Real-time treatment monitoring system and method based on double-frequency focused transducer

Abstract

The invention belongs to the technical field of medical equipment, and discloses a real-time treatment monitoring system and method based on a double-frequency focused transducer, and the system comprises an ultrasonic signal excitation module, a vibration signal monitoring module, a temperature monitoring module and a motion control device. The system provided by the invention is easy to build, can realize real-time monitoring of target tissue damage, and greatly improves the treatment efficiency while shortening the treatment time. The method comprises the following steps that S1, an ultrasonic signal excitation module generates an excitation signal and triggers local vibration in a target tissue; s2, a vibration signal monitoring module monitors a sound wave signal generated by vibration of the target tissue in real time; meanwhile, the temperature monitoring module monitors the temperature of the target tissue in the treatment process in real time. The monitoring method is easy to operate, monitoring is conducted in the treatment process at the same time, and the treatment duration is greatly shortened.

Description

Technical Field

[0001] The present invention relates to the technical field of medical equipment, and in particular to a real-time treatment monitoring system and method based on a dual-frequency focused transducer. Background Art

[0002] As a cutting-edge non-invasive medical method, high-intensity focused ultrasound (HIFU) technology has shown great potential and value in many fields such as tumor treatment, tissue ablation and cosmetic surgery in recent years. Its principle is mainly to accurately control the focus of the ultrasound beam to produce a high-intensity, high-energy ultrasound focus in vitro. The energy density of this focus area is sufficient to cause local rapid heating in the target tissue, thereby achieving the therapeutic effect of destroying the diseased tissue, promoting tissue remodeling or stimulating collagen regeneration. However, one of the potential risks associated with this treatment process is tissue damage, which is an important aspect that cannot be ignored in the application of HIFU technology.

[0003] In order to evaluate the degree and scope of tissue damage during HIFU treatment, the medical community has widely adopted a variety of imaging technologies as monitoring methods, among which magnetic resonance imaging (MRI) and ultrasound imaging are particularly prominent. MRI, with its excellent soft tissue resolution and three-dimensional imaging capabilities, can more accurately depict the structural changes of tissues after treatment, and is particularly effective in identifying larger areas of damage. Ultrasound imaging, with its real-time, low-cost and radiation-free advantages, plays an important role in the real-time monitoring of HIFU treatment, especially in guiding the treatment process and ensuring precise targeting.

[0004] Despite the many advantages of existing imaging technologies, there are still certain limitations in detecting HIFU-induced tissue damage, especially their inability to directly measure temperature changes during treatment, which is a key parameter for evaluating treatment efficacy and preventing excessive damage. During HIFU treatment, the temperature inside the tissue rises rapidly and reaches a level sufficient to cause protein denaturation and cell necrosis, and real-time monitoring of this temperature change process is crucial for optimizing treatment parameters and ensuring treatment safety. However, most of the currently available temperature monitoring methods focus on assessing tissue damage after the treatment. These methods not only lag behind the actual treatment, but also fail to provide immediate temperature feedback information.

[0005] Based on the problems existing in the prior art, the concept of ultrasound stimulated acoustic emission (USAE) has been proposed in the field of disease. The principle includes using a dual-frequency HIFU transducer to emit two beams of ultrasound with a small frequency difference, focusing on the target area. The interference of ultrasound in the confocal area generates a dynamic radiation force of frequency difference, causing the lesion tissue to vibrate and generate an acoustic signal, which is detected by an external low-frequency hydrophone. Since the signal is related to the mechanical and acoustic properties of the lesion tissue, it can be used for tissue-specific detection and imaging. Although the above scheme can be detected during the treatment process, the scheme mainly uses a single-frequency HIFU transducer during the treatment, and uses a dual-frequency transducer to intermittently detect the USAE signal for monitoring target tissue damage; and in existing studies, researchers mainly focus on the spectrum and amplitude changes of the USAE signal after HIFU treatment, which limits the real-time monitoring of target tissue damage. In addition, the HIFU transducer used in the above method has a small driving power, and it takes hundreds of seconds to form a single lesion, resulting in low treatment efficiency and long treatment time. Summary of the invention

[0006] The purpose of the present invention is to propose a real-time treatment monitoring method system based on a dual-frequency focused transducer, which is easy to build and can realize real-time monitoring of target tissue damage, thereby greatly improving treatment efficiency while shortening treatment time.

[0007] The technical solution adopted to achieve the purpose of the present invention is:

[0008] A real-time treatment monitoring method based on a dual-frequency focused transducer, comprising:

[0009] An ultrasonic signal excitation module, used to generate an excitation signal and induce local vibration in the target tissue;

[0010] A vibration signal monitoring module, used to monitor the acoustic wave signal generated by the vibration of the target tissue in real time;

[0011] A temperature monitoring module, used to monitor the temperature of the target tissue during treatment in real time;

[0012] Motion control device, used to control the position and movement trajectory of the target tissue.

[0013] Furthermore, a control device is also included, and the ultrasonic signal excitation module, the vibration signal monitoring module, the temperature monitoring module and the motion control device all establish remote communication with the control device.

[0014] Furthermore, the temperature monitoring module includes a temperature sensor and a data acquisition device. The temperature sensor is used to collect the temperature of the target tissue and transmit it to the data acquisition device; the data acquisition device is connected to the control device.

[0015] Furthermore, the ultrasonic signal excitation module includes a signal generator and an ultrasonic transducer, the signal generator is connected to the ultrasonic transducer respectively, and the signal generator establishes remote communication with the control device.

[0016] Furthermore, the vibration signal monitoring module includes a hydrophone, which is used to receive the frequency difference signal emitted by the vibration of the target tissue and transmit it to the control device.

[0017] Furthermore, the system also includes a first oscilloscope, the first oscilloscope establishes remote communication with the control device, and the signal generating device and the hydrophone are both connected to the first oscilloscope.

[0018] Furthermore, the motion control device includes a mechanical arm, and the mechanical arm is connected to the control device.

[0019] Furthermore, the motion control device also includes a second oscilloscope, which is connected to the robotic arm and establishes remote communication with the control device.

[0020] Another object of the present invention is to provide a real-time treatment monitoring method based on a dual-frequency focused transducer, which is easy to operate and can monitor simultaneously during the treatment process, greatly shortening the treatment time.

[0021] The technical solution adopted to achieve another purpose of the present invention is:

[0022] The real-time treatment monitoring method based on dual-frequency focused transducer specifically includes the following steps:

[0023] Step S1, the ultrasonic signal excitation module generates an excitation signal and induces local vibration in the target tissue;

[0024] Step S2, the vibration signal monitoring module monitors the acoustic wave signal generated by the vibration of the target tissue in real time; at the same time, the temperature monitoring module monitors the temperature of the target tissue during the treatment process in real time.

[0025] Further, in step S2, the sound wave signal monitored by the vibration signal monitoring module and the temperature monitored by the temperature monitoring module are both transmitted to the control device.

[0026] The beneficial effects of the present invention are as follows: the system of the present invention is easy to build, and the USAE technology is used to realize the monitoring of focal target tissue damage during dual-frequency HIFU enhanced treatment. The acoustic emission signal of the dual-frequency HIFU ultrasound is used to monitor the temperature rise of the target tissue in real time, which greatly improves the treatment efficiency while shortening the treatment time. In addition, the monitoring method of the present invention is easy to operate, and simultaneous monitoring during the treatment process greatly shortens the treatment time. BRIEF DESCRIPTION OF THE DRAWINGS

[0027] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the present invention will be further described below in conjunction with the accompanying drawings and embodiments. The drawings described below are only some embodiments of the present invention. For those of ordinary skill in the art, other drawings can be obtained based on these drawings without creative work:

[0028] Figure 1 It is a connection relationship schematic diagram of the system of the present invention.

[0029] Figure 2 A graph showing the variation of acoustic emission signal amplitude and temperature over time in a graphite phantom.

[0030] Figure 3 A graph showing the change in acoustic emission signal amplitude and temperature over time in isolated tissue. DETAILED DESCRIPTION

[0031] The examples are provided to better illustrate the present invention, but the present invention is not limited to the examples. Therefore, those skilled in the art may make non-essential improvements and adjustments to the implementation scheme according to the above invention content, which still fall within the protection scope of the present invention.

[0032] like Figure 1 As shown, a real-time treatment monitoring method based on a dual-frequency focused transducer comprises:

[0033] An ultrasonic signal excitation module, used to generate an excitation signal and induce local vibration in the target tissue;

[0034] A vibration signal monitoring module is used to monitor the acoustic wave signal generated by the vibration of the target tissue in real time and convert it into an image;

[0035] A temperature monitoring module, used to monitor the temperature of the target tissue during treatment in real time;

[0036] Motion control device, used to control the position and movement trajectory of the target tissue.

[0037] The invention also includes a control device, and the ultrasonic signal excitation module, the vibration signal monitoring module, the temperature monitoring module and the motion control device all establish remote communication with the control device. The control device is a PC commonly used in the prior art. In addition, the remote communication in the present invention is a common method in the prior art, and a wired or wireless method can be selected. The specific selection needs to be made according to the actual situation. The present invention preferably establishes remote communication by wired connection.

[0038] The ultrasonic signal excitation module in the present invention comprises a signal generator and an ultrasonic transducer. The signal generator is connected to the ultrasonic transducer respectively, and the signal generator establishes remote communication with the control device.

[0039] In the present invention, the ultrasonic transducer is a dual-frequency HIFU sector transducer, which is composed of eight sector-shaped piezoelectric ceramic array elements, with a central opening radius of 29 mm, an aperture radius of 86 mm, and a geometric focal length of 90 mm. The eight sector-shaped array elements are alternately divided into two groups, each with a frequency of f1=f2. c +Δf / 2 and f2=f c +Δf / 2 continuous electrical signal drive, so that it can generate target tissue vibration with a frequency of Δf / 2 = |f1-f2| in the focus of the target tissue. Specifically, the two groups of array elements of the present invention are driven by continuous electrical signals with frequencies of 1.065MHz and 1.085MHz respectively, and the frequency difference is 20kHz.

[0040] In the above frequency formula,

[0041] f1 represents one of the frequencies of the ultrasound wave acting on the target tissue;

[0042] f2 represents another frequency of ultrasound acting on the target tissue;

[0043] f c It represents the center frequency of the ultrasonic wave, that is, the propagation frequency of the ultrasonic wave in the medium when there is no influence of flow velocity;

[0044] Δf represents the difference between the two ultrasonic propagation frequencies, that is, the frequency difference.

[0045] The dual-frequency HIFU sector transducer in the present invention can generate two ultrasonic beams with a small frequency difference, which are focused on the target area, causing the temperature of the local target tissue to rise, generating a thermal effect, causing coagulative necrosis of the target tissue, thereby achieving the purpose of treatment.

[0046] In the present invention, the number of signal generators and ultrasonic transducers is two, and they correspond to the two output ends of the signal generator respectively. Among them, a power amplifier and an impedance matching box are arranged in sequence between the signal generator and the ultrasonic transducer. The power amplifier mainly amplifies the signal generated by the signal generator, increases the voltage or current amplitude of the signal, thereby increasing the power of the signal, thereby ensuring that the ultrasonic transducer has enough power to generate efficient ultrasonic waves. In addition, the power amplifier can also adjust the output impedance to match it with the input impedance of the ultrasonic transducer, maximize the energy transfer, reduce power loss, and improve the efficiency of the ultrasonic system. The main function of the impedance matching box is to ensure that the signal maintains integrity during transmission and avoid waveform distortion and amplitude changes. Through impedance matching, the ultrasonic transducer can obtain the maximum power output, thereby improving the overall efficiency of the ultrasonic system. At the same time, impedance matching can also reduce the reactive component in the circuit and reduce the energy loss of the system. Impedance matching can also play a role in protecting the equipment. When the impedance between the signal generator and the ultrasonic transducer is not matched, it may cause the generation of reflected waves, causing damage to the equipment. The impedance matching box can effectively absorb or reflect these reflected waves to protect the equipment from damage.

[0047] The signal generator model in the present invention is a function arbitrary waveform generator of DG4202 of RIGOL, which establishes remote communication with the control device, and the output parameters of the excitation signal can be set through the control device to adjust the working state of the transducer. The signal generator needs to control the synchronous emission signal of two channels and synchronously control the emission waveform. The imaging mode signal output waveform is a pulse wave, the trigger mode is external trigger, and the trigger signal comes from the data emission card (the data generation card is installed in the control device). The transducer output signal is adjusted by adjusting the pulse repetition period and pulse width of the waveform.

[0048] The working principle of the ultrasonic signal excitation module is as follows: the electrical signal generated by the signal generator is first amplified by the power amplifier, and then input into the driving circuit of the ultrasonic transducer through the impedance matching box. The driving circuit adjusts its output signal according to the frequency and amplitude of the input signal to drive the piezoelectric ceramic element in the vibration system. The piezoelectric ceramic element deforms under the action of the electrical signal and generates mechanical vibration. This mechanical vibration is transmitted through the transducer housing, matching layer or acoustic window and other structures to form ultrasonic waves.

[0049] In the present invention, the temperature monitoring module includes a temperature sensor and a data acquisition device. The temperature sensor is used to collect the temperature of the target tissue and transmit it to the data acquisition device; the data acquisition device is connected to the control device.

[0050] The temperature sensor is mainly used to collect the temperature of the target tissue location for treatment, and transmit the temperature to the data acquisition instrument, which is then sorted by the data acquisition instrument and transmitted to the control device. The data acquisition instrument is a common data acquisition instrument on the market that is compatible with thermocouple probes, such as Winterner WTN DAQ-T-1602 and Omega TC-08. The real-time temperature changes of the damaged area during HIFU treatment can be measured by the data acquisition instrument.

[0051] In the present invention, the vibration signal monitoring module includes a hydrophone, which is used to receive the frequency difference signal emitted by the vibration of the target tissue and transmit it to the control device. In actual operation, the interference of ultrasonic waves in the confocal area generates a dynamic radiation force of frequency difference, causing the target tissue of the lesion to vibrate and generate an acoustic signal. This acoustic signal is detected by the hydrophone, and the hydrophone transmits the captured model to the control device. The hydrophone in the present invention is a small spherical hydrophone of domestic model RHS-20, which establishes remote communication with the control device to receive the frequency difference signal emitted by the vibration of the target tissue. The characteristics of the above-mentioned hydrophone are: good directivity; wide frequency band range; flat sensitivity response; good stability and high reliability. The basic characteristics are as follows: operating frequency range: 10Hz~100kHz. Horizontal directivity: ±1.5dB (100kHz). Vertical directivity: ±2.0dB (100kHz, 240° range).

[0052] The system of the present invention also includes a first oscilloscope, the first oscilloscope establishes remote communication with the control device, and the signal generating device and the hydrophone are both connected to the first oscilloscope. The first oscilloscope is a PicoScope5000 series oscilloscope, which has four acquisition channels. The present invention only uses the acquisition channel A of the pico to temporarily store the target tissue vibration signal acquired by the hydrophone.

[0053] The first oscilloscope establishes remote communication with the control device to facilitate setting of signal acquisition parameters and acquisition modes. The first oscilloscope is connected to the hydrophone to observe the acoustic signal detected by the hydrophone in real time. After receiving the data collected by the hydrophone, the first oscilloscope temporarily stores the data and then transmits it to the control device. The control device further analyzes, processes or stores the data collected by the hydrophone to monitor the results. In actual operation, professional software is used in the control device to analyze, process or store the collected data for subsequent research or report generation.

[0054] In the present invention, the motion control device includes a mechanical arm connected to the control device; and also includes a second oscilloscope connected to the mechanical arm and establishing remote communication with the control device.

[0055] The motion control device is mainly responsible for accurately controlling the position and movement trajectory of the target tissue for treatment. Among them, the robotic arm is a domestically produced Elfin P05 robotic arm, and the oscilloscope is a PicoScope2000 series oscilloscope. In the present invention, the second oscilloscope establishes remote communication with the control device, transmits a voltage greater than 1.5V to the robotic arm, and drives the operation of the robotic arm. The robotic arm adopts an innovative dual-joint modular design, which gives it excellent flexibility while maintaining a high repeatability positioning accuracy of ±0.02 mm, ensuring that complex paths can be planned and navigated, ensuring accurate alignment and smooth movement of the transducer focus during treatment, thereby achieving uniform coverage of the treatment area and efficient energy transfer.

[0056] The main steps of the working process of the system of the present invention are as follows:

[0057] Step S1, trigger signal transmission and synchronization. The data transmission card of the control device sends a trigger signal and transmits it to the signal generator through the first oscilloscope synchronization signal. In this step, the trigger signal is used to start the entire system, and the first oscilloscope can be used to synchronize the output of the trigger signal.

[0058] Step S2, generation and amplification of electrical signals. After receiving the synchronization signal, the signal generator starts to generate electrical signals. These electrical signals, as the initial energy source for ultrasonic generation, are first sent to the power amplifier. The power amplifier amplifies these weak electrical signals to ensure that they have enough energy to drive the subsequent ultrasonic transducer.

[0059] Step S3, impedance matching and signal input. The amplified electrical signal then passes through an impedance matching box. The impedance matching box ensures that the electrical signal will not cause energy loss due to impedance mismatch when it is transmitted to the driving circuit of the ultrasonic transducer. After impedance matching is completed, the electrical signal is smoothly input into the driving circuit.

[0060] Step S4, adjustment and output of the driving circuit. After receiving the input signal, the driving circuit makes intelligent adjustments according to the frequency and amplitude of the signal. This ensures that the output signal can accurately match the working requirements of the piezoelectric ceramic element in the vibration system. The adjusted signal is used to drive the piezoelectric ceramic element.

[0061] Step S5, generation and propagation of ultrasonic waves. Under the action of the electrical signal, the piezoelectric ceramic element of the ultrasonic transducer is deformed, and this deformation is converted into mechanical vibration. These mechanical vibrations are efficiently transmitted through the transducer's housing, matching layer or acoustic window and other structures, and finally form ultrasonic waves in the air or medium. In this step, the ultrasonic transducer emits two beams of ultrasonic waves with a very small frequency difference, which are focused on the target area for treatment, and the interference of ultrasonic waves in the confocal area generates a dynamic radiation force of the frequency difference, causing the target tissue of the lesion to vibrate and generate an acoustic signal.

[0062] Step S6, monitoring of target tissue and environment. The hydrophone and thermocouple probe in the present invention perform real-time monitoring. The hydrophone detects the vibration information of the target tissue, and transmits the monitored frequency difference signal back to the first oscilloscope for temporary storage, and then transmits it to the control device for result monitoring. The thermocouple probe is responsible for collecting temperature information around the focus of the target tissue, and transmits this information to the data acquisition instrument for real-time monitoring.

[0063] During the treatment process of the present invention, the robotic arm drives the target tissue to move according to a preset program to ensure that the treatment area can be evenly covered, thereby ensuring the effectiveness and uniformity of the treatment.

[0064] Feasibility experiment

[0065] This experiment is mainly to verify the USAE signal amplitude monitoring and temperature monitoring in the graphite phantom and in vitro target tissue, so as to verify the effect of the system of the present invention and further explore the correlation between temperature and amplitude.

[0066] 1. USAE signal amplitude monitoring and temperature monitoring in graphite phantom

[0067] 1. Graphite replica production

[0068] Step 1: Prepare agar mimic. Use an electronic scale to weigh 8g of agar powder, use a measuring cylinder to measure 400ml of degassed water, put the degassed water and agar into a beaker, stir evenly with a glass rod, seal the beaker with plastic wrap and put it in a microwave oven, heat it to boiling on high heat, then switch to medium-high heat until the agar powder is completely dissolved. Take out the beaker, wait for the temperature of the agar solution to drop to about 40°C, and slowly pour the agar solution into the mold. Wait for it to cool and solidify to obtain the agar mimic.

[0069] Step 2: Prepare a graphite phantom. Add graphite powder to the agar phantom to make a graphite phantom. The specific process is as follows: Use an electronic scale to weigh 4g of graphite powder, cool the agar solution to about 70°C and add the graphite powder, use a magnetic stirrer to stir continuously, and when the temperature of the mixed solution drops to about 40°C, slowly pour it into the mold. Wait for it to cool and solidify to obtain a graphite phantom.

[0070] 2. Monitoring process

[0071] In order to explore the relationship between the amplitude change of ultrasonic acoustic emission (USAE) signal and temperature change, this experiment used ultrasound with an irradiation power of 3W and effective durations of 4s, 7.2s and 10s respectively. The specific results are as follows Figure 2 As shown. Figure 2 middle, Figure 2 (a) to Figure 2 The detailed description of the drawings in (d) is as follows:

[0072] Figure 2 (a) is the result of the change of acoustic emission signal amplitude and temperature over time when the action time is 4s;

[0073] Figure 2 (b) is the result of the change of acoustic emission signal amplitude and temperature over time when the action time is 7.4s;

[0074] Figure 2 (c) is the result of the change of acoustic emission signal amplitude and temperature over time when the action time is 10s;

[0075] Figure 2 (d) is the result diagram of the damaged area of ​​the graphite phantom when the action time is 4s, 7.2s and 10s respectively.

[0076] according to Figure 2 (a) to Figure 2 The results of (d) show that the present invention can monitor the amplitude and temperature of the acoustic emission signal of the graphite phantom in real time, and record the changes of the amplitude and temperature of the acoustic emission signal over time. This result illustrates the feasibility of the system of the present invention, that is, the temperature monitoring of the target tissue during the treatment process.

[0077] according to Figure 2 The results of (a) show that when the USAE signal does not have an inflection point, both the temperature and the USAE signal amplitude increase with time. The temperature rises from 24.5℃ to 27℃, indicating that there is a strong correspondence between temperature and amplitude.

[0078] according to Figure 2 (b) and Figure 2 From the results in (c), it can be seen that when the ultrasonic time is 6s, the acoustic emission signal shows an obvious downward trend, and as the ultrasonic time increases, the temperature stabilizes at around 27.5℃.

[0079] according to Figure 2 The results of (d) show that after the graphite is sliced ​​longitudinally, the solidification damage is obvious. After the inflection point, the damage area further expands with the increase of ultrasonic time.

[0080] 2. USAE signal amplitude monitoring and temperature monitoring in ex vivo tissues

[0081] The experiment used isolated bovine heart tissue irradiated at 60W for 4s, 7.4s and 10s. The specific results are as follows Figure 3 As shown. Figure 3 middle, Figure 3 (a) to Figure 3 The detailed description of the drawings in (d) is as follows:

[0082] Figure 3(a) is the result of the change of acoustic emission signal amplitude and temperature over time when the action time is 4s;

[0083] Figure 3 (b) is the result of the change of acoustic emission signal amplitude and temperature over time when the action time is 7.4s;

[0084] Figure 3 (c) is the result of the change of acoustic emission signal amplitude and temperature over time when the action time is 10s;

[0085] Figure 3 (d) is the result diagram of the in vitro tissue damage area when the action time is 4s, 7.2s and 10s respectively.

[0086] according to Figure 3 From the results in (a), it can be seen that when the ultrasonic acoustic emission (USAE) signal has no inflection point (under 4 s ultrasound), both the temperature and the USAE signal amplitude increase with time.

[0087] according to Figure 3 (b) and Figure 3 From the results in (c), it can be seen that after reaching the inflection point (ultrasonic treatment for 4 s), the temperature gradually stabilized, and the USAE signal amplitude gradually decreased with the duration of ultrasonic treatment of 7.4 s and 10 s.

[0088] according to Figure 3 The results in (d) show that coagulative necrosis was observed in bovine heart tissue sections, and the damaged area further expanded with the increase of ultrasound time, which is consistent with the results of the graphite model.

[0089] According to the above two experiments, the present invention uses USAE technology to monitor focal tissue damage during dual-frequency HIFU enhanced treatment. The acoustic emission signal of dual-frequency HIFU ultrasound is used to monitor the temperature rise of the tissue in real time. The present invention conducts experiments on graphite phantoms and ex vivo tissues respectively. The results show that it is feasible to combine the HIFU treatment system and the imaging system into one system, which can realize real-time monitoring of tissue damage during dual-frequency HIFU enhanced treatment, greatly improving work efficiency.

[0090] In addition, the present invention linearly fits and compares the temperature and amplitude at the same time, and finds that before coagulative necrosis occurs, there is a certain correlation between temperature and USAE amplitude changes. After necrosis occurs, the correlation between temperature and USAE amplitude changes. This may be because once thermal coagulation occurs, the elastic modulus of the tissue will gradually decrease, thereby reducing the amplitude of tissue vibration, that is, reducing the amplitude of the acoustic emission signal, proving that the temperature and USAE amplitude changes are very consistent. In the future, we can continue to decouple the factors that affect the amplitude changes of the USAE signal during dual-frequency HIFU treatment, aiming to quantify the relationship between these changes and tissue damage, so that the monitoring system can be seamlessly integrated with the HIFU treatment system, facilitating rapid clinical application.

[0091] Finally, it should be noted that the above embodiments are only used to illustrate the technical solution of the present invention rather than to limit it. Although the present invention has been described in detail with reference to the preferred embodiments, those skilled in the art should understand that the technical solution of the present invention can be modified or replaced by equivalents without departing from the purpose and scope of the technical solution of the present invention, which should be covered by the scope of the claims of the present invention.

Claims

1. A real-time treatment monitoring method based on a dual-frequency focused transducer, characterized in that: include: An ultrasonic signal excitation module, used to generate an excitation signal and induce local vibration in the target tissue; A vibration signal monitoring module, used to monitor the acoustic wave signal generated by the vibration of the target tissue in real time; A temperature monitoring module, used to monitor the temperature of the target tissue during treatment in real time; Motion control device, used to control the position and movement trajectory of the target tissue.

2. The real-time treatment monitoring method based on dual-frequency focused transducer according to claim 1, characterized in that: It also includes a control device, and the ultrasonic signal excitation module, the vibration signal monitoring module, the temperature monitoring module and the motion control device all establish remote communication with the control device.

3. The real-time treatment monitoring method based on dual-frequency focused transducer according to claim 2, characterized in that: The temperature monitoring module includes a temperature sensor and a data acquisition device. The temperature sensor is used to collect the temperature of the target tissue and transmit it to the data acquisition device; the data acquisition device is connected to the control device.

4. The real-time treatment monitoring method based on dual-frequency focused transducer according to claim 2 or 3, characterized in that: The ultrasonic signal excitation module includes a signal generator and an ultrasonic transducer. The signal generator is connected to the ultrasonic transducer respectively, and the signal generator establishes remote communication with the control device.

5. The real-time treatment monitoring method based on dual-frequency focused transducer according to claim 2 or 3, characterized in that: The vibration signal monitoring module includes a hydrophone, which is used to receive the frequency difference signal emitted by the vibration of the target tissue and transmit it to the control device.

6. The real-time treatment monitoring method based on dual-frequency focused transducer according to claim 5, characterized in that: The system also includes a first oscilloscope, which establishes remote communication with the control device, and the signal generating device and the hydrophone are both connected to the first oscilloscope.

7. The real-time treatment monitoring method based on dual-frequency focused transducer according to claim 2, 3 or 6, characterized in that: The motion control device comprises a mechanical arm, and the mechanical arm is connected to the control device.

8. The real-time treatment monitoring method based on dual-frequency focused transducer according to claim 2, 3 or 6, characterized in that: The motion control device also includes a second oscilloscope, which is connected to the mechanical arm and establishes remote communication with the control device.

9. A monitoring method for a real-time treatment monitoring system based on a dual-frequency focused transducer according to any one of claims 1 to 8, characterized in that: The specific steps include: Step S1, the ultrasonic signal excitation module generates an excitation signal and induces local vibration in the target tissue; Step S2, the vibration signal monitoring module monitors the acoustic wave signal generated by the vibration of the target tissue in real time; at the same time, the temperature monitoring module monitors the temperature of the target tissue during the treatment process in real time.

10. The real-time treatment monitoring method based on dual-frequency focused transducer according to claim 9, characterized in that: In step S2, the sound wave signal monitored by the vibration signal monitoring module and the temperature monitored by the temperature monitoring module are transmitted to the control device.

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