Computer readable storage medium and pulse ablation system

Abstract

The invention provides a computer readable storage medium and a pulse ablation system, when a program on the medium is executed, the following steps are executed: controlling a pulse generator to generate pulses at least according to a preset relationship among a pulse width D, a current I in a pulse circuit and a pulse frequency f in each cardiac cycle; the preset relation is I * f * lt; h; # imgabs0 # U is the voltage in the pulse circuit, S1 is the surface area of a head electrode of the ablation catheter, S2 is the sum of the surface areas of all ring electrodes of the ablation catheter, L is the distance between the head electrode and a preset plane, the plane is set to be perpendicular to the axis of the ablation catheter, the distances between the preset plane and the two ring electrodes used for forming the negative electrode are equal, and n1 and n2 are constants larger than 1; h is a constant. The computer readable storage medium is applied to the pulse ablation system, so that when the pulse generator generates pulses and is applied to cardiac ablation, generation of microbubbles and sparks can be reduced, and stimulation to the phrenic nerves is reduced under the condition that the ablation catheter is close to the phrenic nerves.

Description

Technical Field

[0001] The present invention belongs to the technical field of medical devices, and in particular relates to a computer-readable storage medium and a pulse ablation system. Background Art

[0002] Ablation is a common way to treat arrhythmias. Pulsed electric field is a non-thermal ablation energy source with the advantages of high efficiency and safety. Pulsed electric field technology can be used to apply a short high voltage to tissues to generate a local high electric field of hundreds of volts per centimeter. The local high electric field causes cell membrane permeability by creating pores in the cell membrane, thereby destroying the cell membrane. Different tissue cells have different voltage penetration thresholds. The use of pulsed electric field technology can selectively treat cardiomyocytes without affecting other non-target cell tissues. At the same time, because the pulsed electric field releases energy for a very short time, it will not produce a thermal effect and can avoid tissue scab.

[0003] During ablation, pulse energy is transmitted to the target tissue through the ablation catheter. When the target tissue is close to the diaphragm, the energy of the pulsed electric field may reach the voltage penetration threshold of the phrenic nerve, causing the phrenic nerve to be stimulated and produce muscle contraction problems. In addition, inappropriate pulse parameters may also form microbubbles during the ablation process, and even sparks in severe cases. Microbubbles may flow into the brain blood vessels through the blood to form blood clots, and the formation of sparks will cause tissue damage. Summary of the invention

[0004] The object of the present invention is to provide a computer-readable storage medium and a pulse ablation system, aiming to improve the reliability and safety during the pulse ablation process.

[0005] To achieve the above object, the present invention provides a computer-readable storage medium having a program stored thereon, which, when executed, performs:

[0006] Controlling a pulse generator to generate pulses at least according to a preset relationship between a plurality of pulse parameters;

[0007] The pulse parameters include pulse width D, current I in the pulse circuit, and pulse frequency f in a single cardiac cycle; the preset relationship is:

[0008] I*f*D <H;

[0009] in, U is the voltage in the pulse circuit, S1 is the surface area of ​​the head electrode of the ablation catheter, S2 is the sum of the surface areas of all the ring electrodes of the ablation catheter, L is the distance between the head electrode and a preset plane, the preset plane is located between the two ring electrodes used to form the negative electrode, and the distances from the preset plane to the two ring electrodes used to form the negative electrode are equal; n1 and n2 are both constants greater than 1; H is a constant.

[0010] Optionally, the inter-phase delay of the pulses is 0.1 μs to 5 μs.

[0011] Optionally, the pulse width is 0.01 μs to 10 μs.

[0012] Optionally, the voltage amplitude of the pulse is 600V to 4000V.

[0013] Optionally, the pulse generator is configured to generate biphasic pulses, and the pulses generated by the pulse generator constitute at least one pulse sequence;

[0014] The pulse sequence includes a plurality of basic sequences, the basic sequence includes a plurality of unit sequences, and the unit sequence includes a forward pulse and a reverse pulse;

[0015] The inter-pulse delay of the pulses in the basic sequence is 10 to 30 times the inter-phase delay, and the time interval between two adjacent basic sequences of the same pulse sequence is 200 to 400 times the inter-phase delay.

[0016] Optionally, the unit sequence includes a first type of unit sequence and a second type of unit sequence;

[0017] In the first type of unit sequence, the forward pulse precedes the reverse pulse;

[0018] In the second type of unit sequence, the forward pulse follows the reverse pulse;

[0019] The basic sequence includes the first type of unit sequence and / or the second type of unit sequence.

[0020] Optionally, the basic sequence includes at least 10 of the pulses, and the pulse sequence includes at least 50 of the pulses.

[0021] Optionally, the program further performs:

[0022] Obtain an electrocardiogram;

[0023] The pulse generator is controlled to generate the pulse sequence according to the electrocardiogram.

[0024] Optionally, the control of the pulse generator by the electrocardiogram to generate the pulse sequence includes:

[0025] Controlling the pulse generator to generate the pulse sequence within 30 ms to 70 ms after the start of the R wave and stop generating the pulse sequence before the start of the T wave.

[0026] To achieve the above object, the present invention also provides a pulse ablation system, including:

[0027] A pulse generator;

[0028] An ablation catheter, including a catheter body, a tip electrode and a ring electrode; the tip electrode is provided at the distal end of the catheter body; the number of the ring electrodes is three, and the three ring electrodes are arranged at intervals along the axial direction of the catheter body, and the three ring electrodes are all sleeved on the outer side surface of the catheter body; the tip electrode and all the ring electrodes are electrically connected to the pulse generator, and the tip electrode and the nearest ring electrode thereto are used to form a positive electrode, and the remaining ring electrodes are used to form a negative electrode; and,

[0029] A controller, communicatively connected to the pulse generator and configured to execute the program stored on the computer-readable storage medium as described in any one of the preceding items.

[0030] Optionally, a perfusion hole is provided on the tip electrode; a perfusion channel extending along the axial direction of the catheter body is provided on the catheter body, and the distal end of the perfusion channel is communicated with the perfusion hole.

[0031] Optionally, the pulse ablation system further includes a three-dimensional mapping unit, the three-dimensional mapping unit is communicatively connected to the controller, and the three-dimensional mapping unit is also electrically connected to the ring electrode.

[0032] Compared with the prior art, the computer-readable storage medium and the pulse ablation system of the present invention have the following advantages:

[0033] A program is stored on the aforementioned computer-readable storage medium, and when the program is executed, it performs: controlling at least a pulse generator to generate pulses according to a preset relationship of multiple pulse parameters; the pulse parameters include a pulse width D, a current I in a pulse circuit, and a pulse frequency f within a single cardiac cycle; the preset relationship is: I*f*D < H; wherein, U is the voltage in the pulse circuit, S1 is the surface area of ​​the head electrode of the ablation catheter, S2 is the sum of the surface areas of all the ring electrodes of the ablation catheter, L is the distance between the head electrode and a preset plane, the preset plane is perpendicular to the axis of the ablation catheter, and the distances from the preset plane to the two ring electrodes used to form the negative electrode are equal, n1 and n2 are both constants greater than 1; H is a constant. The computer-readable storage medium is applied to a pulse ablation system, and when the pulse generator is controlled to generate pulses based on the above method and applied to cardiac ablation, the possibility of generating microbubbles and sparks can be reduced, and when the ablation catheter is close to the phrenic nerve, the stimulation to the phrenic nerve can be reduced, thereby reducing the probability of muscle contraction. BRIEF DESCRIPTION OF THE DRAWINGS

[0034] The accompanying drawings are used to better understand the present invention and do not constitute an improper limitation of the present invention.

[0035] Figure 1 is a schematic structural diagram of a pulse ablation system provided according to an embodiment of the present invention;

[0036] Figure 2 is a partial structural schematic diagram of a medical catheter of a pulse ablation system provided by the present invention according to an embodiment;

[0037] Figure 3 is a schematic diagram of a pulse sequence generated by a pulse generating device of a pulse ablation system provided by an embodiment of the present invention;

[0038] Figure 4 yes Figure 3 A is an enlarged schematic diagram;

[0039] Figure 5 is a schematic diagram of a basic sequence of a pulse sequence generated by a pulse generating device of a pulse ablation system provided by another embodiment of the present invention;

[0040] Figure 6 is a schematic diagram of a basic sequence of a pulse sequence generated by a pulse generating device of a pulse ablation system provided by another embodiment of the present invention;

[0041] Figure 7 It is a partial schematic diagram of an electrocardiogram of a patient who is undergoing pulse ablation treatment using the pulse ablation system provided by an embodiment of the present invention.

[0042] [Description of reference numerals is as follows]:

[0043] 100-pulse generator, 200-ablation catheter, 210-electrode assembly, 211-head electrode, 2111-infusion hole, 212-ring electrode, 212a-first ring electrode, 212b-second ring electrode, 212c-third ring electrode, 220-tube body, 230-pressure monitoring element, 240-connecting wire, 250-insulating protective sleeve, 260-traction piece, 261-inner core, 262-outer shell, 201-first channel, 300-controller, 400-three-dimensional mapping part, 1-preset plane, 01-pulse sequence, 011-basic sequence, 0111-unit sequence, 0111a-first type unit sequence, 0111b-second type unit sequence, 0011-forward pulse, 0012-reverse pulse. DETAILED DESCRIPTION

[0044] The following is an explanation of the embodiments of the present invention by specific examples, and those skilled in the art can easily understand other advantages and effects of the present invention from the contents disclosed in this specification. The present invention can also be implemented or applied through other different specific embodiments, and the details in this specification can also be modified or changed in various ways based on different viewpoints and applications without departing from the spirit of the present invention. It should be noted that the illustrations provided in the present embodiment only illustrate the basic concept of the present invention in a schematic manner, and only the components related to the present invention are shown in the figure instead of being drawn according to the number, shape and size of the components in the actual implementation. The type, quantity and proportion of each component in the actual implementation can be a random change, and the component layout type may also be more complicated.

[0045] In addition, each embodiment of the following description has one or more technical features, but this does not mean that the user of the present invention must implement all the technical features in any embodiment at the same time, or can only implement part or all of the technical features in different embodiments separately. In other words, under the premise that implementation is possible, those skilled in the art can selectively implement part or all of the technical features in any embodiment according to the disclosure of the present invention and according to the design specifications or implementation requirements, or selectively implement a combination of part or all of the technical features in multiple embodiments, thereby increasing the flexibility of the implementation of the present invention.

[0046] As used in this specification, the singular forms "one", "an" and "the" include plural objects, and the plural form "multiple" includes more than two objects, unless the content clearly indicates otherwise. As used in this specification, the term "or" is usually used in the sense of including "and / or", unless the content clearly indicates otherwise, and the terms "install", "connect", and "connect" should be understood in a broad sense, for example, it can be a fixed connection, a detachable connection, or an integral connection. It can be a mechanical connection or an electrical connection. It can be directly connected or indirectly connected through an intermediate medium, and it can be the internal connection of two elements or the interaction relationship between two elements. Relational terms such as the terms "first", "second", etc. are only used to distinguish one entity or operation from another entity or operation, and do not necessarily require or imply any such actual relationship or order between these entities or operations, nor do they indicate or imply relative importance or implicitly indicate the number of technical features indicated. For those of ordinary skill in the art, the specific meanings of the above terms in the present invention can be understood according to specific circumstances.

[0047] The terms "proximal end" and "distal end" used in this article are described based on the relative positions and orientations of the various elements and components of the medical device. Although non-limiting, the "distal end" is usually the end that first enters the patient's body during normal use of the medical device. The "proximal end" is opposite to the "distal end" and is closer to the operator.

[0048] In order to make the purpose, advantages and features of the present invention more clear, the present invention is further described in detail below with reference to the accompanying drawings. It should be noted that the drawings are all in very simplified form and in non-precise proportions, and are only used to conveniently and clearly assist in explaining the purpose of the embodiments of the present invention. The same or similar reference numerals in the drawings represent the same or similar components.

[0049] Figure 1 FIG. 2 is a schematic diagram showing the structure of a pulse ablation system provided by an embodiment of the present invention. Figure 1 As shown, the pulse ablation system includes a pulse generator 100, an ablation catheter 200 and a controller 300. The controller 300 is connected to the pulse generator 100 for communication and is configured to control the pulse generator 100 to generate pulses. Figure 2 As shown, the ablation catheter 200 includes an electrode assembly 210 , which is electrically connected to the pulse generator 100 and is used to receive the pulse generated by the pulse generator 100 .

[0050] It should be understood that the ablation catheter 200 further includes a catheter body 220, and the electrode assembly 210 is disposed at the distal end of the catheter body 220. The pulsed ablation system can be used to perform pulsed ablation to treat abnormal heart rhythms. During the treatment process, the distal end of the ablation catheter 200 is inserted into the patient's heart and contacts the myocardial tissue, so that the electrode assembly 210 is also located in the heart and contacts the myocardial tissue. In this way, when the pulse generator 100 generates a pulse, the electrode assembly 210 can apply the pulse energy to the myocardium to perform myocardial ablation.

[0051] Further, with continued reference to Figure 1 , the electrode assembly 210 includes a plurality of electrodes, namely a tip electrode 211 and three ring electrodes 212. The tip electrode 211 is disposed at the distal end of the catheter body 220. The three ring electrodes 212 are arranged at intervals along the axial direction of the catheter body 220, and the three ring electrodes 212 are all sleeved on the distal side surface of the catheter body 220. It can be understood that all the ring electrodes 212 are located on the proximal side of the tip electrode 211.

[0052] During the pulsed ablation procedure, the tip electrode 211 and the one ring electrode 212 closest to the tip electrode 211 jointly serve as the positive electrode, and the remaining two ring electrodes 212 jointly serve as the negative electrode. Thus, the positive electrode and the negative electrode perform bipolar discharge based on the pulses generated by the pulse generator 100.

[0053] For convenience of description, as Figure 2 shown, along the direction away from the tip electrode 211 (or along the distal-to-proximal direction), the three ring electrodes 212 are respectively referred to as the first ring electrode 212a, the second ring electrode 212b, and the third ring electrode 212c. Therefore, the first ring electrode 212a is closest to the tip electrode. That is, during the pulsed ablation procedure, the first ring electrode 212a and the tip electrode 211 jointly form the positive electrode, and the second ring electrode 212b and the third ring electrode 212c jointly form the negative electrode.

[0054] In an embodiment of the present invention, the controller 300 is configured to control the pulse generator 100 to generate pulses at least according to a preset relationship among a plurality of pulse parameters.

[0055] The pulse parameters include the pulse width D, the current I in the pulse circuit, and the pulse frequency f within a single cardiac cycle. The preset relationship is: I * f * D < H, where H is a constant; U is the voltage in the pulse circuit, n1 and n2 are both constants greater than 1, S1, S2, and L are product parameters of the ablation catheter 200, wherein S1 is the surface area of ​​the head electrode 211, S2 is the sum of the surface areas of all the ring electrodes 212 (that is, when the three ring electrodes 212 are the first ring electrode 212a, the second ring electrode 212b, and the third ring electrode 212c, S2 is the sum of the surface areas of the first ring electrode 212a, the second ring electrode 212b, and the third ring electrode 212c), and L is the distance between the head electrode 211 and a preset plane 1, the preset plane 1 is perpendicular to the axis of the ablation catheter, and the distance from the preset plane 1 to the second ring electrode 212b is equal to the distance from the preset plane 1 to the third ring electrode 212c.

[0056] At Figure 2 In the figure, the preset plane 1 is perpendicular to the paper surface and is shown as a straight line. In addition, the surface area mentioned in this article refers to the area of ​​the surface that is exposed and can be seen.

[0057] Preferably, if Figures 3 to 6 As shown, the pulse generator 100 is configured to generate a biphasic pulse, that is, to generate a forward pulse 0011 and a reverse pulse 0012. The pulses generated by the pulse generator 100 constitute at least one pulse sequence 01. Each of the pulse sequences 01 includes a plurality of basic sequences 011. Each of the basic sequences 011 includes a plurality of unit sequences 0111, and each of the unit sequences 0111 includes a forward pulse 0011 and a reverse pulse 0012.

[0058] According to the sequence of the forward pulse 0011 and the reverse pulse 0012 in the same cell sequence 0111, the cell sequence 0111 is divided into a first type of cell sequence 0111a and a second type of cell sequence 0111b. Specifically, the cell sequence 0111 in which the forward pulse 0011 precedes the reverse pulse 0012 is divided into the first type of cell sequence 0111a (e.g. Figure 4 and Figure 6 ), the cell sequence 0111 of the forward pulse 0011 after the reverse pulse 0012 is divided into a second type of cell sequence 0111b (as shown in Figure 5 and Figure 6In the embodiment of the present invention, all the unit sequences 0111 included in the basic sequence 011 are all the first-type unit sequences 0111a, or all the unit sequences 0111 included in the basic sequence 011 are all the second-type unit sequences 0111b, or the basic sequence 011 includes both the first-type unit sequences 0111a and the second-type unit sequences 0111b.

[0059] The inter-pulse delay of the pulses in any basic sequence 011 is 10 to 30 times the inter-phase delay, and the time interval between two adjacent basic sequences 011 in the same pulse sequence 01 is 200 to 400 times the inter-phase delay. In this way, the occurrence of microbubbles and sparks during pulse ablation can be further avoided, and it is more conducive to reducing the stimulation of the phrenic nerve.

[0060] Optionally, the number of pulses included in the basic sequence 011 is not less than ten. It can be understood that the number of pulses included in the basic sequence 011 is less than the number of pulses included in the pulse sequence 01. Generally, the number of pulses included in the pulse sequence 01 is not less than fifty.

[0061] In the embodiment of the present invention, the delay between the pulses may be 0.1 μs to 5 μs. In addition, the width of the pulses may be 0.01 μs to 10 μs.

[0062] In addition, the head electrode 211 and the ring electrode 212 both have smooth surfaces. Figure 2 As shown, the head electrode 211 is also provided with an irrigation hole 2111. The tube body 220 is provided with a first channel 201 extending along its own axial direction, and the first channel 201 is used as an irrigation channel and is connected to the irrigation hole 2111. When performing pulse ablation, the operator can perfuse physiological saline or other suitable liquids through the irrigation channel to perfuse the head electrode 211 to reduce its surface temperature, thereby eliminating the high temperature generated by the electric field distortion of the head electrode 211 during the ablation process, thereby reducing the generation of microbubbles and sparks.

[0063] Preferably, a plurality of the injection holes 2111 arranged evenly and dispersedly are provided on the head electrode 211 to enhance the cooling effect on the surface of the head electrode 211 .

[0064] Furthermore, the three ring electrodes 212 can also cooperate with each other to obtain ECG signals. Figure 1As shown, the pulse ablation system further includes a three-dimensional mapping unit 400, which is electrically connected to the ring electrode 212 to receive the electrocardiogram signal acquired by the ring electrode 212 and process the electrocardiogram signal to obtain an electrocardiogram. The controller 300 is also in communication connection with the three-dimensional mapping unit 400 and is configured to receive the electrocardiogram and process related mapping / ablation data.

[0065] The controller 300 is also configured to control the pulse generator 100 to generate pulses according to the electrocardiogram. Specifically, the pulse generator 100 is controlled to generate pulses within 30ms to 70ms after the start of the R wave, and stop generating pulses before the start of the T wave (e.g. Figure 7 The advantage of this is that the pulse energy stimulation is adapted to the cardiac cycle, thereby reducing or even avoiding ventricular fibrillation.

[0066] The pulse generator 100 is configured to generate pulses with different voltage amplitudes. The optional voltage amplitude is 600V to 4000V. In this way, when the pulse ablation system is used to perform in vitro experiments or animal experiments, the pulse generator can generate pulses with appropriate voltage amplitudes as needed.

[0067] In addition, if Figure 2 As shown, the ablation catheter 200 further includes a pressure monitoring element 230, which is disposed inside the distal end of the tube body 220, for example, embedded in the wall of the tube body 220 in any suitable manner. The pressure monitoring element 230 is configured to monitor the pressure between the distal end of the ablation catheter 200 and the myocardial tissue. Based on the pressure information, the operator can determine whether the distal end of the ablation catheter 200 is in effective contact with the myocardial tissue, thereby facilitating improving the ablation effect.

[0068] From the axial direction of the ablation catheter 200, it is preferred that the pressure monitoring element 230 is disposed between the positive electrode and the negative electrode. That is, the pressure monitoring element 230 is located between the first ring electrode 212a and the second ring electrode 212b. This is because, during the pulse ablation process, the positive electrode discharges to the negative electrode, so that the electric field energy between the positive electrode and the negative electrode is the strongest, and the pressure monitoring element 230 is disposed between the positive electrode and the negative electrode, so that the pressure monitoring element 230 can accurately measure the pressure between the part of the ablation catheter 200 located between the positive electrode and the negative electrode and the myocardium, thereby facilitating the operator to determine whether the part of the ablation catheter 200 located between the positive electrode and the negative electrode is in effective contact with the myocardium, and start ablation after determining that the part of the ablation catheter 200 located between the positive electrode and the negative electrode is in effective contact, so as to ensure the ablation effect.

[0069] It can be understood that the tube body 220 also has a second channel (not shown in the figure) extending along the axial direction thereof. Figure 2 , the ablation catheter 200 also includes a connecting wire 240 and an insulating protective sleeve 250. There are multiple connecting wires 240, and each connecting wire 240 is partially inserted into the second channel. The head electrode 211 and each ring electrode 212 are respectively electrically connected to the distal end of a connecting wire 240, and the insulating protective sleeve 250 is sleeved on the distal end section of each connecting wire 240. The insulating protective sleeve 250 is used to insulate the distal end of the connecting wire 240, so as to prevent the connecting wire 240 from being broken down during the discharge from the positive electrode to the negative electrode.

[0070] Optionally, the number of the insulating protective sleeves 250 is two, one of which is sleeved on the distal end section of the connecting wire 240 connected to the head electrode 211 and the distal end section of the connecting wire 240 connected to the first ring electrode 212a, and the other insulating protective sleeve 250 is sleeved on the distal end section of the connecting wire 240 connected to the second ring electrode 212b and the distal end section of the connecting wire 240 connected to the third ring electrode 212c. In other words, one insulating protective sleeve 250 is sleeved on the distal end section of the connecting wire 240 connected to the electrode constituting the positive electrode, and the other insulating protective sleeve 250 is sleeved on the distal end section of the connecting wire 240 connected to all the ring electrodes 212 constituting the negative electrode.

[0071] Optionally, a third channel (not shown in the figure) is further provided on the tube body 220. The ablation catheter 200 further includes a traction member 260, which is disposed in the third channel. The traction member 260 includes an inner core 261 and an outer sleeve 262, wherein the inner core 261 extends along the axial direction of the tube body 220, and the outer sleeve 262 is sleeved on at least part of the outer surface of the inner core 261, and the outer sleeve 262 is a three-dimensional spiral structure. By providing the traction member 260, the pushability and torsion controllability of the ablation catheter 200 can be improved, so that the distal end of the ablation catheter 200 can be more easily passed through the tortuous blood vessels and reach the heart.

[0072] It is understandable that the third channel, the second channel, and the first channel are isolated from each other. In addition, in the cross section of the ablation catheter 200, the third channel, the second channel, and the first channel have any appropriate relative positional relationship.

[0073] It can also be understood that the ablation catheter 200 further includes a handle (not shown in the figure), which is connected to the proximal end of the tube body 220 and is used for an operator to hold.

[0074] In addition, it should be noted that, in the case where the pulse ablation system includes the three-dimensional mapping unit 400, the controller 300 may also control the pulse generator 100 to generate pulses only according to the electrocardiogram, rather than controlling the pulse generator 100 to generate pulses according to the preset relationship between the pulse width D, the current I in the pulse circuit, and the pulse frequency f in a single cardiac cycle. In this case, the number of the ring electrodes 212 may be more than three, as long as when performing bipolar discharge for pulse ablation, the head electrode 211 and the ring electrode 212 closest to the head electrode 211 together constitute a positive electrode, and the remaining ring electrodes 212 together constitute a negative electrode; and the plurality of ring electrodes 212 can cooperate with each other to collect electrocardiographic signals.

[0075] Furthermore, an embodiment of the present invention further provides a computer-readable storage medium having a program stored thereon, and when the program is executed, the following steps are performed: controlling the pulse generator 100 to generate pulses at least according to a preset relationship between a plurality of pulse parameters. The preset relationship between the plurality of pulse parameters is described above and will not be repeated here.

[0076] Furthermore, the program further executes: controlling the pulse generator 100 to generate pulses according to the electrocardiogram. The specific operations are still described in the above text and will not be repeated here.

[0077] Although the present invention is disclosed as above, it is not limited thereto. Those skilled in the art may make various changes and modifications to the present invention without departing from the spirit and scope of the present invention. Thus, if these modifications and variations of the present invention fall within the scope of the claims of the present invention and their equivalents, the present invention is also intended to include these modifications and variations.

Claims

1. A computer-readable storage medium having a program stored thereon, characterized in that: When the program is executed, it performs: Controlling a pulse generator to generate pulses at least according to a preset relationship between a plurality of pulse parameters; The pulse parameters include pulse width D, current I in the pulse circuit, and pulse frequency f in a single cardiac cycle; the preset relationship is: I*f*D <H; in, U is the voltage in the pulse circuit, S1 is the surface area of ​​the head electrode of the ablation catheter, S2 is the sum of the surface areas of all the ring electrodes of the ablation catheter, L is the distance between the head electrode and a preset plane, the preset plane is perpendicular to the axis of the ablation catheter, and the distances from the preset plane to the two ring electrodes used to form a negative electrode are equal; n1 and n2 are both constants greater than 1; H is a constant.

2. The computer-readable storage medium according to claim 1, wherein: The inter-phase delay of the pulses is 0.1 μs to 5 μs.

3. The computer-readable storage medium according to claim 1, wherein: The pulse width is 0.01 μs to 10 μs.

4. The computer-readable storage medium according to claim 1, wherein: The voltage amplitude of the pulse is 600V to 4000V.

5. The computer-readable storage medium according to claim 1 or 2, characterized in that: The pulse generator is configured to generate biphasic pulses, and the pulses generated by the pulse generator constitute at least one pulse train; The pulse sequence includes a plurality of basic sequences, the basic sequence includes a plurality of unit sequences, and the unit sequence includes a forward pulse and a reverse pulse; The inter-pulse delay of the pulses in the basic sequence is 10 to 30 times the inter-phase delay, and the time interval between two adjacent basic sequences of the same pulse sequence is 200 to 400 times the inter-phase delay.

6. The computer-readable storage medium according to claim 5, wherein: The unit sequence includes a first type of unit sequence and a second type of unit sequence; In the first type of unit sequence, the forward pulse precedes the reverse pulse; In the second type of unit sequence, the forward pulse follows the reverse pulse; The basic sequence includes the first type of unit sequence and / or the second type of unit sequence.

7. The computer-readable storage medium according to claim 5, wherein: The basic sequence includes at least 10 of the pulses, and the pulse sequence includes at least 50 of the pulses.

8. The computer-readable storage medium according to claim 1, wherein: The program also performs: Obtain an electrocardiogram; The pulse generator is controlled to generate the pulse sequence according to the electrocardiogram.

9. The computer-readable storage medium according to claim 8, wherein: The step of controlling the pulse generator to generate the pulse sequence according to the electrocardiogram comprises: The pulse generator is controlled to generate the pulse sequence within 30ms to 70ms after the onset of the R wave, and to stop generating the pulse sequence before the onset of the T wave.

10. A pulse ablation system, characterized in that: include: Pulse generator; An ablation catheter comprises a tube body, a head electrode and a ring electrode; the head electrode is arranged at the distal end of the tube body; the number of the ring electrodes is three, the three ring electrodes are arranged at intervals along the axial direction of the tube body, and the three ring electrodes are all sleeved on the outer surface of the tube body; the head electrode and all the ring electrodes are electrically connected to the pulse generator, and the head electrode and the ring electrode closest to it are used to form a positive electrode, and the remaining two ring electrodes are used to form a negative electrode; and, A controller is communicatively connected to the pulse generator and is configured to execute the program stored on the computer-readable storage medium according to any one of claims 1-9.

11. The pulse ablation system according to claim 10, characterized in that: The head electrode is provided with a perfusion hole; the tube body is provided with a perfusion channel extending along its own axial direction, and the distal end of the perfusion channel is communicated with the perfusion hole.

12. The pulse ablation system according to claim 10, characterized in that: The pulse ablation system further includes a three-dimensional mapping unit, which is communicatively connected to the controller and is also electrically connected to the ring electrodes.

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