts the relative rotation between the electrode base 1 and the conduit electrode 2 by inserting into the limiting groove 14.

[0075] Preferably, the induction coil 401 is rectangular to make full use of the space of the electrode base 1, thereby increasing the upper limit of the power of the induction coil 401.

[0076] The above embodiments are merely exemplary embodiments of this application and are not intended to limit this application. The scope of protection of this application is defined by the claims. Those skilled in the art can make various modifications or equivalent substitutions to this application within its substance and scope of protection, and such modifications or equivalent substitutions should also be considered to fall within the scope of protection of this application.

Claims

1. A non-contact pressure-regulated radiofrequency ablation catheter, characterized in that, include: The catheter electrode (2) ablates the lesion by receiving the radiofrequency pulse energy of the radiofrequency ablation device and generating local high temperature; The electrode base (1) is slidably inserted into the catheter electrode (2), and the electrode base (1) and the catheter electrode (2) are arranged with their ends facing each other. A magnet (3) is disposed at the tail end of the conduit electrode (2); An electromagnetic force drive assembly is disposed on the electrode base (1), and the electromagnetic force drive assembly is used to generate an induced current to drive the magnet (3) to push the catheter electrode (2) to slide on the electrode base (1) to adjust the pressure applied to the lesion; The electromagnetic force drive component uses an external alternating electromagnetic field to generate an induced current, and adjusts the pressure applied by the catheter electrode (2) to the lesion site according to the magnetic field strength of the external alternating electromagnetic field. The electromagnetic force drive assembly includes a semiconducting coil assembly (4) and a drive coil (5). The semiconducting coil assembly (4) is disposed on the side of the electrode base (1), and the drive coil (5) is disposed on the electrode base (1) near the front end of the conduit electrode (2). The semiconducting coil assembly (4) is electrically connected to the drive coil (5), and the magnet (3) is disposed on the conduit electrode (2) near the tail end of the drive coil (5). The semiconductor coil assembly (4) uses an external alternating electromagnetic field to generate a unidirectional induced current, and the drive coil (5) uses the unidirectional induced current to generate an electromagnetic field so that the magnet (3) is interacted with by the electromagnetic field generated by the drive coil (5) and drives the conduit electrode (2) to move.

2. The non-contact pressure-regulated radiofrequency ablation catheter according to claim 1, characterized in that, The semiconductor coil assembly (4) includes an induction coil (401) and a micro diode (402). The induction coil (401) is disposed on the side of the electrode base (1). One end of the induction coil (401) is electrically connected to one end of the drive coil (5), and the other end of the induction coil (401) is electrically connected to the other end of the drive coil (5) through the micro diode (402).

3. The non-contact pressure-regulated radiofrequency ablation catheter according to claim 2, characterized in that, Multiple induction coils (401) are electrically connected to the drive coil (5) in parallel via multiple micro diodes (402), and the multiple induction coils (401) are circumferentially distributed on the side of the electrode base (1); The electrode base (1) has multiple embedding slots on its side for embedding the induction coil (401) so that the induction coil (401) can be stably mounted on the electrode base (1) while the number of turns increases.

4. The non-contact pressure-regulated radiofrequency ablation catheter according to claim 3, characterized in that, The electrode base (1) has a cavity (7) inside for mounting the micro diode (402). The ends of the induction coil (401) and the driving coil (5) pass through the side wall of the electrode base (1) and are connected to the micro diode (402) in the cavity (7), so that the side of the electrode base (1) can be used to mount more of the induction coil (401) because it is not occupied by the micro diode (402).

5. The non-contact pressure-regulated radiofrequency ablation catheter according to claim 2, characterized in that, The electrode base (1) is provided with a plug-in part (10) facing the front end of the conduit electrode (2). The conduit electrode (2) is provided with a plug hole (9) for the plug-in part (10) to be slidably plugged in. The drive coil (5) is installed at the end of the electrode base (1) and sleeved on the plug-in part (10). The magnet (3) is ring-shaped and slidably sleeved on the plug-in part (10).

6. The non-contact pressure-regulated radiofrequency ablation catheter according to claim 5, characterized in that, The electromagnetic force drive assembly also includes a tubular annular iron core (12), the plug-in part (10) is plugged into the annular iron core (12), and the annular iron core (12) is disposed at the front end of the electrode base (1); The annular iron core (12) is inserted into the driving coil (5). The front end of the annular iron core (12) is directly opposite to the end of the magnet (3). The annular iron core (12) is magnetized by the driving coil (5) through which a unidirectional induced current is passed, so that the driving coil (5) enhances the repulsive effect on the magnet (3) through the annular iron core (12). The front end of the electrode base (1) is provided with a tubular annular yoke wall (11), the drive coil (5) is located inside the annular yoke wall (11), and the annular iron core (12) extends outward from the front end of the magnet (3) and connects to the annular yoke wall (11). The annular yoke wall (11) is used to shield or reduce the interference of external alternating electromagnetic fields on the induction coil (401).

7. The non-contact pressure-regulated radiofrequency ablation catheter according to claim 1, characterized in that, The electrode base (1) and the conduit electrode (2) are connected by a flexible tubular elastic sleeve (601). The semiconducting coil assembly (4), the driving coil (5), and the magnet (3) are all located inside the tubular elastic sleeve (601). The tubular elastic sleeve (601) is stretched when the drive coil (5) with a unidirectional induced current drives the conduit electrode (2) away, and the tubular elastic sleeve (601) pulls the conduit electrode (2) to reset after the drive coil (5) is de-energized.

8. The non-contact pressure-regulated radiofrequency ablation catheter according to claim 7, characterized in that, Both ends of the tubular elastic sleeve (601) are fixedly mounted on the electrode base (1) and the conduit electrode (2) by positioning clamps (602), and clamp grooves (8) are provided on the side walls of the electrode base (1) and the conduit electrode (2). The tubular elastic sleeve (601) is clamped in the clamp groove (8) by the positioning clamps (602) at the location where the positioning clamps (602) are located.

9. A non-contact pressure-regulated radiofrequency ablation catheter according to claim 5, characterized in that, The insertion hole (9) has a protruding ridge (13) on its wall. The side of the insertion part (10) has a limiting groove (14) that slides and engages with the protruding ridge (13). The protruding ridge (13) restricts the relative rotation between the electrode base (1) and the conduit electrode (2) by inserting into the limiting groove (14).

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