Radio frequency thermal therapy equipment test system

Abstract

The invention discloses a radio frequency thermal therapy equipment testing system, relates to the technical field of equipment testing, and is used for solving the problems that the uncertainty in the energy transmission process is increased, and the system output stability and response precision are reduced. The output power is calculated in combination with an analog multiplier, and difference analysis is carried out in cooperation with ideal power; meanwhile, performing fast Fourier transform on the original signal to extract a frequency concentration ratio, and calculating a heat concentration coefficient; the tissue temperature at a needle is monitored based on an optical fiber fluorescence sensor, fluorescence detection temperature and observation temperature values are calculated in combination with fluorescence lifetime, difference analysis is performed to obtain a thermal response deviation factor, and the two values are fused to obtain a feedback calibration result for equipment performance optimization, and real-time monitoring of an energy state and abnormal heat accumulation identification are realized.

Description

Technical Field

[0001] The present invention relates to the technical field of equipment testing, and more specifically, to a radiofrequency hyperthermia equipment testing system. Background Art

[0002] Radiofrequency heating technology is widely used in various industrial and experimental systems to achieve energy transfer and thermal field regulation of specific materials or target areas. Such systems usually output radiofrequency energy to specific positions through high-frequency signal driving methods to form local thermal effects.

[0003] The prior art has the following deficiencies: Currently, in the actual application process, the output state of radiofrequency energy, frequency stability, power control accuracy, and the thermal response of the target area are all interfered by various environmental and equipment parameters. It is impossible to effectively associate power fluctuations with frequency energy distribution for discrimination, resulting in the inability to timely issue adjustment prompts when the thermal output is abnormal, increasing the uncertainty of the energy transfer process, and reducing the output stability and response accuracy of the system. Therefore, a radiofrequency hyperthermia equipment testing system is proposed.

[0004] The above information disclosed in the background art section is only used to enhance the understanding of the background of the present disclosure, and thus it may include information that does not constitute the prior art known to those of ordinary skill in the art. Summary of the Invention

[0005] In order to overcome the above-mentioned defects of the prior art, the embodiments of the present invention provide a radiofrequency hyperthermia equipment testing system, which uses an original signal multi-path processing mechanism, a power-frequency correlation modeling method, and a feedback determination mechanism based on thermal effect response to solve the problems proposed in the above background art.

[0006] To achieve the above object, the present invention provides the following technical solution. The radiofrequency hyperthermia equipment testing system includes a signal acquisition and processing module, a power measurement module, a frequency analysis module, and a temperature detection module, and the electrical signals of each module are connected: The signal acquisition and processing module is used to receive the original signal from the radiofrequency hyperthermia equipment and distribute the original signal to the power measurement module and the frequency analysis module for processing; The power measurement module uses a low-pass filter to remove the high-frequency components in the original signal, converts the processed original signal into current and detects it through an ammeter, and calculates the output power of the radiofrequency hyperthermia equipment according to the detection result of the ammeter and the real-time voltage through a analog multiplier, and transmits it to the frequency analysis module; The frequency analysis module is used to receive the output power of the radiofrequency hyperthermia device, process it to obtain the power difference of the radiofrequency hyperthermia device, perform fast Fourier transform processing on the original signal, extract the frequency concentration index, combine the power difference of the radiofrequency hyperthermia device, obtain the heat concentration coefficient, and transmit it to the temperature detection module; The temperature detection module measures the temperature distribution of the tissue contact needle based on the fiber optic fluorescence sensor, calculates the fluorescence detection temperature value using the relationship between the fluorescence afterglow lifetime and the temperature, and then processes it based on the average temperature of the contact electrode area to obtain the thermal response deviation factor. Combining the heat concentration coefficient, it determines to issue a calibration prompt.

[0007] In a preferred embodiment, in the signal acquisition and processing module, the original signal generated by the radiofrequency hyperthermia device during operation is acquired; The cut-off frequency is calculated through the resistance and capacitance of the low-pass filter; The original signal is input into the low-pass filter to obtain the processed original signal: If the signal frequency component in the original signal is lower than the cut-off frequency, the signal frequency component is retained; otherwise, the signal frequency component is filtered; The processed original signal is converted into a current signal that is linearly proportional to the corresponding original signal, and the current value of the current signal is detected by an ammeter.

[0008] In a preferred embodiment, in the power measurement module, the voltage value of the radiofrequency hyperthermia device is acquired in real time; The product of the current value of the current signal and the voltage value of the radiofrequency hyperthermia device is used as the output power of the radiofrequency hyperthermia device.

[0009] In a preferred embodiment, in the frequency analysis module, the user-input target power set value and the real-time monitoring parameters are combined, and using a preset prediction model, the ideal power of the radiofrequency hyperthermia device is obtained; The absolute difference between the output power of the radiofrequency hyperthermia device and the ideal power of the radiofrequency hyperthermia device is calculated to obtain the power difference of the radiofrequency hyperthermia device.

[0010] In a preferred embodiment, in the frequency analysis module, fast Fourier transform processing is performed on the original signal to extract the frequency concentration index. The specific process is as follows: Receive the original signal from the signal acquisition and processing module, convert it into a frequency domain signal through fast Fourier transform, generate a normalized frequency spectrum diagram, and use the ratio of the main frequency band energy to the total energy in the normalized frequency spectrum diagram as the frequency concentration index; The power difference of the radiofrequency hyperthermia device and the frequency concentration index are normalized.

[0011] In a preferred embodiment, in the frequency analysis module, the power difference of the normalized radiofrequency hyperthermia device and the frequency concentration index are substituted into the inverse difference tangent mapping function to obtain the heat concentration coefficient. The specific formula is expressed as: ; wherein, is the heat concentration coefficient, is the normalized frequency concentration index, is the power difference of the normalized radiofrequency hyperthermia device, , are the influence weights corresponding to the power difference of the normalized radiofrequency hyperthermia device and the frequency concentration index respectively, is the nonlinear compression characteristic of the function itself, and the outer layer realizes normalization processing.

[0012] In a preferred embodiment, in the temperature detection module, based on the fiber optic fluorescence sensor, the temperature distribution of the tissue contact needle is measured, and the fluorescence detection temperature value is calculated using the relationship between the fluorescence afterglow lifetime and the temperature; By emitting an excitation light pulse to the tissue contact needle area, exciting the fluorescent material to produce a fluorescence response, receiving and recording the afterglow decay process of the fluorescence signal to obtain the fluorescence afterglow lifetime, and using the function relationship model between the fluorescence afterglow lifetime and the temperature to obtain the fluorescence detection temperature value; According to the average temperature of the contact electrode area, the observed temperature value is obtained.

[0013] In a preferred embodiment, in the temperature detection module, based on the infrared temperature sensing array element, the temperature of the preset points in the contact electrode area is measured to obtain a set of discrete temperature values, and according to the preset electrode area division scheme, the discrete temperature values are statistically analyzed, and the observed temperature value is obtained according to the weighted average calculation; Substituting the fluorescence detection temperature value and the observed temperature value into the dual-temperature fusion comparison strategy to obtain the thermal response deviation factor. The specific steps are as follows: Calculate the deviation amounts of the fluorescence detection temperature value and the observed temperature value from the target temperature range respectively to obtain the observed temperature deviation factor and the fluorescence temperature deviation factor, and introduce the weight coefficient to fuse the two types of temperature response information. The specific formula for the thermal response deviation factor is expressed as follows: ; wherein, is the thermal response deviation factor, is the observed temperature deviation factor, is the fluorescence temperature deviation factor, is the observed temperature weight, is the fluorescence detection temperature weight.

[0014] In a preferred embodiment, in the temperature detection module, after normalizing the thermal response deviation factor, the thermal response deviation factor and the heat concentration coefficient are substituted into the product amplification difference adjustment model to obtain the thermal effect calibration coefficient. The specific formula is as follows: ; In the formula, is the thermal effect calibration coefficient, is the normalized thermal response deviation factor, is the heat concentration coefficient, is the non-linear response adjustment parameter.

[0015] In a preferred embodiment, in the temperature detection module, the thermal effect calibration coefficient is compared with a preset calibration threshold. If the thermal effect calibration coefficient is greater than or equal to the preset calibration threshold, a calibration prompt is issued; If the thermal effect calibration coefficient is less than the preset calibration threshold, there is no need to issue a calibration prompt.

[0016] Technical effects and advantages of the present invention: The present invention receives the original signal output during the operation of the radiofrequency hyperthermia device, removes the high-frequency noise components through a first-order passive RC low-pass filter, then converts the smoothed signal into a current signal, calculates the output power value through the combined operation of current sampling and analog multiplier, performs difference analysis in combination with the ideal power, and simultaneously performs a fast Fourier transform on the original signal to extract the frequency concentration degree, finally calculates the heat concentration coefficient, monitors the tissue temperature at the treatment needle in real time based on the fiber optic fluorescence sensor, calculates the fluorescence detection temperature and the observed temperature value in combination with the fluorescence lifetime, performs difference analysis on the two, obtains the thermal response deviation factor, combines the thermal response deviation factor and the heat concentration coefficient, and outputs the feedback calibration result for guiding the optimization of the device performance, realizing the real-time monitoring of the radiofrequency energy output state and the comprehensive evaluation of multi-dimensional parameters, and can effectively identify the abnormal heat distribution phenomenon caused by power deviation and frequency imbalance. BRIEF DESCRIPTION OF THE DRAWINGS

[0017] Figure 1 is the implementation flowchart of the radiofrequency hyperthermia device test system of the present invention.

[0018] Figure 2 is the step schematic diagram of the radiofrequency hyperthermia device test system of the present invention. DETAILED DESCRIPTION OF THE EMBODIMENTS

[0019] The following will clearly and completely describe the technical solutions in the embodiments of the present invention in conjunction with the accompanying drawings in the embodiments of the present invention. Obviously, the described embodiments are only a part of the embodiments of the present invention, rather than all the embodiments. All other embodiments obtained by those of ordinary skill in the art based on the embodiments of the present invention without creative efforts belong to the scope of protection of the present invention.

[0020] The present invention receives the original signal output during the operation of the radiofrequency hyperthermia device, removes the high-frequency noise components through a first-order passive RC low-pass filter, then converts the smoothed signal into a current signal, calculates the output power value through the combined operation of current sampling and analog multiplier, performs difference analysis in combination with the ideal power, and at the same time performs a fast Fourier transform on the original signal to extract the frequency concentration degree, finally calculates the heat concentration coefficient, monitors the tissue temperature at the treatment needle in real time based on the fiber optic fluorescence sensor, calculates the fluorescence detection temperature and the observed temperature value in combination with the fluorescence lifetime, performs difference analysis on the two to obtain the thermal response deviation factor, combines the thermal response deviation factor and the heat concentration coefficient, and outputs the feedback calibration result for guiding the optimization of the device performance.

[0021] Embodiment 1 Please refer to Figures 1 to 2 , a radiofrequency hyperthermia device test system, including a signal acquisition and processing module, a power measurement module, a frequency analysis module, and a temperature detection module, and the electrical signals of each module are connected; The functions of each module are as follows: The signal acquisition and processing module is used to receive the original signal from the radiofrequency hyperthermia device and distribute the original signal to the power measurement module and the frequency analysis module for processing; The power measurement module uses a low-pass filter to remove the high-frequency components in the original signal, converts the processed original signal into a current and detects it through an ammeter, calculates the output power of the radiofrequency hyperthermia device through an analog multiplier according to the detection result of the ammeter and the real-time voltage, and transmits it to the frequency analysis module; The frequency analysis module is used to receive the output power of the radiofrequency hyperthermia device for processing to obtain the power difference of the radiofrequency hyperthermia device, perform a fast Fourier transform on the original signal, extract the frequency concentration index, and combine the power difference of the radiofrequency hyperthermia device to obtain the heat concentration coefficient and transmit it to the temperature detection module; The temperature detection module measures the temperature distribution of the tissue in contact with the needle based on the fiber optic fluorescence sensor, calculates the fluorescence detection temperature value using the relationship between the fluorescence afterglow lifetime and the temperature, and then processes the average temperature in the contact electrode area to obtain the thermal response deviation factor, combines the heat concentration coefficient, and determines to issue a calibration prompt.

[0022] The specific implementation is as follows: In the signal acquisition and processing module, the original signal generated by the radiofrequency hyperthermia device during operation is acquired through an impedance-matching sampling circuit. The original signal is transmitted to the power measurement module and the frequency analysis module through a dual-channel output structure without any form of preprocessing or transformation, ensuring that each module receives exactly the same original signal.

[0023] It should be noted that the impedance-matching sampling circuit is a circuit structure used to achieve non-interfering sampling of high-frequency signals and ensure impedance matching of the signal transmission path; the dual-channel output structure is a structure that can output the same original input signal to two functional modules simultaneously without changing the physical characteristics of the original input signal.

[0024] In the power measurement module, the original signal transmitted by the signal acquisition and processing module is received and input into the low-pass filter inside the power measurement module. The low-pass filter adopts a first-order passive RC circuit structure, and the specific design satisfies the following formula: ; where is the cut-off frequency, is the resistance of the low-pass filter, is the capacitance of the low-pass filter.

[0025] If the signal frequency component in the original signal is lower than the cut-off frequency, the signal frequency component is retained; otherwise, the signal frequency component is filtered.

[0026] The low-pass filter only allows the signal frequency components with frequencies lower than the cut-off frequency to pass through, reduces the high-frequency noise interference components in the original signal, and smooths the spike shape, thereby removing the high-frequency signal frequency components in the original signal.

[0027] After the low-pass filter completes the filtering of the signal frequency components, the processed original signal is obtained, and current conversion and electric power calculation operations are performed on the processed original signal: The processed original signal is converted into a current signal linearly proportional to the corresponding original signal through a precision current sampling resistor, and an ammeter is used to detect the current signal to obtain the current value of the current signal.

[0028] The voltage value of the radiofrequency hyperthermia device is collected in real time through a voltmeter. The current value of the current signal and the voltage value of the radiofrequency hyperthermia device are input into a analog multiplier for electric power calculation. The analog multiplier performs a multiplication operation on the current value of the current signal and the voltage value of the radiofrequency hyperthermia device to obtain the output power of the radiofrequency hyperthermia device.

[0029] The output power of the radiofrequency hyperthermia device is transmitted to the frequency analysis module for subsequent power analysis and calculation of the heat concentration coefficient.

[0030] It should be noted that a low-pass filter is an analog signal processing circuit with frequency selectivity function; the structure of a first-order passive RC circuit is a first-order linear filtering circuit composed of a resistor element and a capacitor element according to a specific connection method; a precision current sampling resistor is a resistor device used to convert the passing voltage signal into a current signal according to Ohm's law; an analog multiplier is an analog computing circuit device with the function of multiplying two continuously changing analog signals, which will not be elaborated here.

[0031] In the frequency analysis module, after receiving the output power of the radiofrequency hyperthermia device, the ideal power of the radiofrequency hyperthermia device is collected simultaneously. Among them, the ideal power of the radiofrequency hyperthermia device is the power reference value determined according to the device design parameters, the set treatment power target, and the pre-calibrated performance model, usually corresponding to the expected power level output by the device under standard working conditions. Its acquisition logic is to combine the target power setting value input by the user and the real-time monitoring parameters, and use the preset prediction model to obtain the ideal power of the radiofrequency hyperthermia device. Specifically, the target power setting value input by the user is obtained through the device operation interface or the input module in the control system. The real-time monitoring parameters include but are not limited to the voltage, current, load impedance, temperature sensing data, etc. of the radiofrequency signal. The selection of specific monitoring parameters is determined by the experimenter according to actual application requirements and will not be elaborated here. It should be noted that the preset prediction model is established by the experimenter based on the historical operation data of the device, environmental parameters, and empirical rules set by the treatment plan. The specific model can be set as a linear regression model, a support vector machine model, a neural network model, or other machine learning models. The selection and call of the model are determined by the experimenter according to experimental requirements and data performance and will not be elaborated here. Calculate the absolute difference between the output power of the radiofrequency hyperthermia device and the ideal power of the radiofrequency hyperthermia device to obtain the power difference of the radiofrequency hyperthermia device. Furthermore, perform fast Fourier transform processing on the original signal to extract the frequency concentration index. The specific process is as follows: A1: Collect the original signal from the output end of the radiofrequency hyperthermia device. This signal is a high-frequency alternating current signal in the time domain, containing the main frequency components of the radiofrequency excitation and their harmonic components, denoted as: ; In the formula, is the signal amplitude, is the center frequency, is the phase, is the perturbation term varying with time, is the time variable, representing the instantaneous state of the signal, is the instantaneous voltage varying with time; A2: Perform fast Fourier transform processing on the original time signal to convert it into a frequency-domain signal and obtain the mapping relationship between frequency and amplitude: ; In the formula, is the abbreviation of fast Fourier transform; Derive the spectral image, including the main frequency component, harmonics, and background noise; A3: Normalize the spectrum to obtain the unit energy density spectrum; ; In the formula, represents the relative energy density at the center frequency , represents the infinitesimal increment of frequency change. Specifically, serves to indicate what to integrate in the integral. In the integral formula for frequency-domain energy density normalization, is an indispensable standard calculus symbol; A4: Identify the main frequency point, that is, the frequency point corresponding to the maximum value, and set the symmetric bandwidth range: ; In the formula, is the main frequency point, is the symmetric bandwidth range, is the frequency variable; A5: Calculate the frequency concentration index according to the distribution of spectral energy in the main frequency band, defined as the ratio of the energy in the main frequency band to the total energy: ; In the formula, the numerator represents the energy proportion in the frequency concentration interval, reflecting the degree of energy aggregation of the radio frequency signal near the main frequency. The denominator represents the energy in the total frequency range, is the frequency concentration index, , are the upper and lower limits of the analysis frequency range respectively; Specifically, the closer the value of the frequency concentration index is to 1, the more concentrated the energy is near the main frequency, indicating more focused heat output. The closer the frequency concentration index tends to 0, the more scattered the frequency distribution is, which may lead to heat diffusion or poor focusing; It should be noted that the original signal transmitted to the frequency analysis module retains the high-frequency components in the original signal to ensure the accuracy and integrity of frequency analysis. Specifically, a band-pass filter or a high-pass filter is used to retain and extract the high-frequency components. The filtering parameters are set according to the operating frequency range of the radiofrequency hyperthermia device, which will not be elaborated here; Normalize the power difference of the radiofrequency hyperthermia device and the frequency concentration index so that the power difference of the radiofrequency hyperthermia device and the frequency concentration index are kept under the same dimension; It should be noted that the methods of standardization include, but are not limited to, standard linear transformation based on interval scaling, Z-Score standardization method based on statistics, or normalization method based on non-linear mapping function. The application methods of standardization will not be elaborated here; Substitute the power difference of the radiofrequency hyperthermia device and the frequency concentration index after normalization into the inverse difference tangent mapping function to obtain the heat concentration coefficient. The specific formula is expressed as: ; In the formula, is the heat concentration coefficient, is the frequency concentration index after normalization, is the power difference of the radiofrequency hyperthermia device after normalization, , are the influence weights corresponding to the power difference of the radiofrequency hyperthermia device and the frequency concentration index after normalization respectively, The function itself has non-linear compression characteristics, which can enhance the discrimination sensitivity at the critical point. The outer layer realizes the normalization process; It should be noted that when the power difference of the radiofrequency hyperthermia device after normalization is larger and the frequency concentration index after normalization is smaller, the heat concentration coefficient is lower, indicating that the heat distribution of the radiofrequency hyperthermia device is dispersed; On the contrary, if the power difference of the radiofrequency hyperthermia device after normalization is smaller and the frequency concentration index after normalization is larger, the heat concentration coefficient is higher, indicating that the heat distribution of the radiofrequency hyperthermia device is concentrated.

[0032] In the temperature detection module, the temperature distribution of the tissue contact needle is measured based on an optical fiber fluorescence sensor, and the fluorescence detection temperature value is calculated using the relationship between the fluorescence afterglow lifetime and the temperature; The fluorescence detection temperature value is the instantaneous temperature value of the tissue contact needle area calculated based on the fluorescence afterglow lifetime measured by an optical fiber fluorescence sensor through the quantitative functional relationship between the fluorescence afterglow lifetime and temperature. Its acquisition logic is to emit an excitation light pulse to the tissue contact needle area to excite the fluorescent material to generate a fluorescence response, receive and record the afterglow decay process of the fluorescence signal to obtain the fluorescence afterglow lifetime, and use the functional relationship model between the fluorescence afterglow lifetime and temperature to obtain the fluorescence detection temperature value; It should be noted that the optical fiber fluorescence sensor is a type of high-sensitivity temperature detection device constructed based on the principle of coupling of fluorescent materials and optical fibers. It introduces an excitation light signal of a specific wavelength into the fluorescent material pre-placed in the contact area to trigger fluorescence emission and detects the change in its luminescence characteristics through the optical fiber. This sensor has the characteristics of fast response speed, strong anti-electromagnetic interference ability, and is suitable for working in a radio frequency electromagnetic field environment, especially suitable for non-contact temperature measurement of the tissue surface or contact point during radiofrequency hyperthermia; The fluorescence afterglow lifetime refers to the time required for the emission light intensity of the fluorescent material to decay from the initial peak to a preset proportion of the original intensity after the excitation light irradiation stops. The unit is microseconds or nanoseconds. This parameter reflects the average lifetime of the excited state of the fluorescent material and has the physical property of being highly sensitive to the ambient temperature; Furthermore, the preset proportion in which the emission light intensity decays from the initial peak to the preset proportion of the original intensity is determined by the experimenter based on the fluorescence decay characteristic parameters of the selected fluorescent material and the experimental data of temperature response stability, which will not be elaborated here; The functional relationship model between the fluorescence afterglow lifetime and temperature is usually an analytic function with monotonic change. Its form can be determined according to the temperature response characteristics of the selected fluorescent material. Commonly used models include but are not limited to the exponential decay model, linear model, or empirical fitting model, etc., which will not be elaborated here; Based on the average temperature of the contact electrode area, the observed temperature value is obtained; Among them, the contact electrode area is the area range set by the experimenter based on the equipment structure parameters and the actual action distribution characteristics of the radio frequency energy. The specific setting rules and the area change period are not limited, but are set by the experimenter according to the specific scenario, which will not be elaborated here; The observed temperature value refers to the average temperature parameter of the overall thermal effect of the area obtained by spatially sampling and processing the temperature distribution of the contact electrode area during radiofrequency hyperthermia. Its acquisition logic is based on an infrared temperature sensing array element to measure the temperature of the preset points in the contact electrode area to obtain a set of discrete temperature values, and according to the preset electrode area division scheme, the discrete temperature values are statistically analyzed and calculated based on weighted average to obtain the observed temperature value; Among them, the infrared temperature-sensing array element refers to a two-dimensional or multi-dimensional imaging detection component composed of multiple infrared-sensitive units, which has the ability of non-contact, high spatial resolution, and real-time response temperature perception. It can perform multi-point synchronous temperature measurement on the target area in an array manner and is suitable for radiofrequency hyperthermia application scenarios with strong electromagnetic interference or where it is not suitable to use electrical contact sensors; The preset points in the contact electrode area are determined by the experimenter based on the characteristics of the electrode geometric structure and the simulation analysis results of the energy conduction path. The spatial position of this point can correspond to the central axis, edge radiation area, or temperature rise sensitive area of the radiofrequency electrode, and the specific distribution is not limited; The preset electrode area division scheme is a spatial division rule set by the experimenter according to the electrode area size, shape structure, and expected area, and can be in the form of symmetric grid division, equal energy and isothermal distribution division, or non-uniform area division based on the thermal field simulation results, etc.; Furthermore, different weights are assigned to each preset point in the divided area during the weighted average calculation process. The weight value can be set based on the position of the point, the simulation results of the energy density, or the historical temperature measurement response curve. The spatial coordinates, quantity, and weight function form of the specific points are not limited and are independently configured by the experimenter according to the application requirements. Further, the weighted average algorithm is common knowledge of the experimenter and will not be elaborated here; Substitute the fluorescence detection temperature value and the observed temperature value into the dual-temperature fusion comparison strategy to obtain the thermal response deviation factor. The specific steps are as follows: Calculate the deviation amounts of the fluorescence detection temperature value and the observed temperature value from the target temperature range respectively. Among them, the target temperature range is the target temperature interval preset by the experimenter, and the specific interval size is not limited. The specific calculation process is as follows: ; In the formula, is the observed temperature value, is the fluorescence detection temperature value, is the central temperature of the target temperature range, is the maximum value of the preset target temperature range, is the minimum value of the preset target temperature range, is the observed temperature deviation factor, reflecting the deviation degree of the surface thermal response, is the fluorescence temperature deviation factor, reflecting the deviation degree of the thermal response at the contact interface or inside; Furthermore, the calculation formula for the central temperature of the standard temperature range is: ; In the formula, is the central temperature of the target temperature range; The observed temperature deviation factor and the fluorescence temperature deviation factor are introduced into the weight coefficient to fuse two types of temperature response information, and the thermal response deviation factor is obtained. The specific formula is as follows: ; where is the thermal response deviation factor, is the weight of the observed temperature, is the weight of the fluorescence detection temperature; Specifically, the weight coefficient is set by the experimenter according to the equipment response delay, the importance of the measurement position, and the actual clinical needs, which will not be elaborated here; The thermal response deviation factor is normalized so that the thermal response deviation factor and the heat concentration coefficient are kept under the same dimension; The thermal response deviation factor and the heat concentration coefficient are substituted into the product amplification difference adjustment model to obtain the thermal effect calibration coefficient. The specific formula is as follows: ; In the formula, is the thermal effect calibration coefficient, is the normalized thermal response deviation factor,[[ID=2�]] is the heat concentration coefficient, is the non-linear response adjustment parameter; It should be noted that when the thermal response deviation factor is larger and the heat concentration coefficient is smaller, the thermal effect calibration coefficient is smaller, and the current energy output process deviates from the target range and the heat accumulation effect is poor, and a calibration prompt needs to be issued. On the contrary, when the thermal response deviation factor is smaller and the heat concentration coefficient is larger, the thermal effect calibration coefficient is larger, and the current energy output process has an accurate response and good energy concentration, and the current power control state is maintained to operate stably without issuing a calibration prompt; The thermal effect calibration coefficient is compared with the preset calibration threshold. If the thermal effect calibration coefficient is greater than or equal to the preset calibration threshold, it means that the response accuracy and heat accumulation degree of the current energy output process both meet the expected standards, and a calibration prompt is issued. If the thermal effect calibration coefficient is less than the preset calibration threshold, it means that there is a response deviation or uneven heat distribution in the current energy output process, and no calibration prompt needs to be issued; It should be noted that the preset calibration threshold is obtained by the experimenter based on the safety tolerance range and the evaluation benchmark preset for typical application conditions, which will not be elaborated here; Optionally, the calibration prompt can set different calibration prompt rules according to the specific values of the heat concentration coefficient and the thermal response deviation factor. The specific examples are as follows: When the thermal effect calibration coefficient is greater than or equal to a preset calibration threshold, analyze the specific values of the heat concentration coefficient and the thermal response deviation factor. If the heat concentration coefficient is still in (e.g., about 0.7 to 0.85), but the thermal response deviation factor is slightly higher (e.g., 0.15 to 0.3), the system issues a prompt and enters the pending calibration mode; When the heat concentration coefficient is low (e.g., less than 0.7) and the thermal response deviation factor is significantly high (e.g., greater than 0.3), the system issues a significant calibration prompt to check the energy output consistency; If the heat concentration coefficient is below the preset critical value (e.g., below 0.5), regardless of the value range of the thermal response deviation factor, it is regarded as a potential heat accumulation abnormal state, and the system issues a high-priority calibration prompt and enters the safety protection process; It should be noted that the above rules are for illustrative purposes. The specific threshold setting and prompt level division can be flexibly configured by the experimenters according to the system performance parameters, custom scenario requirements, and feedback strategies, which will not be elaborated here.

[0033] The above embodiments can be implemented in whole or in part by software, hardware, firmware, or any other combination. When implemented using software, the above embodiments can be implemented in whole or in part in the form of a computer program product.

[0034] Those of ordinary skill in the art can realize that the modules and algorithm steps of each example described in combination with the embodiments disclosed in this article can be implemented by electronic hardware, or a combination of computer software and electronic hardware. Whether these functions are executed in hardware or software depends on the specific application and invention constraints of the technical solution. Professional technicians can use different methods to implement the described functions for each specific application, but this implementation should not be considered to exceed the scope of this application.

[0035] In addition, in each embodiment of this application, the functional modules can be integrated into one processing module, or each module can exist physically alone, or two or more modules can be integrated into one module.

[0036] The above is only the specific implementation manner of this application, but the protection scope of this application is not limited thereto. Any person skilled in the art can easily think of changes or substitutions within the technical scope disclosed in this application, and all should be covered by the protection scope of this application. Therefore, the protection scope of this application should be subject to the protection scope of the claims.

[0037] Finally: The above is only the preferred embodiment of the present invention and is not used to limit the present invention. Any modifications, equivalent substitutions, improvements, etc. made within the spirit and principle of the present invention should be included in the protection scope of the present invention.

Claims

1. Radiofrequency hyperthermia equipment testing system, characterized in that: It includes a signal acquisition and processing module, a power measurement module, a frequency analysis module, and a temperature detection module, and the electrical signals of each module are connected: The signal acquisition and processing module is used to receive the original signal from the radiofrequency hyperthermia device and distribute the original signal to the power measurement module and the frequency analysis module for processing; The power measurement module uses a low-pass filter to remove the high-frequency components in the original signal, converts the processed original signal into current and detects it through an ammeter, and calculates the output power of the radiofrequency hyperthermia device according to the detection result of the ammeter and the real-time voltage through a analog multiplier, and transmits it to the frequency analysis module; The frequency analysis module is used to receive the output power of the radiofrequency hyperthermia device for processing to obtain the power difference of the radiofrequency hyperthermia device, perform fast Fourier transform processing on the original signal, extract the frequency concentration index, and synthesize the power difference of the radiofrequency hyperthermia device to obtain the heat concentration coefficient and transmit it to the temperature detection module; The temperature detection module measures the temperature distribution of the tissue contact needle based on the fiber optic fluorescence sensor, calculates the fluorescence detection temperature value using the relationship between the fluorescence afterglow lifetime and the temperature, and then processes the average temperature in the contact electrode area to obtain the thermal response deviation factor, and synthesizes the heat concentration coefficient to determine and issue a calibration prompt.

2. The radiofrequency hyperthermia device test system according to claim 1, wherein: In the signal acquisition and processing module, the original signal generated during the operation of the radiofrequency hyperthermia device is collected; The cut-off frequency is calculated through the resistance and capacitance of the low-pass filter; The original signal is input into the low-pass filter to obtain the processed original signal: If the signal frequency component in the original signal is lower than the cut-off frequency, the signal frequency component is retained, otherwise, the signal frequency component is filtered; The processed original signal is converted into a current signal linearly proportional to the corresponding original signal, and the current value of the current signal is detected through an ammeter.

3. The radiofrequency hyperthermia device test system according to claim 2, wherein: In the power measurement module, the voltage value of the radiofrequency hyperthermia device is collected in real time; The product of the current value of the current signal and the voltage value of the radiofrequency hyperthermia device is used as the output power of the radiofrequency hyperthermia device.

4. The radiofrequency hyperthermia device test system according to claim 3, wherein: In the frequency analysis module, the target power set value input by the user is combined with the real-time monitoring parameters, and the ideal power of the radiofrequency hyperthermia device is obtained by using a preset prediction model; An absolute difference calculation is performed between the output power of the radiofrequency hyperthermia device and the ideal power of the radiofrequency hyperthermia device to obtain the power difference of the radiofrequency hyperthermia device.

5. The radiofrequency hyperthermia device test system according to claim 1, wherein: In the frequency analysis module, fast Fourier transform processing is performed on the original signal to extract the frequency concentration index, and the specific process is as follows: Receive the original signal from the signal acquisition and processing module, convert it into a frequency domain signal through fast Fourier transform, generate a normalized frequency spectrum diagram, and use the ratio of the main frequency band energy to the total energy in the normalized frequency spectrum diagram as the frequency concentration index; Normalize the power difference of the radiofrequency hyperthermia device and the frequency concentration index.

6. The RF hyperthermia device test system according to claim 5, wherein: In the frequency analysis module, the power difference of the RF hyperthermia device after normalization processing and the frequency concentration index are substituted into the inverse difference tangent mapping function to obtain the heat concentration coefficient. The specific formula is expressed as: ； In the formula, is the heat concentration coefficient, is the frequency concentration index after normalization, is the power difference of the radiofrequency hyperthermia device after normalization, , are the influence weights corresponding to the power difference and the frequency concentration index of the radiofrequency hyperthermia device after normalization respectively, means that the function itself has a non-linear compression characteristic, and the outer layer realizes the normalization process.

7. The RF hyperthermia device test system according to claim 1, wherein: In the temperature detection module, the temperature distribution of the tissue contact needle is measured based on the fiber optic fluorescence sensor, and the fluorescence detection temperature value is calculated using the relationship between the fluorescence afterglow lifetime and the temperature; By emitting an excitation light pulse to the tissue contact needle area, exciting the fluorescent material to generate a fluorescence response, receiving and recording the afterglow decay process of the fluorescence signal to obtain the fluorescence afterglow lifetime, and using the function relationship model between the fluorescence afterglow lifetime and the temperature to obtain the fluorescence detection temperature value; Based on the average temperature of the contact electrode area, the observed temperature value is obtained.

8. The RF hyperthermia device test system according to claim 7, wherein: In the temperature detection module, based on the infrared temperature sensing array element, the temperature of the preset points in the contact electrode area is measured to obtain a set of discrete temperature values, and according to the preset electrode area division scheme, the discrete temperature values are statistically analyzed and calculated based on weighted average to obtain the observed temperature value; Substitute the fluorescence detection temperature value and the observed temperature value into the dual-temperature fusion comparison strategy to obtain the thermal response deviation factor. The specific steps are as follows: Calculate the deviation amounts of the fluorescence detection temperature value and the observed temperature value from the target temperature range respectively to obtain the observed temperature deviation factor and the fluorescence temperature deviation factor, and introduce a weight coefficient to fuse the two types of temperature response information. The specific formula for the thermal response deviation factor is expressed as follows: ； Among them, is the thermal response deviation factor, is the observed temperature deviation factor, is the fluorescence temperature deviation factor, is the observed temperature weight, is the fluorescence detection temperature weight.

9. The RF hyperthermia device test system according to claim 8, wherein: In the temperature detection module, after normalizing the thermal response deviation factor, substitute the thermal response deviation factor and the heat concentration coefficient into the product amplification difference adjustment model to obtain the thermal effect calibration coefficient. The specific formula is expressed as follows: ； In the formula, is the thermal effect calibration coefficient, is the thermal response deviation factor after normalization, is the heat concentration coefficient, is the non-linear response adjustment parameter.

10. The RF hyperthermia device test system according to claim 9, wherein: In the temperature detection module, compare the thermal effect calibration coefficient with the preset calibration threshold. If the thermal effect calibration coefficient is greater than or equal to the preset calibration threshold, a calibration prompt is issued; If the thermal effect calibration coefficient is less than the preset calibration threshold, no calibration prompt is required.

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