Microwave ablation and multi-point electrical impedance real-time monitoring integrated needle and control system thereof

Abstract

This invention discloses an integrated needle for microwave ablation and multi-point impedance real-time monitoring, and its control system. The integrated needle comprises: a microwave transmission core for delivering microwave energy to the target tissue; an insulating support layer covering the outer periphery of the microwave transmission core, including a puncture head at the foremost tip of the needle and an insulating dielectric sleeve; and a flexible sensing layer covering the surface of the insulating support layer, including a flexible substrate and six annular sensing electrodes disposed on the flexible substrate. The six annular sensing electrodes are symmetrically distributed about the microwave radiation center, forming a first electrode pair, a second electrode pair, and a third electrode pair sequentially from far to near along the axial direction, with different axial spacing between the first, second, and third electrode pairs. This invention can effectively inhibit tissue carbonization under water-free conditions, increasing the sphericity of the ablation foci to above 0.72 and reducing the needle withdrawal force to 0.4N, achieving precise efficacy assessment and closed-loop control of carbonization prevention during the ablation process.

Description

Technical Field

[0001] This invention falls under the technical field of medical device technology, specifically relating to an integrated ablation needle with microwave ablation and multi-point bioelectrical impedance sensing functions, and its control system. Background Technology

[0002] Microwave ablation still faces a challenge in efficacy assessment in clinical practice: the risk of tissue carbonization. Because microwave energy density is extremely high near the antenna radiation window, the temperature in this area can exceed 100°C or even reach over 150°C within a short period. When tissue moisture evaporates rapidly, the tissue surrounding the ablation needle can dry out, char, or even carbonize. Carbonized tissue not only provides strong shielding against microwave energy, hindering heat diffusion to distal areas and causing the ablation lesion to appear as an ellipsoid with an excessively long axis instead of an ideal sphere, but it also easily adheres severely to the ablation needle. Adhesion not only makes postoperative needle removal difficult but can also lead to massive bleeding or tumor cell implantation along the needle tract.

[0003] Bioelectrical impedance analysis (BIA) technology measures the complex impedance of biological tissues under low-frequency electric fields, sensitively reflecting changes in extracellular fluid, cell membrane integrity, and tissue water content. In the initial stages of heating, tissue impedance decreases slightly with increasing temperature. However, during coagulation, necrosis, and carbonization, the impedance modulus undergoes a dramatic shift of several times or even tens of times due to water loss and cell structure disintegration. Therefore, integrating multi-point bioelectrical impedance monitoring onto the ablation needle to provide physical indicators for real-time feedback control is a key pathway to achieving "precise ablation" and "carbonization-free ablation." However, existing impedance monitoring technologies are mostly discrete or single-point, making deep integration with microwave antennas within the sub-millimeter needle body difficult. Furthermore, electromagnetic interference remains a core bottleneck restricting its clinical application. Summary of the Invention

[0004] The purpose of this invention is to provide an integrated microwave ablation and multi-point impedance real-time monitoring needle and its control system, which aims to solve the problems of traditional ablation needles being prone to central tissue carbonization under water-free conditions and sensor being severely interfered with by microwave fields, so as to achieve accurate assessment of the ablation process and carbonization-free large-volume ablation.

[0005] To achieve the above objectives, the present invention adopts the following technical solution:

[0006] A microwave ablation and multi-point impedance real-time monitoring integrated needle includes:

[0007] The microwave transmission core is used to deliver microwave energy to the target tissue;

[0008] An insulating support layer, covering the outer periphery of the microwave transmission core, includes a puncture head located at the very tip of the needle and an insulating dielectric sleeve;

[0009] The flexible sensing layer covers the surface of the insulating support layer and includes a flexible substrate and six annular sensing electrodes disposed on the flexible substrate. The six annular sensing electrodes are symmetrically distributed about the microwave radiation center and form a first electrode pair, a second electrode pair, and a third electrode pair in sequence from far to near along the axial direction. The first, second, and third electrode pairs have different axial spacings.

[0010] Preferably, the axial spacing of the first electrode pair is 26 mm, the axial spacing of the second electrode pair is 18 mm, and the axial spacing of the third electrode pair is 10 mm.

[0011] Preferably, each annular sensing electrode has a width of 2 mm and a thickness of 0.2 mm.

[0012] The present invention also provides a control system for the integrated needle for microwave ablation and multi-point impedance real-time monitoring.

[0013] A control system for the aforementioned integrated microwave ablation and multi-point impedance real-time monitoring needle includes:

[0014] A microwave power source is used to generate microwave energy and deliver it to the integrated microwave ablation and multi-point impedance real-time monitoring needle.

[0015] Impedance analysis module is used to apply excitation signal to the annular sensing electrode of the integrated microwave ablation and multi-point impedance real-time monitoring needle and collect response signal;

[0016] The main control unit is connected to both the microwave power source and the impedance analysis module, and is configured to execute the following control logic:

[0017] Timing alternation logic: The ablation process is divided into a recurring ablation phase and a measurement phase, wherein the duration of the ablation phase is... The measurement phase duration is 10 seconds. It is 1 second;

[0018] During the measurement phase, the main control unit controls the microwave power source to physically cut off its output and controls the impedance analysis module to turn on to acquire electrical signals.

[0019] Preferably, the impedance analysis module applies an AC constant current excitation signal with a frequency of 20kHz and an amplitude of 5mA to the ring sensing electrode, and uses a four-electrode measurement method to acquire the response voltage to calculate the complex impedance.

[0020] Preferably, the main control unit calculates the relative impedance change characteristic quantity, and automatically shuts off the microwave output when the relative impedance change characteristic quantity exceeds a preset threshold.

[0021] Preferably, the impedance analysis module acquires tissue impedance information at different depths by switching different electrode pair combinations during the measurement phase; the switching includes acquiring voltage by using one pair of electrodes as the excitation electrode pair and another pair of electrodes as the measurement electrode pair.

[0022] Preferably, the main control unit includes a main control switch matrix for switching different electrode pair combinations to obtain the response voltages of the first electrode pair, the second electrode pair, and the third electrode pair in real time.

[0023] The present invention also provides a method for real-time monitoring and control of microwave ablation based on the system.

[0024] A method for real-time monitoring and control of microwave ablation based on the system includes the following steps:

[0025] Step 1: Divide the ablation process into a recurring ablation phase and a measurement phase, wherein the duration of the ablation phase is... The measurement phase duration is 10 seconds. It is 1 second;

[0026] Step 2: During the measurement phase, the microwave output is physically cut off, and the response voltage signal under different electrode pair combinations is collected through the ring sensing electrode of the integrated microwave ablation and multi-point impedance real-time monitoring needle. The complex impedance modulus is extracted by discrete Fourier transform.

[0027] Step 3: Calculate the relative impedance change characteristic. When the relative impedance change characteristic exceeds the preset threshold, automatically adjust the microwave output power or turn off the microwave output.

[0028] Preferably, in step 2, after obtaining the complex impedance modulus, the main control unit runs a multi-feature fusion prediction model to classify and predict the state of the ablated tissue and calculate the range of the solidification zone; the multi-feature fusion prediction model is a Stacking-XGBoost model, which integrates the outputs of support vector regression and extreme learning machine.

[0029] Beneficial effects: Compared with the prior art, the present invention has the following advantages:

[0030] (1) By integrating a flexible sensor array on the surface of the ablation needle, the present invention realizes the "in-situ" perception of the ablation state, solves the problem of the ablation thermal field being invisible, and enables doctors to grasp the degree of tissue degeneration in real time.

[0031] (2) By using time reuse logic and specific impedance change threshold (15%~115%) control, without increasing the water cooling circulation system, the carbonization of the tissue center is effectively avoided, making the shape of the ablation lesion closer to the ideal sphere, and the needle removal force is reduced from 3.5N to 0.4N, which basically eliminates tissue adhesion.

[0032] (3) It integrates a multi-feature fusion prediction algorithm, which can quantitatively give the ablation range, significantly improve the accuracy of the operation, and provide a scientific basis for the complete inactivation of tumors. Attached Figure Description

[0033] Figure 1 : A geometric model diagram of a microwave ablation and multi-point impedance real-time monitoring needle.

[0034] Figure 2 (a) is a cross-sectional view of the needle system, and (b) is a side view and unfolded design drawing of the multi-point sensing flexible electrode (FPC).

[0035] Figure 3 Timing diagram of microwave ablation and electrical impedance measurement.

[0036] Figure 4 : Schematic diagram of the current excitation and voltage measurement method of the present invention.

[0037] Figure 5 Simulation cloud diagrams of current density distribution at different ablation times in this invention. Among them, (a) represents the ablation state at 0s, and (b) represents the ablation state at 180s.

[0038] Figure 6 : A structural diagram of the experimental system of this invention.

[0039] Figure 7 : A graph showing the relative change in impedance amplitude versus temperature over ablation time.

[0040] Figure 8 Comparison of microwave ablation (50W) carbonization control based on real-time monitoring feedback of multi-point impedance. Detailed Implementation

[0041] The present invention will now be described in detail with reference to the accompanying drawings and embodiments.

[0042] Example 1: Integrated needle for microwave ablation and real-time monitoring of multi-point impedance

[0043] This embodiment provides an integrated needle for microwave ablation and real-time monitoring of multi-point electrical impedance, the structure of which is as follows: Figure 1 and Figure 2 As shown.

[0044] like Figure 1 The diagram shows a geometric model of the integrated needle for microwave ablation and real-time multi-point impedance monitoring according to the present invention. The needle body is 120mm in length, with a puncture head at the front end. The puncture head is a ceramic flexible tube with a length of 11mm. The core of the needle body, from the inside out, includes:

[0045] The microwave transmission core is used to deliver microwave energy to the target tissue;

[0046] An insulating support layer is wrapped around the outer periphery of the microwave transmission core.

[0047] A flexible sensing layer is wrapped around the surface of the insulating support layer.

[0048] The microwave transmission core comprises an inner conductor and a semi-coaxial cable. Specifically, the semi-coaxial cable has a radius of 0.95 mm, and the inner conductor has a radius of 0.15 mm. At the radiation window, the outer shielding layer of the semi-coaxial cable is circumferentially cut to form a radiation window with a width of 1.5 mm to ensure the release of microwave energy.

[0049] When the microwave transmission core is in operation, the microwave electric field distribution within the tissue satisfies the following transmission equation:

[0050]

[0051] Where E is the electric field strength, σ is the conductivity, ε is the dielectric constant, μ is the magnetic permeability, and t is the instantaneous time variable of the microwave electromagnetic field.

[0052] External heat source generated by tissue absorption of microwave energy Satisfying the formula:

[0053]

[0054] This heat source drives tissue temperature changes, following the Pennes biological heat conduction model:

[0055]

[0056] Where ρ is tissue density, C is specific heat capacity, k is thermal conductivity, and T is tissue temperature.

[0057] By optimizing the antenna geometry, energy is evenly distributed in the radiation window, thus initially suppressing local hotspots.

[0058] The insulating support layer includes a PTFE insulating medium. The PTFE medium covers the outer periphery of the microwave transmission core, providing electrical isolation and mechanical support.

[0059] A flexible sensing layer covers the surface of an insulating support layer and includes a flexible substrate and six annular sensing electrodes disposed on the flexible substrate, namely annular sensing electrode A1, annular sensing electrode A2, annular sensing electrode B1, annular sensing electrode B2, annular sensing electrode C1, and annular sensing electrode C2. The flexible substrate is a polyimide (PI) film with a thickness of 0.11 mm.

[0060] Six ring-shaped sensing electrodes are symmetrically distributed about the microwave radiation center. Along the axial direction from farthest to near (from the end furthest from the needle tip to the end closest to the needle tip), they sequentially form the first electrode pair (A1-A2), the second electrode pair (B1-B2), and the third electrode pair (C1-C2), with different axial spacing between the first, second, and third electrode pairs. Specifically:

[0061] The axial spacing of the first electrode pair (A1-A2) is 26 mm (edge ​​region).

[0062] The axial spacing of the second electrode pair (B1-B2) is 18 mm (transition zone).

[0063] The axial spacing of the third electrode pair (C1-C2) is 10 mm (core area).

[0064] To optimize the coating process, the electrodes are precisely configured with this spacing. This configuration ensures that the sensor covers a tissue target ablation thermal field with a radius of approximately 40 mm.

[0065] Each annular sensing electrode is 2 mm wide and 0.2 mm thick. This configuration ensures that the sensor covers a tissue target ablation thermal field with a radius of approximately 40 mm.

[0066] During the measurement phase, a 20kHz alternating current is injected into the multi-point monitoring sensing layer through electrodes. The potential distribution φ within the tissue satisfies the generalized Laplace equation:

[0067]

[0068] in, The conductivity is complex. The central control unit obtains tissue impedance information at different depths by switching electrode pairs (e.g., A1-A2 excitation, B1-B2 measurement), realizing all-round perception of the thermal field from the center to the edge.

[0069] Example 2: Control system for an integrated needle for microwave ablation and real-time multi-point impedance monitoring

[0070] This embodiment provides a control system for an integrated needle used in Embodiment 1 for microwave ablation and real-time monitoring of multi-point impedance. For example... Figure 6 As shown, the control system includes: a microwave power source, an impedance analysis module, and a main control unit, wherein:

[0071] A microwave power source is used to generate microwave energy and deliver it to the integrated needle.

[0072] The impedance analysis module is used to apply an excitation signal to the ring sensing electrode of the integrated needle and acquire the response signal.

[0073] The main control unit (e.g., an STM32 main control board) is connected to the microwave power source and the impedance analysis module, respectively.

[0074] The main control unit executes the following control logic:

[0075] Timing alternation logic: The ablation process is divided into a recurring ablation phase and a measurement phase, wherein the duration of the ablation phase is... The measurement phase duration is 10 seconds. The duration is 1 second. During the measurement phase, the main control unit physically cuts off the microwave power source output and controls the impedance analysis module to start acquiring electrical signals. This time-multiplexing (TDM) control logic can eliminate microwave high-frequency coupling interference.

[0076] The impedance analysis module is configured to apply an AC constant current excitation signal with a frequency of 20kHz and an amplitude of 5mA to the ring sensing electrode, and to use a four-electrode measurement method to acquire the response voltage to calculate the complex impedance.

[0077] The principle of eliminating contact resistance using the four-electrode measurement method is as follows: Figure 4 As shown: A current I is injected into one pair of electrodes, and a voltage U is sampled on the other pair of electrodes. The regional impedance Z = U / I is then calculated. For example, a current is injected into A1-A2, and a voltage is sampled at B1-B2 or C1-C2.

[0078] The main control unit calculates the characteristic quantity of relative impedance change. :

[0079]

[0080] in, The initial impedance is... The impedance at the time of ablation; when When the system enters the preset carbonization monitoring range (preferably 15%~115%), the system automatically adjusts the microwave output power; when it reaches or exceeds the upper limit of the range, the system automatically shuts off the microwave output to prevent carbonization.

[0081] The system has a built-in logic judgment module: when At the same time, maintain a full ablation power of 40W;

[0082] when When the system detects that the tissue has entered the pre-carbonization zone, it automatically adjusts the low microwave duty cycle to suppress the central polarity.

[0083] During the measurement phase, the impedance analysis module acquires tissue impedance information at different depths by switching between different electrode pair combinations. Switching involves acquiring voltage using one electrode pair as the excitation electrode pair and the other as the measurement electrode pair. Specifically, the system supports multiple excitation modes:

[0084] Mode (a): Inject current into A1-A2 and sample voltage at B1-B2 or C1-C2;

[0085] Mode (b): Inject current into B1-B2 and sample voltage at A1-A2 or C1-C2;

[0086] Mode (c): Inject current into C1-C2 and sample voltage at A1-A2 or B1-B2.

[0087] By using the four-electrode cyclic sampling method, the interference of contact impedance between the electrode and the tissue was effectively eliminated.

[0088] The main control unit includes a main control switch matrix, used to switch different electrode pair combinations to obtain the response voltages of the first, second, and third electrode pairs in real time. The central control unit obtains the response voltages of different electrode pairs (A1-A2, B1-B2, C1-C2) in real time through the main control switch matrix and executes the connection control logic.

[0089] The system will complete a full work cycle. Classified as ablation phase With measurement phase :

[0090] when At this time, the microwave power supply is turned on to perform high-energy ablation;

[0091] when At this time, the microwave power supply is physically turned off, and the impedance analysis module fills the excitation electrode with a 5mA sinusoidal signal to perform multi-point impedance sampling.

[0092] Example 3: Real-time monitoring and control method for microwave ablation

[0093] This embodiment provides a real-time monitoring and control method for microwave ablation based on the control system of Embodiment 2. The method includes the following steps:

[0094] Step 1: Timing Partitioning

[0095] The ablation process is divided into a recurring ablation phase and a measurement phase, wherein the duration of the ablation phase is... The measurement phase duration is 10 seconds. It takes 1 second.

[0096] Step 2: Measurement Phase Acquisition and Signal Processing

[0097] During the measurement phase, the microwave output is physically cut off, and the response voltage signal under different electrode pair combinations is collected through the ring sensing electrode of the integrated needle. The complex impedance modulus is extracted by discrete Fourier transform (DFT).

[0098] Specifically, the four-electrode measurement method is used to eliminate contact impedance: current is injected into one pair of electrodes, and voltage is collected on the other pair. For example, current I is injected into electrode pair A1-A2, and voltage U is collected on B1-B2, or voltage U can be collected on C1-C2. The impedance magnitude of this region, |Z|=|U / I|, is then calculated. By performing a discrete Fourier transform on the collected time-domain voltage signal, the amplitude and phase at the corresponding frequency (20kHz) are extracted, thereby obtaining the complex impedance information.

[0099] Step 3: Threshold Determination and Closed-Loop Control

[0100] Calculate the characteristic quantity of relative impedance change :

[0101]

[0102] in, The initial impedance is... The impedance at the time of ablation; when When the system enters the preset carbonization monitoring range (preferably 15%~115%), the system automatically adjusts the microwave output power; when it reaches or exceeds the upper limit of the range, the system automatically shuts off the microwave output to prevent carbonization.

[0103] The system has a built-in logic judgment module: when At the same time, maintain a full ablation power of 40W;

[0104] when When the system detects that the tissue has entered the pre-carbonization zone, it automatically adjusts the low microwave duty cycle to suppress the central polarity.

[0105] In step 2, after obtaining the complex impedance modulus, the process also includes running a multi-feature fusion prediction model through the main control unit to classify and predict the state of the ablated tissue and calculate the range of the solidification zone. The multi-feature fusion prediction model is a Stacking-XGBoost model, which integrates the outputs of support vector regression (SVR) and extreme learning machine (ELM).

[0106] The specific implementation of this model is as follows: Multiple electrode pairs (A1-A2, B1-B2, C1-C2) are used as inputs, collecting multi-dimensional features such as impedance magnitude, phase, and relative impedance change. Initial predictions are first performed using SVR and ELM, respectively. Then, the outputs of these two models are used as the second-layer features input to the XGBoost model for final prediction. The output classifies the tissue ablation state (normal, coagulation necrosis, carbonization) and the range of the coagulation zone (short axis, long axis, sphericity, etc.). Experimental verification shows that the prediction error of this model is limited to within -170~+110μm, and the coefficient of determination R0 is [value missing]. 2 Greater than 0.88.

[0107] like Figure 5 The figure shows the simulation cloud diagram of current density distribution at different ablation times according to an embodiment of the present invention. (a) represents the ablation state at 0s, where the current streamlines are uniformly distributed; (b) represents the ablation state at 180s, where the density streamlines show obvious sparsity and path distortion due to the sudden change in local impedance caused by heating of the central tissue. The simulation demonstrates the technological advancement of inverting the degree of tissue denaturation by monitoring the field response with current.

[0108] like Figure 7 The figure shows the impedance versus temperature kinetics curves under an ablation power of 40W according to an embodiment of the present invention. The results show that in the first 60 seconds of ablation, the relative change in impedance reaches an inflection point (approximately 18.7%) as the temperature rises to 60°C; after 180 seconds of ablation, the tissue enters the carbonization risk zone, and the impedance value increases exponentially. The closed-loop algorithm of this invention... Threshold interception within the range of 15% to 115% increased the short diameter of the ablation lesion from 18.6 mm to 28.1 mm, and improved the simulation accuracy from 0.59 to 0.72. Both simulation and real-world results demonstrate that this invention has significant clinical advantages in dispersing thermal deposition pressure, eliminating adhesion risks, and increasing ablation volume.

[0109] like Figure 8 As shown, (a) illustrates the ablation effect under a constant power output of 50W. It can be seen that the rapid heating of the tissue around the needle tip leads to a severe and irregular carbonization zone. The central charred area is relatively large, indicating that the tissue excessively dehydrates in a short time due to the lack of real-time feedback. This "barrier effect" limits the effective conduction of microwaves to the surrounding deep tissues, resulting in a relatively blurred ablation boundary and uneven heat distribution. (b) shows the ablation effect after applying the control system of this invention. Also under a 50W environment, after applying the "Microwave Ablation and Multi-Point Impedance Real-Time Monitoring Integrated Needle and its Control System" of this patent, the ablation zone shows significant optimization: not only is carbonization significantly suppressed, but the central charred area is significantly reduced and more compact, avoiding energy shielding caused by excessive carbonization. Furthermore, the ablation morphology is regular, with the ablation zone exhibiting a more spherical / quasi-circular shape, effectively balancing the influence of the heat sink effect.

[0110] Simulation and experimental results show that the present invention can significantly inhibit tissue carbonization under waterless cooling conditions, increase the short diameter of the ablation lesion from 18.6 mm to 28.1 mm, improve the sphericity from 0.59 to 0.72, reduce the needle withdrawal force from 3.5 N to 0.4 N, and make the ablation morphology closer to the ideal sphere, providing accurate and real-time efficacy assessment and intelligent shutdown basis for tumor microwave ablation.

[0111] The above description is only a preferred embodiment of the present invention. It should be noted that for those skilled in the art, several improvements and modifications can be made without departing from the principle of the present invention, and these improvements and modifications should also be considered within the scope of protection of the present invention.

Claims

1. A microwave ablation and multi-point impedance real-time monitoring integrated needle, characterized in that, include: The microwave transmission core is used to deliver microwave energy to the target tissue; An insulating support layer covers the outer periphery of the microwave transmission core, including a puncture head at the very tip of the needle and an insulating dielectric sleeve. The flexible sensing layer covers the surface of the insulating support layer and includes a flexible substrate and six annular sensing electrodes disposed on the flexible substrate. The six annular sensing electrodes are symmetrically distributed about the microwave radiation center and form a first electrode pair, a second electrode pair, and a third electrode pair in sequence from far to near along the axial direction. The first, second, and third electrode pairs have different axial spacings.

2. The integrated needle for microwave ablation and multi-point impedance real-time monitoring according to claim 1, characterized in that, The axial spacing of the first electrode pair is 26 mm, the axial spacing of the second electrode pair is 18 mm, and the axial spacing of the third electrode pair is 10 mm.

3. The integrated needle for microwave ablation and multi-point impedance real-time monitoring according to claim 1, characterized in that, Each ring-shaped sensing electrode is 2 mm wide and 0.2 mm thick.

4. A control system for the integrated microwave ablation and multi-point impedance real-time monitoring needle as described in claim 1, characterized in that, include: A microwave power source is used to generate microwave energy and deliver it to the integrated microwave ablation and multi-point impedance real-time monitoring needle. Impedance analysis module is used to apply excitation signal to the annular sensing electrode of the integrated microwave ablation and multi-point impedance real-time monitoring needle and collect response signal; The main control unit is connected to both the microwave power source and the impedance analysis module, and is configured to execute the following control logic: Timing alternation logic: The ablation process is divided into a recurring ablation phase and a measurement phase, wherein the duration of the ablation phase is... The measurement phase duration is 10 seconds. It is 1 second; During the measurement phase, the main control unit controls the microwave power source to physically cut off its output and controls the impedance analysis module to turn on to acquire electrical signals.

5. The system according to claim 4, characterized in that, The impedance analysis module applies an AC constant current excitation signal with a frequency of 20kHz and an amplitude of 5mA to the ring sensing electrode, and uses a four-electrode measurement method to acquire the response voltage to calculate the complex impedance.

6. The system according to claim 4, characterized in that, The main control unit calculates the relative impedance change characteristic quantity, and automatically shuts off the microwave output when the relative impedance change characteristic quantity exceeds a preset threshold.

7. The system according to claim 4, characterized in that, During the measurement phase, the impedance analysis module acquires tissue impedance information at different depths by switching different electrode pair combinations; the switching includes acquiring voltage by using one pair of electrodes as the excitation electrode pair and another pair of electrodes as the measurement electrode pair.

8. The system according to claim 4, characterized in that, The main control unit includes a main control switch matrix, which is used to switch different electrode pair combinations to obtain the response voltages of the first electrode pair, the second electrode pair, and the third electrode pair in real time.

9. A method for real-time monitoring and control of microwave ablation based on the system described in claim 4, characterized in that, Includes the following steps: Step 1: Divide the ablation process into a recurring ablation phase and a measurement phase, wherein the duration of the ablation phase is... The measurement phase duration is 10 seconds. It is 1 second; Step 2: During the measurement phase, the microwave output is physically cut off, and the response voltage signal under different electrode pair combinations is collected through the ring sensing electrode of the integrated microwave ablation and multi-point impedance real-time monitoring needle. The complex impedance modulus is extracted by discrete Fourier transform. Step 3: Calculate the relative impedance change characteristic. When the relative impedance change characteristic exceeds the preset threshold, automatically adjust the microwave output power or turn off the microwave output.

10. The method according to claim 9, characterized in that, In step 2, after obtaining the complex impedance modulus, the main control unit runs a multi-feature fusion prediction model to classify and predict the state of the ablated tissue and calculate the range of the solidification zone. The multi-feature fusion prediction model is a Stacking-XGBoost model, which integrates the outputs of support vector regression and extreme learning machine.

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