Method for detecting tissue ablation effect

Abstract

The invention relates to the technical field of medical instruments, and discloses a method for detecting a tissue ablation effect. The method comprises the following steps: acquiring an initial bioelectrical impedance value and an initial electrical conduction path state of a target tissue; in the ablation process, the real-time bioelectrical impedance value of the target tissue is periodically obtained, and the real-time electrical conduction path state of the target tissue is synchronously obtained. The real-time electrical conduction path state is detected through induction points arranged on the two sides of the ablation electrode. And finally, when the real-time bioelectrical impedance value meets a preset electrical impedance judgment condition and the real-time electrical conduction path state is an off state, judging that the target tissue reaches a preset ablation end point. According to the method, comprehensive judgment is carried out through double indexes of bioelectrical impedance and the electrical conduction path state, the problem that misjudgment is caused by tissue lesion only depending on a single electrical impedance parameter is solved, the ablation end point judgment is more accurate and objective, and the success rate and safety of an operation are remarkably improved.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and in particular to a method for detecting the effect of tissue ablation. Background Technology

[0002] Pulsed electric field ablation is a medical technology applied in fields such as cardiac electrophysiology therapy and tumor treatment. This technology uses specialized ablation instruments to apply high-intensity microsecond or nanosecond-level electrical pulses to target tissues, causing irreversible electroporation of cell membranes and leading to apoptosis, thus achieving precise ablation of specific tissues. Because different cell types have different electroporation thresholds, this technology can selectively ablate target tissues (such as cardiomyocytes) while minimizing damage to adjacent nerves, blood vessels, and other tissues.

[0003] In current ablation surgery practices, determining whether the ablation operation has reached the expected endpoint is a crucial step in ensuring surgical effectiveness. Currently, a common method is to monitor changes in the bioelectrical impedance of the target tissue. Specifically, the operator uses ablation electrodes on an ablation device to ablate the tissue while simultaneously measuring the impedance value between the electrodes. During ablation, tissue cells undergo structural and electrical changes due to necrosis, typically manifested as a significant decrease in the impedance value between the electrodes. Therefore, the operator uses a decrease in impedance value to a predetermined threshold or a predetermined rate of change as the basis for determining the completion of ablation.

[0004] However, the inventors discovered that in clinical applications, the accuracy of techniques relying solely on bioelectrical impedance as a single parameter for endpoint determination can be limited in certain situations. The initial electrical properties of the target tissue to be ablated are not constant. For example, when the tissue itself has undergone pathological changes such as fibrosis or cancer, its baseline impedance value may deviate from the range of normal tissue. This difference in initial state can lead to distorted results when using a uniform impedance threshold based on empirical data for judgment. If the initial impedance value of the diseased tissue is low, the preset threshold may be reached before the tissue is completely and transmurally ablated, causing the operator to prematurely terminate the ablation operation, thus creating a risk of postoperative lesion recurrence. Therefore, the reliability of existing technologies in dealing with complex tissue conditions is insufficient, directly affecting the long-term success rate of the procedure. Summary of the Invention

[0005] The purpose of this invention is to provide a method for detecting the ablation effect of tissue, so as to solve the technical problem that the existing technology relies solely on bioelectrical impedance index to determine the ablation endpoint, which leads to inaccurate judgment and incomplete ablation in special cases such as when the target tissue is lesioned.

[0006] To achieve the above objectives, the present invention provides the following technical solution:

[0007] A method for detecting the effect of tissue ablation includes the following steps:

[0008] S1. The ablation device is placed against the target tissue to be ablated. The ablation device has at least one pair of ablation electrodes and at least one pair of sensing points. The ablation electrodes are used to apply ablation energy and perform bioelectrical impedance measurements, and the sensing points, independent of the ablation electrodes, are used to detect the state of electrical conduction pathways.

[0009] S2. Before ablation of the target tissue, baseline state measurements are performed. This step obtains the initial bioelectrical impedance values ​​between the ablation electrodes and the initial electrical conduction pathway state between the sensing points. The initial bioelectrical impedance values ​​and the initial electrical conduction pathway state are recorded as a benchmark for subsequent determinations.

[0010] S3. Real-time status monitoring is performed during the ablation of the target tissue. This step obtains the real-time bioelectrical impedance value between the ablation electrodes and simultaneously obtains the real-time electrical conduction pathway status between the sensing points.

[0011] S4. Based on the initial bioelectrical impedance value obtained in step S2, the real-time bioelectrical impedance value obtained in step S3, and the real-time electrical conduction pathway status, it is comprehensively determined whether the target tissue has reached the preset ablation endpoint.

[0012] In a specific embodiment, in step S4, the condition for determining that the target tissue has reached the preset ablation endpoint is defined as:

[0013] The preset impedance determination condition is met, and the real-time electrical conduction path is in an open state. Both conditions must be met simultaneously.

[0014] Preferably, the preset bioimpedance determination condition is achieved by calculating a normalized rate of change of bioimpedance. The normalized rate of change of bioimpedance is calculated based on the initial bioimpedance value and the real-time bioimpedance value, and its calculation formula is as follows:

[0015] ;

[0016] in:

[0017] This represents the normalized rate of change of electrical impedance;

[0018] This represents the initial bioelectrical impedance value;

[0019] This represents the real-time bioelectrical impedance value.

[0020] When the When the preset ratio threshold is reached or exceeded, the preset impedance determination condition is determined to be satisfied.

[0021] As another implementation, the preset impedance determination condition is achieved through absolute value comparison. Specifically, when the real-time bioelectrical impedance value is lower than or equal to a preset absolute impedance threshold, the preset impedance determination condition is determined to be met.

[0022] Furthermore, the determination logic for not reaching the preset ablation endpoint in step S4 includes:

[0023] When the preset impedance determination condition is met, but the real-time electrical conduction path is in a conducting state, it is determined that the target tissue has not reached the preset ablation endpoint.

[0024] Alternatively, if the preset impedance determination condition is not met, the target tissue is determined not to have reached the preset ablation endpoint, regardless of the state of the real-time electrical conduction path.

[0025] In a specific embodiment, the operation of obtaining the real-time electrical conduction path status in step S3 includes: applying a test electrical signal to one of the transmitting ends of the sensing point, detecting the test electrical signal at another receiving end of the sensing point, and determining the real-time electrical conduction path status based on the detection result.

[0026] Preferably, the test electrical signal is a weak high-frequency AC signal, whose energy is insufficient to produce an ablation effect on the target tissue.

[0027] Further, the specific steps for determining the real-time electrical conduction path status include: comparing the voltage amplitude of the test electrical signal detected by the receiving end with a preset voltage threshold. The real-time electrical conduction path status... The decision logic can be represented by the following function:

[0028] On state Off state ;

[0029] in:

[0030] A logical value representing the state of the real-time electrical conduction path;

[0031] This represents the voltage amplitude of the test electrical signal detected at the receiving end;

[0032] This represents the preset voltage threshold.

[0033] In one specific embodiment, after step S4, the method further includes: providing feedback to the operator via a human-computer interaction interface on the determination result of whether the target tissue has reached the preset ablation endpoint. The feedback may be one or more combinations of visual signals, digital displays, or audio prompts.

[0034] In summary, the present invention has at least one of the following beneficial technical effects:

[0035] 1. This invention obtains an independent physical indicator, namely the real-time electrical conduction pathway status, while acquiring real-time bioelectrical impedance values. The judgment results of the two indicators are logically combined. The ablation endpoint is determined only when the preset impedance judgment conditions are met and the real-time electrical conduction pathway status is disconnected. This avoids misjudgment caused by the initial abnormal electrical characteristics of the target tissue (such as low baseline impedance of lesion tissue) and the decrease of a single impedance indicator, thereby increasing the certainty of the ablation endpoint determination.

[0036] 2. This invention establishes a clear judgment logic, namely, when the preset impedance judgment condition is met, but the real-time electrical conduction path is still in a conducting state, the target tissue is judged not to have reached the preset ablation endpoint. This can prevent premature termination of the ablation operation due to the appearance of a single indicator, and directly reduce the risk of treatment failure or the need for a second operation due to incomplete ablation.

[0037] 3. This invention comprehensively determines two parameters—bioelectrical impedance value and electrical conduction pathway status—and provides the operator with a direct and unambiguous indication of the ablation endpoint through a human-computer interaction interface, based on the final, clear determination result (i.e., whether the target tissue has reached the preset ablation endpoint). This eliminates the need for the operator to simultaneously interpret and weigh multiple potentially contradictory physical quantities, simplifying the decision-making process and facilitating the formation of a closed-loop operation procedure. Attached Figure Description

[0038] Figure 1 This is a system functional block diagram of a method for detecting the effect of tissue ablation according to an embodiment of the present invention;

[0039] Figure 2 This is a flowchart of a tissue ablation effect detection method according to an embodiment of the present invention;

[0041] Figure 3 This is a perspective view of the ablation device in an embodiment of the present invention;

[0042] Figure 4 This is a schematic diagram of the end structure of the probe unit in an embodiment of the present invention. Detailed Implementation

[0043] See attached document Figure 3 , Figure 3 This is a perspective view of the ablation device 100 in an embodiment of the present invention. (Refer to the attached diagram.) Figure 1 , Figure 1 This is a system functional block diagram for performing a tissue ablation effect detection method according to an embodiment of the present invention.

[0044] The present invention provides an ablation device 100 for detecting tissue ablation effect. The ablation device 100 may include a probe unit 10 and a signal processing and control unit 20.

[0045] See attached document Figure 4 , Figure 4 This is a schematic diagram of the end structure of the probe unit 10 in an embodiment of the present invention. Figure 4 As shown, the probe unit 10 is the part of the ablation device 100 that directly contacts the target tissue, and its end is integrated with at least one pair of ablation electrodes 11 and at least one pair of sensing points 12. The ablation electrodes 11 and the sensing points 12 are electrically insulated from each other and are arranged according to a preset geometric position relationship. For example, the sensing points 12 may be symmetrically distributed on the outside of the ablation electrodes 11.

[0046] The ablation electrode 11 is made of a conductive, biocompatible material, such as medical-grade stainless steel or a platinum-iridium alloy. The ablation electrode 11 has a dual function: firstly, as an energy output terminal, it is used to apply ablation energy to the target tissue; secondly, as a sensing terminal for impedance measurement, it is used to obtain the bioelectrical impedance value between the ablation electrodes.

[0047] Sensing point 12 is also made of a conductive, biocompatible material. Independent of the ablation energy circuit, sensing point 12 serves as a dedicated signal transceiver for detecting the state of the electrical conduction pathway between sensing points. One sensing point acts as the transmitter, and the other as the receiver.

[0048] The signal processing and control unit 20 is connected to the probe unit 10 via a cable. The signal processing and control unit 20 is the central part that executes the core algorithm of the method of the present invention. In a specific embodiment, the signal processing and control unit 20 includes: an ablation energy driving module 21, a bioelectrical impedance measurement module 22, a conduction pathway detection module 23, a central processing module 24, and a human-computer interaction module 25.

[0049] It should be noted that although this embodiment describes the ablation energy driving module 21, the bioelectrical impedance measurement module 22, the conduction pathway detection module 23, the central processing module 24, and the human-computer interaction module 25 as being integrated inside the signal processing and control unit 20, in other embodiments, some functional modules (such as the conduction pathway detection module 23) may also be physically independent external devices that communicate with the central processing module 24 through a standard data interface, thereby achieving the functions of the present invention.

[0050] The ablation energy driving module 21 is connected to the ablation electrode 11 and is used to generate and output radio frequency ablation energy with specific power and duration according to the control command issued by the central processing module 24.

[0051] The bioelectrical impedance measurement module 22 is connected to the ablation electrode 11 and is used to apply a preset measurement current to the target tissue through the ablation electrode 11, and simultaneously detect the voltage generated between the ablation electrodes 11, and calculate the bioelectrical impedance value according to Ohm's law. Its calculation principle follows the formula below:

[0052] ;

[0053] in:

[0054] Represents bioelectrical impedance value;

[0055] This represents the voltage detected between the ablation electrodes 11;

[0056] This represents the measurement current applied to the ablation electrode 11.

[0057] The conduction path detection module 23 is connected to the sensing point 12. Module 23 includes a test electrical signal generator and a signal detector. The test electrical signal generator generates a test electrical signal and applies it to the sensing point, which acts as the transmitting end; the signal detector is connected to the sensing point, which acts as the receiving end, and is used to detect the voltage amplitude of the test electrical signal.

[0058] The central processing module 24 is the core of the signal processing and control unit 20. It communicates with the ablation energy drive module 21, the bioelectrical impedance measurement module 22, the conduction pathway detection module 23, and the human-machine interface module 25 via an internal bus for data communication and control signal transmission. The central processing module 24 includes a processor and a memory. The memory stores an executable program. When the processor executes the program, it performs data acquisition, storage, calculation, and comprehensive determination of the ablation endpoint in the method of this invention.

[0059] The human-computer interaction module 25 is connected to the central processing module 24 and is used to receive the final judgment result output by the central processing module 24. Through its included display screen, status indicator light or sound generator and other components, the result is presented to the operator in the form of visual or auditory signals.

[0060] See attached document Figure 2 , Figure 2 This is a flowchart of a method for detecting the effect of tissue ablation according to an embodiment of the present invention. The following will be discussed in conjunction with the attached diagram. Figure 1 The ablation device 100 described herein provides a detailed explanation of the detection method of the present invention.

[0061] The execution of the method of the present invention begins with step S1, in which the operator places the end of the probe unit 10 against the surface of the target tissue to be ablated. This operation must ensure that both the ablation electrode 11 and the sensing point 12 form stable physical and electrical contact with the target tissue, providing a basis for subsequent electrical parameter measurements.

[0062] Before initiating ablation energy output, the central processing module 24 executes step S2, namely baseline state measurement. After the operator triggers this step through the human-machine interface module 25, the central processing module 24 first instructs the bioelectrical impedance measurement module 22 to acquire a bioelectrical impedance value, and uses this value as the initial bioelectrical impedance value. The data is stored in memory. Next, the central processing module 24 and the instruction conduction path detection module 23 acquire the initial electrical conduction path state and record this state as the initial electrical conduction path state.

[0063] Once the ablation operation begins, the method enters the real-time monitoring phase of step S3. The central processing module 24 instructs the ablation energy drive module 21 to output ablation energy to the ablation electrode 11. During this process, the central processing module 24 periodically instructs the bioelectrical impedance measurement module 22 to perform measurements at a preset sampling frequency (e.g., 10 times per second), thereby continuously acquiring real-time bioelectrical impedance values. .

[0064] Simultaneously, the central processing module 24 instructs the conduction path detection module 23 to acquire the real-time electrical conduction path status. In one specific embodiment, the test electrical signal generator within the conduction path detection module 23 generates a high-frequency weak AC signal, for example, a sine wave signal with a frequency of 50kHz and a voltage amplitude of 100mV, the energy of which is far below the threshold for generating tissue thermal effects. The signal is applied to the sensing point 12, which serves as the transmitting end. After passing through the target tissue between the sensing points, the signal is received by the sensing point 12, which serves as the receiving end. The signal detector within the conduction path detection module 23 measures the voltage amplitude of the signal received at the receiving end. .

[0065] Central processing module 24 receives voltage amplitude Then, it is compared with the preset voltage threshold in the memory. The physical principle behind this comparison is that tissue that has not been sufficiently ablated retains good conductivity. The conductivity is relatively high; however, the conductivity of tissue that has undergone sufficient ablation and coagulation decreases sharply, leading to... Significant attenuation. This change in conductivity stems from physiological alterations in the tissue during ablation: irreversible electroporation of the cell membrane occurs under the influence of a pulsed electric field, cell contents leak out, and intercellular structures are disrupted, thereby blocking effective ion conduction pathways between tissues. Therefore, when When the real-time electrical conduction path is determined to be in a conducting state; when When the time is right, the real-time electrical conduction path is determined to be disconnected.

[0066] After obtaining each set of real-time bioelectrical impedance values After confirming the real-time electrical conduction pathway status, the central processing module 24 immediately executes step S4, namely, the comprehensive determination of the ablation endpoint. The core of this step is based on the initial bioelectrical impedance value. Real-time bioelectrical impedance value The system uses three input quantities—the real-time electrical conduction path status, and the input quantity—to perform a logical decision.

[0067] First, the central processing module 24 determines whether a preset impedance determination condition is met. In one embodiment, this condition is determined by normalizing the impedance change rate. To achieve this. The central processing module 24 follows the formula. Calculate the current rate of change and compare it with a preset rate threshold (e.g., 0.4). If If the value is greater than or equal to a preset ratio threshold, then the preset impedance determination condition is met. In another embodiment, this condition can be simplified to directly using the real-time bioelectrical impedance value. Compared to an absolute impedance threshold (e.g., 50Ω), if If the absolute impedance threshold is lower than or equal to the threshold value, the condition is met.

[0068] After determining the preset impedance determination conditions, the central processing module 24 executes the final combinational logic determination:

[0069] If the preset impedance determination condition is met and the real-time electrical conduction path is in an open state, then the target tissue is determined to have reached the preset ablation endpoint.

[0070] If the preset impedance judgment condition is met, but the real-time electrical conduction path is in a conducting state, then the target tissue is determined not to have reached the preset ablation endpoint.

[0071] If the preset impedance judgment condition is not met, the target tissue is determined not to have reached the preset ablation endpoint, regardless of the real-time electrical conduction path status.

[0072] After the central processing module 24 completes the comprehensive determination in step S4 during each monitoring cycle, the method further includes the step of outputting the determination result. The central processing module 24 sends a logical result indicating whether the target tissue has reached the preset ablation endpoint to the human-computer interaction module 25, which then presents this result to the operator in one or more forms.

[0073] In one specific embodiment, the human-computer interaction module 25 includes a liquid crystal display screen 30. The central processing module 24 controls the display content of the liquid crystal display screen 30. (See attached...) Figure 3 As shown, the display screen 30 can be divided into multiple areas to simultaneously present multidimensional information related to the determination process.

[0074] A parameter display area 31 is used to display key values ​​in real time. This area may include: real-time bioelectrical impedance values. Digital display, normalized impedance change rate The percentage display provides the operator with quantitative information on process changes through real-time updates of these values. Furthermore, the parameter display area 31 can also display preset target thresholds (e.g., preset ratio thresholds), allowing the operator to visually compare the difference between real-time values ​​and target values, thus providing a clear expectation of the ablation process.

[0075] A status indication area 32 is used to visually display non-numerical status information. This area may include a real-time electrical conduction path status indicator 321, for example, using a graphic symbol for a closed circuit to represent the conducting state and a graphic symbol for an open circuit to represent the disconnected state.

[0076] A comprehensive results area 33 is used to display the final determination. This area presents the information in the most prominent way, for example, through large font text and background color blocks. When the determination result is that the ablation endpoint has not been reached, this area displays the text "Ablation in progress" with a blue background; when the determination result is that the preset ablation endpoint has been reached, this area displays the text "Ablation endpoint reached" with a green background.

[0077] As an alternative or supplementary feedback method, the human-computer interaction module 25 may also include one or more status indicator lights. For example, a dual-color LED indicator light flashes blue during the ablation process; when the preset ablation endpoint is determined to have been reached, the indicator light switches to a solid green light.

[0078] In addition, the human-computer interaction module 25 also includes a sound generator. During the ablation process, the sound generator emits no sound or emits a calm, periodic beep. When the preset ablation endpoint is reached, the central processing module 24 instructs the sound generator to emit a clear, distinctive beep (e.g., a long beep or three short beeps) to notify the operator via auditory signal. This combination of visual and auditory signals ensures that the determination result is received unambiguously by the operator.

[0079] Example 2: Application in pulmonary vein electrical isolation for atrial fibrillation

[0080] To illustrate the technical solution provided by this invention more specifically, the following will take the typical clinical application scenario of pulmonary vein electrical isolation for atrial fibrillation as an example to describe in detail the usage process of the device and method of this invention. The core objective of this surgery is to form a continuous and complete annular scar around the opening of the pulmonary vein by ablation point by point, so as to achieve electrical isolation of abnormal electrical signals from the pulmonary vein.

[0081] Preoperative preparation and baseline measurement:

[0082] The operator precisely navigates the probe unit 10 of the ablation device 100 to the target pulmonary vein opening. Before applying the first ablation energy, the operator first performs step S1, stabilizing the end of the probe unit 10 against the starting point of the planned circular ablation path. At this time, the operator triggers baseline measurement through the human-machine interface module 25, and the central processing module 24 performs step S2, acquiring and storing the initial bioelectrical impedance value and the initial electrical conduction pathway status at that point. Since the tissue has not yet been ablated, the initial electrical conduction pathway status is usually in a "conducting state".

[0083] Single-point ablation and endpoint determination:

[0084] The operator initiates ablation, and the central processing module 24 instructs the ablation energy drive module 21 to output energy, while simultaneously entering the real-time monitoring cycle of step S3. On the screen of the human-machine interaction module 25, the parameter display area 31 refreshes in real time the decrease of the bioelectrical impedance value, the status indicator area 32 shows that the electrical conduction pathway is still in the "conducting state", and the comprehensive result area 33 displays "ablation in progress".

[0085] As ablation proceeds, once the tissue at that point is fully ablated, its bioelectrical impedance value meets the preset impedance determination criteria (e.g., normalized rate of change reaches 40%). Simultaneously, due to the altered electrical properties of the local tissue at that point, its electrical conductivity is lost, and the real-time electrical conduction pathway switches to an "open state." At this point, the central processing module 24 executes the comprehensive determination in step S4. Since both conditions are met simultaneously, it is ultimately determined that the single point has reached the preset ablation endpoint. The comprehensive result area 33 of the human-machine interaction module 25 immediately turns green and displays "Ablation endpoint reached," along with an audible prompt. The operator then stops energy output.

[0086] Constructing isolation lines and gaps for verification:

[0087] The operator moves the probe unit 10 to the next target point adjacent to the previous ablation point, repeats the operation of step 2 above, and so on point by point, until a circular ablation path is finally formed.

[0088] The key advantage of this invention is demonstrated at this stage: after the ablation of the entire annular diameter is completed, the operator can use the ablation device 100 of this invention to verify the integrity of the isolation line. The operator slowly drags the probe unit 10 along the formed ablation diameter. During the dragging process, since the tissue along the entire diameter has been fully ablated, theoretically, no matter where the probe unit 10 moves to, the electrical conduction path of the tissue between its sensing points 12 should be "disconnected".

[0089] If the indicator in status indicator area 32 remains in the "disconnected state" throughout the test, it proves that the annular ablation path is continuous and complete, and the pulmonary vein electrical isolation is successful.

[0090] Conversely, if, while the probe is being moved to a certain location, the indicator in status indicator area 32 suddenly changes from "disconnected" to "conductive," it clearly indicates the presence of an insufficiently ablated conduction gap at that location. This gap is the root cause of surgical failure and atrial fibrillation recurrence. The operator can immediately perform supplementary ablation at that location until the electrical conduction pathway at that point returns to the "disconnected" state.

[0091] As can be seen from the above application examples, this invention not only provides accurate endpoint determination for operations at individual ablation points, but more importantly, it offers a direct and reliable real-time detection tool for verifying the continuity and integrity of linear ablation. It uses the loss of tissue electrical function (disruption of electrical conduction pathways) as one of the gold standards for judgment, effectively overcoming the misjudgment caused by tissue heterogeneity when relying solely on bioelectrical impedance parameters. This helps operators identify and compensate for potential conduction gaps, significantly improving the immediate success rate and long-term effectiveness of the procedure.

Claims

1. A method for detecting the effect of tissue ablation, characterized in that, include: S1. The ablation device is placed against the target tissue to be ablated, wherein the ablation device has at least one pair of ablation electrodes and at least one pair of sensing points; S2. Before ablation of the target tissue, obtain the initial bioelectrical impedance value between the ablation electrodes and the initial electrical conduction pathway state between the sensing points; S3. When ablation is performed on the target tissue, the real-time bioelectrical impedance value between the ablation electrodes and the real-time electrical conduction pathway status between the sensing points are obtained. S4. Based on the initial bioelectrical impedance value, the real-time bioelectrical impedance value, and the real-time electrical conduction pathway status, comprehensively determine whether the target tissue has reached the preset ablation endpoint.

2. The method for detecting the effect of tissue ablation according to claim 1, wherein, In step S4, the condition for determining that the target tissue has reached the preset ablation endpoint is: The preset impedance determination condition is met, and the real-time electrical conduction path is in an open state.

3. The method for detecting the effect of tissue ablation according to claim 2, wherein, The preset impedance determination condition is: the normalized impedance change rate calculated based on the initial bioimpedance value and the real-time bioimpedance value reaches a preset ratio threshold.

4. The method for detecting the effect of tissue ablation according to claim 2, wherein, Another way to implement the preset impedance determination condition is: the real-time bioelectrical impedance value is lower than or equal to the absolute impedance threshold.

5. The method for detecting the effect of tissue ablation according to claim 2, wherein, Step S4 also includes: When the preset impedance determination condition is met, but the real-time electrical conduction path is in a conducting state, it is determined that the target tissue has not reached the preset ablation endpoint.

6. The method for detecting the effect of tissue ablation according to claim 2, wherein, Step S4 also includes: When the preset electrical impedance determination condition is not met, it is determined that the target tissue has not reached the preset ablation endpoint.

7. The method for detecting tissue ablation effectiveness according to claim 1, wherein, In step S3, obtaining the real-time electrical conduction path status includes: applying a test electrical signal to one of the transmitting ends of the sensing point and detecting the test electrical signal at another receiving end of the sensing point, thereby determining the real-time electrical conduction path status.

8. The method for detecting the effect of tissue ablation according to claim 7, wherein, The steps for determining the state of the real-time electrical conduction path include: The voltage amplitude of the test electrical signal detected by the receiving end is compared with a voltage threshold.

9. The method for detecting the effect of tissue ablation according to claim 7, wherein, The test electrical signal is a weak high-frequency AC signal.

10. The method for detecting tissue ablation effectiveness according to claim 1, wherein, Following step S4, the method includes: The determination result of whether the target tissue has reached the preset ablation endpoint is fed back to the operator through the human-computer interaction interface.

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