Spiral ultrasonic thrombolysis micro-probe, system, control method, equipment and medium

Abstract

According to the spiral ultrasonic thrombolysis micro-probe, the system, the control method, the equipment and the medium, the spiral ultrasonic thrombolysis micro-probe is precisely cut into a plurality of independent array elements, and the working time sequence and the phase of each array element are independently controlled by a circuit system, so that the synthesis of hurricane spiral ultrasonic fields in different modes is realized. According to the structure, while the processing complexity of the probe is remarkably reduced, drugs and microbubbles act on thrombus through a spiral sound field, and the cavitation effect and mechanical disturbance are effectively enhanced, so that the thrombolysis efficiency is greatly improved. According to the invention, two reliable phase control implementation paths are provided, a specific and feasible circuit implementation scheme is provided for realizing fine and stable phase adjustment, and the requirements of different application scenes are met. According to the invention, the phase of each array element is dynamically regulated and controlled through a circuit system, and the switching of a clockwise scanning mode and an anticlockwise scanning mode of a spiral sound field at different rates is realized.

Description

Technical Field

[0001] This invention relates to the field of medical ultrasound and interventional therapy technology, and in particular to a spiral ultrasound thrombolysis microprobe, system, control method, equipment, and medium. Background Technology

[0002] Thrombotic diseases such as stroke, deep vein thrombosis, and pulmonary embolism are characterized by high incidence, high disability rate, and high mortality rate in clinical practice. Current treatment methods mainly include thrombolysis, mechanical thrombectomy, and interventional surgery, but these generally suffer from problems such as long treatment courses, high risks, and limited applicability. Thrombolysis is limited by its short time window and uneven drug distribution; while mechanical thrombectomy and interventional surgery can directly remove thrombi, they are highly invasive and have long recovery periods.

[0003] In recent years, ultrasonic thrombolysis has become an important direction in thrombosis treatment due to its advantages of high controllability, minimal damage, and the ability to locally enhance drug efficacy. Its core mechanism utilizes the cavitation effect of ultrasound and the microfluidic and shearing forces generated by mechanical vibration to promote drug penetration and accelerate thrombus fragmentation. However, existing ultrasonic thrombolysis systems mostly use plane waves or fixed focused sound fields, resulting in low acoustic energy utilization and uneven energy concentration, leading to local heat accumulation and limited thrombolysis efficiency.

[0004] The cavitation thrombolysis method combining ultrasound with microbubbles and drugs has been proven by numerous studies to significantly improve the thrombus fragmentation rate and drug penetration (such as Chinese patent ZL201620241447.2 and Chinese patent application CN202410978706.9). However, most of these methods still rely on a fixed-direction sound field, making it difficult to achieve a uniform three-dimensional energy distribution.

[0005] Vortex ultrasound, as an emerging form of ultrasound beam, represents a cutting-edge direction in ultrasonic thrombolysis in recent years. Its core advantage lies in generating a tornado-like sound wave with a spiral wavefront, producing a rotational effect as the sound wave propagates. This unique wave pattern can generate intense shear stress in the fluid, resulting in higher thrombolysis efficiency compared to traditional plane wave ultrasound.

[0006] Existing publicly disclosed technologies for achieving helical ultrasound mainly fall into three categories: One approach utilizes the changing physical positions of different array elements in the probe transducer. For example, Chinese patent application CN202310340595.4 discloses a method that uses a 2×2 array of piezoelectric transducers with a λ / 4 height difference introduced in the thickness direction to create a fixed phase difference and synthesize an eddy current sound field. However, this method faces challenges such as high assembly difficulty, difficulty in controlling the top surface height difference, and the inability to change the fixed phase. Another approach, such as Chinese patent application CN202510405291.0, discloses a method that achieves multi-angle focused ultrasound emission through an array of coils around a blood vessel. This method relies on a larger-scale array or mechanical rotation to achieve a helical sound field, facing challenges related to the location of thrombi in blood vessels and size constraints. US patent application US16525648 and Korean patent application KR1020220086633 disclose schemes that generate helical sound waves through phase control devices, but these lack circuit implementation methods, complete control logic, and a fixed ultrasonic helical direction.

[0007] Therefore, there is a real need and great economic value in further designing and implementing a phase-controllable spiral ultrasound system for efficient thrombolysis. Summary of the Invention

[0008] In order to achieve the above-mentioned objectives and other advantages of the present invention, the first objective of the present invention is to provide a spiral ultrasonic thrombolysis microprobe, wherein the transducer in the ultrasonic thrombolysis microprobe adopts a coplanar array form, which includes multiple independent array elements, and the array elements are filled with insulating material and interconnected by electrodes. The ultrasonic thrombolysis microprobe is also equipped with a catheter and a miniature thermocouple temperature sensor. The catheter has a self-sealing valve at its end. The catheter is used to directly introduce thrombolytic drugs or microbubbles into the lesion and to dissipate heat at the front end of the transducer. The miniature thermocouple temperature sensor is used to monitor the transducer's operating temperature in real time and to provide feedback through the control circuit to achieve closed-loop temperature control.

[0009] Furthermore, the ultrasonic thrombolytic microprobe uses a circular planar piezoelectric ceramic wafer, which is divided into multiple independent array elements through laser cutting or micro-milling processes.

[0010] Furthermore, the number of array elements is 4 to 9.

[0011] Furthermore, the number of conduits is two, one used as an input channel and the other as an output channel; Alternatively, the number of catheters is one, which is used as the input channel. The output channel selects the original external support sheath as the return channel, and the gap at the front end is used as the return path, so that the overall probe forms a coaxial double-layer catheter structure.

[0012] Furthermore, the miniature thermocouple temperature sensor is placed between the metal electrode layer on the back of the probe and the ceramic layer of the transducer, or located at the slit of the transducer, so as to be close to the heating area.

[0013] Furthermore, the control circuit includes a differential amplifier, an RC low-pass filter, a cold junction compensation and ADC acquisition module. The temperature signal is differentially amplified by the differential amplifier, filtered by the RC low-pass filter, and then enters the cold junction compensation and ADC acquisition module to realize temperature reading. The system main controller performs dynamic power adjustment based on real-time temperature data: when the probe temperature exceeds a preset threshold, the ultrasonic output duty cycle is reduced. If the probe temperature exceeds the safety limit, immediately shut down the transmission channel and restart it after the temperature recovers.

[0014] The second objective of this invention is to provide a spiral ultrasonic circuit system for use with the aforementioned probe. This system employs an analog phase-shifting single-channel split architecture, which is based on a single-channel power amplifier and achieves a spiral sound field through a multi-branch phase-shifting circuit network in the subsequent stage. The phase-shifting circuit network adopts an adjustable second-order balanced structure based on transformer coupling and a two-stage RC network.

[0015] Furthermore, the transformer adopts a 1:2 turns ratio and grounds its center tap to generate positive and negative excitation signals with equal amplitude and opposite polarity, forming a differential output. This balanced topology, combined with the subsequent RC network, enables continuous phase shift adjustment of the output signal from -π to π at a fixed operating frequency.

[0016] The third objective of this invention is to provide a spiral ultrasonic circuit system for use with the aforementioned probe. This system employs a digital phased-array multi-channel architecture, which is composed of multiple phase-shifting circuit networks. Each transducer array element is equipped with an independent phase-shifting unit. The phase of each channel is synchronously configured by a controller to achieve a dynamically switchable forward and reverse spiral sound field. Alternatively, the architecture implements multi-channel direct digital frequency synthesis within the FPGA, generating independently adjustable phase waveform signals using a phase accumulator and waveform lookup table, which are then output to each power amplifier channel via a DAC.

[0017] Furthermore, phase modulation is achieved within the FPGA through four DDS channels, each controlled by an independent phase accumulator. Arbitrary offsets from 0° to 360° can be achieved by writing different phase control words. The FPGA internally uses lookup table logic to simultaneously drive multi-channel synchronous updates, realizing the generation of clockwise / counterclockwise rotating sound fields and dynamically variable speed rotating sound fields.

[0018] The fourth objective of this invention is to provide a control method for a helical ultrasonic circuit system, applied to the aforementioned system, comprising the following steps: After the system is powered on, it detects and determines the number of connected transducer array elements and loads parameters, including initial phase mapping, scanning direction, and single excitation duration. After initialization is complete, the system enters a waiting state, ready to receive external trigger signals. When a trigger signal is received, the system immediately starts ultrasonic excitation. During the activation process, if the system detects that the user has changed the parameters in real time, it will seamlessly switch to the new configuration in the next control cycle to achieve dynamic adjustment of the scanning mode. When the preset excitation time ends, the system stops outputting and jumps back to the trigger waiting state to prepare for the next treatment cycle.

[0019] Furthermore, by using different phase control methods, the helical sound field generated by the transducer array can possess multiple modes; wherein, the phase of array element n is defined as: , It can be a constant or a function of time; When rotated clockwise ; When rotated counterclockwise ; When in dynamic control It enables spiral scanning with angular velocity acceleration or deceleration.

[0020] A fifth objective of the present invention is to provide a computer device, including a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor executes the computer program to implement the steps of the above-described method.

[0021] A sixth objective of the present invention is to provide a computer-readable storage medium having a computer program stored thereon, wherein the computer program, when executed by a processor, implements the steps of the above-described method.

[0022] Compared with the prior art, the beneficial effects of the present invention are: This invention designs a spiral thrombolysis probe based on a flat piezoelectric ceramic probe chip. By precisely cutting the chip into multiple independent array elements and using a circuit system to independently control the operating timing and phase of each element, the synthesis of different modes of hurricane-like spiral ultrasonic fields is achieved. This structure significantly reduces the complexity of probe fabrication while delivering drugs and microbubbles to the thrombus through a spiral acoustic field, effectively enhancing cavitation and mechanical disturbance, thereby greatly improving thrombolysis efficiency.

[0023] The probe of this invention has a dedicated catheter at its center, which has a dual function: on the one hand, it can be used to accurately introduce thrombolytic drugs or microbubble contrast agents to the lesion area to enhance the thrombolytic effect; on the other hand, it can be used to circulate cooling liquid during the ultrasound emission stage to achieve efficient heat dissipation of the transducer front end and ensure the safety and stability of the system under long-term high-power operation.

[0024] This invention provides two reliable phase control implementation paths: the first is an analog phase shifting scheme based on a transformer-coupled adjustable RC network, which has the advantages of simple structure and low cost; the second is a digital phase control scheme based on FPGA and DDS, which can achieve nanosecond-level delay accuracy and flexible programmability. Both methods provide specific and feasible circuit implementation schemes for achieving fine and stable phase adjustment, adapting to the needs of different application scenarios.

[0025] This invention dynamically adjusts the phase of each array element through a circuit system to switch between clockwise and counterclockwise scanning modes of the helical sound field at different rates. This dynamic adjustment mechanism effectively avoids the problem of localized tissue heat accumulation caused by traditional single-direction scanning. At the same time, through the multi-directional and uniform sound field effect, it significantly improves the uniformity and thoroughness of thrombolysis, thereby achieving efficient thrombolysis and further enhancing treatment safety.

[0026] The above description is merely an overview of the technical solution of the present invention. In order to better understand the technical means of the present invention and to implement it according to the contents of the specification, the preferred embodiments of the present invention are described in detail below with reference to the accompanying drawings. Specific embodiments of the present invention are given in detail below with reference to the accompanying drawings. Attached Figure Description

[0027] The accompanying drawings, which are included to provide a further understanding of the invention and form part of this application, illustrate exemplary embodiments of the invention and, together with their description, serve to explain the invention and do not constitute an undue limitation thereof. In the drawings: Figure 1 This is a schematic diagram of a probe that has been cut into a combination of four piezoelectric components. Figure 2 A schematic diagram of a probe cut into an assembly of 8 piezoelectric components; Figure 3 This is a schematic diagram of phase shift; Figure 4 This is a diagram of a single-channel architecture. Figure 5 This is a schematic diagram of a phase-shifting circuit network; Figure 6 It is a type of multi-channel architecture; Figure 7 This is another type of multi-channel architecture; Figure 8 This is a schematic diagram of the DDS working principle; Figure 9 This is a schematic diagram illustrating the principle of controlling the forward and reverse rotation of a spiral ultrasonic field by adjusting the phase. Figure 10 The system control flow state machine flowchart; Figure 11 This is a schematic diagram showing a 0° phase shift of the excitation signal. Figure 12 A schematic diagram showing a 90° phase shift of the excitation signal; Figure 13 A schematic diagram showing a 180° phase shift of the excitation signal; Figure 14 A schematic diagram showing a 270° phase shift of the excitation signal; Figure 15 This is a block diagram of the temperature control circuit. Figure 16 This is a schematic diagram of a computer device. Figure 17 This is a schematic diagram of a computer-readable storage medium. Detailed Implementation

[0028] The present invention will now be further described with reference to the accompanying drawings and specific embodiments. Obviously, the described embodiments are only some, not all, of the embodiments of the present invention. It should be noted that, without conflict, the various embodiments or technical features described below can be arbitrarily combined to form new embodiments.

[0029] Based on the embodiments of this invention, all other embodiments obtained by those skilled in the art without inventive effort are within the scope of protection of this invention.

[0030] The drawing numbers in this application are only used to distinguish the steps in the scheme and are not used to limit the execution order of the steps. The specific execution order is as described in the specification.

[0031] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention pertains. The terminology used herein in the description of the invention is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention.

[0032] To overcome the shortcomings of existing technologies, this invention provides an ultrasonic microprobe, circuit system, and control method based on multi-element transducer and phase control technology, which achieves efficient and safe thrombolysis treatment through an adjustable spiral sound field.

[0033] Example 1 A spiral ultrasonic thrombolysis microprobe, wherein the transducer of the ultrasonic thrombolysis microprobe adopts a coplanar array form, which contains multiple independent array elements, and the array elements are filled with insulating material and interconnected by electrodes. The ultrasonic thrombolysis microprobe is also equipped with a catheter and a miniature thermocouple temperature sensor. The catheter has a self-sealing valve at its end. The catheter is used to directly introduce thrombolytic drugs or microbubbles into the lesion and to dissipate heat at the front end of the transducer. The miniature thermocouple temperature sensor is used to monitor the transducer's operating temperature in real time and to provide feedback through the control circuit to achieve closed-loop temperature control.

[0034] To achieve the helical ultrasonic function, this invention features an innovative structural design based on the existing flat wafer. The ultrasonic thrombolytic microprobe utilizes a circular planar piezoelectric ceramic wafer (such as PZT-5H), divided into multiple independent array elements using laser cutting or micro-milling processes. Furthermore, the number of array elements is 4 to 9. Figure 1 , Figure 2 As shown, 4-element and 9-element arrays are preferred. In the 9-element array probe, the middle element can be removed and a central conduit channel can be established. The elements are filled with insulating resin and interconnected using a flexible PI substrate to ensure electrical isolation between the elements and probe flexibility.

[0035] The internal catheter design of the probe serves two main purposes: first, it allows for the direct delivery of thrombolytic drugs or microbubbles to the lesion; second, it facilitates heat dissipation at the transducer tip. The placement of the catheters differs between 4-element and 9-element probes. In a 4-element probe, two catheters can be placed, one as the input channel and the other as the output channel. The leading edges of both the input and output channels can be divided into two smaller catheters that exit through a gap. In a 9-element probe, only one catheter can be placed for the input channel, while the original external support sheath serves as the return channel, with the gap at the front end acting as the return path. This results in a coaxial, double-layered catheter structure for the overall probe.

[0036] The inlet catheter can be used for the precise delivery of thrombolytic drugs or microbubble contrast agents, and can also be reused as an inlet path for circulating cooling liquid (preferably physiological saline or deionized water). The catheter's front end is equipped with a self-sealing silicone rubber valve, which has pressure-triggered opening and automatic closing functions. It can open during the drug delivery phase and form a closed cooling loop during the ultrasonic emission phase, achieving a synergistic reuse function of drug delivery and transducer heat dissipation. Specifically, during the drug delivery phase, the rear valve of the outlet catheter is closed, and the internal flow pressure of the inlet catheter is increased to open the self-sealing silicone rubber valve, allowing the drug to flow out from the front valve. During the ultrasonic emission phase, the outer valve of the outlet catheter is opened, forming a complete loop, and the internal pressure of the catheter is reduced, causing the valve to automatically close, achieving the function of internal cooling liquid flow for heat dissipation.

[0037] In addition, the 9-element catheter probe also offers another drug delivery method: a hollow instrument is inserted through the central catheter channel and directly exits through the front silicone valve to complete drug delivery (puncture method). After drug delivery, the hollow instrument is withdrawn, the front silicone valve automatically closes, and a subsequent cooling and heat dissipation process can begin.

[0038] In the spiral ultrasonic catheter of this invention, the transducer operates in a high-power pulse state (tens of volts to hundreds of volts), and temperature rise may lead to acoustic field drift, PZT depolarization, and the risk of tissue thermal damage. Therefore, a circuit system is needed to monitor probe end temperature changes, automatically limit power when overheating, and stop operation. A miniature thermocouple temperature sensor (such as an ultra-fine T-shaped solder joint test probe with a lead diameter of 0.05 mm and a spherical temperature measuring point with a diameter of 0.15 mm; or a thin sheet type with a thickness of 0.02 mm) is embedded inside the probe and placed between the metal electrode layer on the back of the probe and the ceramic layer of the transducer (solder joint type), or located at the transducer slit (thin sheet type), close to the heating area to minimize thermal resistance, and encapsulated and fixed with epoxy resin. The transducer operating temperature is monitored in real time and feedback is provided via the control circuit. When the temperature exceeds a set threshold, the system will automatically reduce the excitation power or temporarily shut down the transmission to ensure safe and stable operation. This composite structure can simultaneously address drug delivery, heat dissipation, and acoustic field control in a minimally invasive environment, significantly improving the long-term reliability and safety of the system.

[0039] The temperature circuit design block diagram is as follows: Figure 15 As shown, the control circuit includes a differential amplifier, an RC low-pass filter, a cold junction compensation and ADC acquisition module. The temperature signal is differentially amplified by the differential amplifier, filtered by the RC low-pass filter, and then enters the cold junction compensation and ADC acquisition module to achieve temperature reading. Specifically, the amplifier uses an AD8628 followed by an RC low-pass filter (R1=100Ω, C1=0.1µF), and the gain is adjusted by setting the amplifier feedback resistor. The cold junction compensation and ADC acquisition module uses a thermocouple / RTD digital converter chip MAX31865 to acquire temperature data. The chip and the FPGA (Xilinx Zynq-7035) main control core are connected via the SPI protocol.

[0040] The system controller performs dynamic power adjustment based on real-time temperature data: when the probe temperature exceeds a preset threshold (such as 45℃), the ultrasonic output duty cycle is reduced; When the probe temperature exceeds the safety limit (e.g., 50 °C), immediately shut down the transmission channel and restart it after the temperature recovers.

[0041] This circuit enables closed-loop temperature control of the catheter ultrasound system, providing a reliable guarantee for the long-term stable operation of the high-power microprobe.

[0042] Example 2 A spiral ultrasonic circuit system is applied to the probe described above. For a detailed description of the probe, please refer to the corresponding description in the probe embodiment described above, which will not be repeated here.

[0043] To achieve precise phase control and efficient power drive for multi-element transducers, this invention designs two complementary circuit system architectures: an analog phase-shifting single-channel splitter architecture and a digital phase-controlled multi-channel architecture.

[0044] The analog phase-shifting single-channel splitter architecture is simple in structure and suitable for generating helical sound fields at medium power and fixed frequencies. The design concept is based on a single-channel power amplifier, using a four-channel (or multi-channel) branched phase-shifting circuit network in the subsequent stage to achieve the helical sound field, such as... Figure 4 As shown. The key phase-shifting circuit network employs an adjustable second-order balanced structure based on transformer coupling and a two-stage RC network, as illustrated below. Figure 5 As shown. The transformer uses a 1:2 turns ratio and grounds its center tap (output common terminal) to generate positive and negative excitation signals of equal amplitude but opposite polarity, forming a differential output. This balanced topology, combined with the subsequent RC network, enables continuous phase shift adjustment of the output signal from -π to π (i.e., -180° to +180°) at a fixed operating frequency, such as... Figure 3 As shown in the diagram, this circuit achieves phase control by adjusting the resistance (R), featuring a simple structure and easy adjustment. A digital potentiometer is preferred for the adjustable resistor due to its digital interface, high precision, and ease of integration; a light-controlled resistor is the second choice, with voltage-controlled or magnetically controlled resistors as alternatives. A digital variable capacitor or varactor diode can be used as the adjustable capacitor to achieve more flexible phase-capacitance matching in conjunction with the resistor. While this architecture offers advantages in terms of low integration difficulty and low cost, significant considerations must be given to system heat dissipation and the voltage, current, and power capacity of components in high-power applications, as achieving high-voltage, high-power phase shifting presents certain challenges.

[0045] The digital phase-controlled multi-channel architecture is suitable for high-power, multi-mode dynamic control scenarios, offering greater flexibility and accuracy. This architecture further includes two implementation paths: Multi-channel independent phase-shifting circuit: composed of multiple aforementioned phase-shifting circuit networks, such as... Figure 6 As shown, each transducer array element is equipped with an independent phase-shifting unit, and the phase of each channel is configured synchronously by the controller to achieve a dynamically switchable forward and reverse spiral sound field.

[0046] FPGA-integrated multi-channel DDS solution: Implementing multi-channel direct digital frequency synthesis (DDS) within the FPGA, such as... Figure 7As shown, a waveform signal with independently adjustable phase is generated using a phase accumulator and waveform lookup table, and then output to each power amplifier channel via a DAC. This method offers high phase control accuracy, fast response speed, and supports complex waveforms and dynamic scanning strategies. The FPGA main control unit uses a Xilinx Zynq-7035, and the high-speed DAC output uses an ADI AD9767. The phase control principle is implemented internally within the FPGA primarily through four DDS channels. Figure 8 As shown, each DDS channel is controlled by an independent phase accumulator, and arbitrary offsets from 0° to 360° are achieved by writing different phase control words. Phase resolution. (n is the number of bits in the accumulator, usually 32), corresponding to a minimum resolution of <0.001°. The FPGA internally drives multiple channels to update synchronously through lookup table logic, which can realize the functions of generating clockwise / counterclockwise rotating sound fields and dynamically variable speed rotating sound fields.

[0047] The second type of architecture can effectively support high-precision phase shifting under high-power conditions and has superior performance, but the system integration complexity is higher and the cost is correspondingly increased.

[0048] The two architectures can complement each other depending on the application scenario. The former is suitable for compact, low-cost thrombolysis catheter systems, while the latter is suitable for high-precision research-oriented thrombolysis devices.

[0049] Example 3 A control method for a helical ultrasonic circuit system is provided, applied to the aforementioned system. A detailed description of the system can be found in the corresponding description in the system embodiments described above, and will not be repeated here. The system control flow is managed by a state machine, such as... Figure 10 As shown, the method includes the following steps: Initialization state: After the system is powered on, it automatically detects and determines the number of connected transducer array elements and loads parameters, including initial phase mapping, scanning direction (forward / reverse), and single excitation duration. Parameter configuration and trigger wait: After initialization, the system enters a waiting state, ready to receive external trigger signals. When a trigger signal is received, the system immediately starts ultrasonic excitation. During the excitation process, if the system detects that the user has changed the scanning direction or other key parameters in real time, it will seamlessly switch to the new configuration in the next control cycle to achieve dynamic adjustment of the scanning mode. State Reset: When the preset excitation time ends, the system automatically stops outputting and jumps back to the trigger waiting state to prepare for the next treatment cycle.

[0050] This invention enables the helical sound field generated by the transducer array to possess multiple modes through different phase control methods, such as fixed helical mode (maintaining a constant phase difference), forward and reverse rotation mode (fixed-period forward and reverse switching), dynamic acceleration and deceleration rotation control, and multi-frequency helical mode (superimposed with the main frequency). With harmonics (wave), etc.

[0051] The phase modulation algorithm is set as follows: Define the phase of array element n as: , It can be a constant or a function of time; When rotated clockwise ; When rotated counterclockwise ; When in dynamic control It enables spiral scanning with angular velocity acceleration or deceleration.

[0052] Taking a 4-element probe as an example, the control logic of the overall circuit in forward and reverse modes is explained.

[0053] Figure 9 To precisely control the phase changes through electronic control circuitry, the helical sound field generated by the transducer array can be dynamically adjusted by switching between clockwise and counterclockwise helical scans. Each array element is applied with a sequentially increasing fixed phase delay to synthesize a sound field rotating in a clockwise direction. The specific configuration is: Element 1: 0° phase delay, Element 2: 90° phase delay, Element 3: 180° phase delay, Element 4: 270° phase delay. Counterclockwise helical scan: By reversing the above phase delay sequence, the instantaneous switching of the sound field rotation direction is achieved. The specific configuration is: Element 1: 270° phase delay, Element 2: 180° phase delay, Element 3: 90° phase delay, Element 4: 0° phase delay.

[0054] In a single-channel circuit framework, the method of controlling phase using phase modulation circuitry is as follows: by applying different phase configurations (different resistance value sequences) to four phase-shifting circuit networks, clockwise and counterclockwise rotating helical sound fields can be synthesized. Each phase-shifting circuit network is configured with an adjustable resistor, such as a digital potentiometer. The controller independently sets the resistance value of each potentiometer via a digital bus (such as SPI), achieving high-resolution, drift-free, precise control that is easy to integrate. A clockwise helical sound field is set as follows: Figures 11-14Channel 1 (Element 1): Control resistors maintain a phase shift of 0°; Channel 2 (Element 2): Control resistors maintain a phase shift of 90°; Channel 3 (Element 3): Control resistors maintain a phase shift of 180°; Channel 4 (Element 4): Control resistors maintain a phase shift of 270°. When a change in scanning direction is needed, the controller simply sends a reversed set of phase configuration parameters to the four phase-shifting circuits to switch the sound field rotation direction.

[0055] The method for controlling the phase of a multi-channel power amplifier using DDS is as follows: The FPGA directly sets the initial phase by writing different phase control words to each DDS channel. The relationship between the phase control word and the phase angle is: Phase offset = (phase control word / 2^N) × 360°, where N is the number of bits in the phase accumulator (usually 28-32 bits). The phase control words for the DDS to control the clockwise spiral sound field are as follows: DDS channel 1 (element 1): Phase control word set to 0 (corresponding to 0° delay). DDS channel 2 (element 2): Phase control word set to 2^(N-2) (corresponding to 90° delay). DDS channel 3 (element 3): Phase control word set to 2^(N-1) (corresponding to 180° delay). DDS channel 4 (element 4): Phase control word set to 3*2^(N-2) (corresponding to 270° delay). Simply reversing the order of the above phase control words will switch the direction of sound field rotation. By dynamically updating the rate of the phase control word using an FPGA, the angular velocity of the sound field rotation can be changed. For example, by implementing linear phase modulation scanning, spiral sound fields with different velocities can be synthesized.

[0056] Example 4 A computer device 100, such as Figure 16 As shown, the system includes a memory 110, a processor 120, and a computer program 130 stored in the memory and executable on the processor. When the processor executes the computer program, it implements the steps of a control method for a spiral ultrasonic circuit system. For a detailed description of the method, please refer to the corresponding description in the above method embodiments; it will not be repeated here.

[0057] Example 5 A computer-readable storage medium, such as Figure 17 As shown, a computer program is stored thereon, which, when executed by a processor, implements the steps of a control method for a helical ultrasonic circuit system. For a detailed description of the method, please refer to the corresponding description in the above method embodiments, and will not be repeated here.

[0058] The number of devices and processing scale described herein are for the purpose of simplifying the description of the invention. Applications, modifications, and variations of the invention will be readily apparent to those skilled in the art.

[0059] Although embodiments of the present invention have been disclosed above, they are not limited to the applications listed in the specification and embodiments. They can be applied to various fields suitable for the present invention. For those skilled in the art, other modifications can be easily made. Therefore, without departing from the general concept defined by the claims and their equivalents, the present invention is not limited to the specific details and illustrations shown and described herein.

[0060] The apparatus, computer device, and non-volatile computer storage medium and method provided in the embodiments of this specification are corresponding. Therefore, the apparatus, computer device, and non-volatile computer storage medium also have similar beneficial technical effects as the corresponding method. Since the beneficial technical effects of the method have been described in detail above, the beneficial technical effects of the corresponding apparatus, computer device, and non-volatile computer storage medium will not be repeated here.

[0061] Those skilled in the art will also know that, besides implementing the controller in the form of purely computer-readable program code, the same functions can be achieved by logically programming the method steps, making the controller take the form of logic gates, switches, application-specific integrated circuits (ASICs), programmable logic controllers (PLCs), and embedded microcontrollers. Therefore, such a controller can be considered a hardware component, and the devices included within it for implementing various functions can also be considered structures within that hardware component. Alternatively, the devices for implementing various functions can be considered as both software units implementing the method and structures within a hardware component.

[0062] The systems, apparatuses, or units described in the above embodiments can be implemented by computer chips or physical entities, or by products with certain functions. For ease of description, the above apparatuses are described separately as various units based on their functions. Of course, when implementing one or more embodiments of this specification, the functions of each unit can be implemented in one or more software and / or hardware.

[0063] Those skilled in the art will understand that the embodiments of this specification can be provided as methods, systems, or computer program products. Therefore, the embodiments of this specification can take the form of a completely hardware embodiment, a completely software embodiment, or an embodiment combining software and hardware aspects. Furthermore, the embodiments of this specification can take the form of a computer program product implemented on one or more computer-usable storage media (including, but not limited to, disk storage, CD-ROM, optical storage, etc.) containing computer-usable program code.

[0064] This specification is described with reference to flowchart illustrations and / or block diagrams of methods, apparatus (systems), and computer program products according to embodiments of this specification. It will be understood that each block of the flowchart illustrations and / or block diagrams, and combinations of blocks in the flowchart illustrations and / or block diagrams, can be implemented by computer program instructions. These computer program instructions can be provided to a processor of a general-purpose computer, special-purpose computer, embedded processor, or other programmable data processing apparatus to produce a machine, such that the instructions, which execute via the processor of the computer or other programmable data processing apparatus, generate instructions for implementing the flowchart illustrations and / or block diagrams. Figure 1 One or more processes and / or boxes Figure 1 A device that provides the functions specified in one or more boxes.

[0065] These computer program instructions may also be stored in a computer-readable storage medium that can direct a computer or other programmable data processing device to function in a particular manner, such that the instructions stored in the computer-readable storage medium produce an article of manufacture including instruction means, which are implemented in a process Figure 1 One or more processes and / or boxes Figure 1 The function specified in one or more boxes.

[0066] These computer program instructions may also be loaded onto a computer or other programmable data processing equipment to cause a series of operational steps to be performed on the computer or other programmable equipment to produce a computer-implemented process, thereby providing instructions that execute on the computer or other programmable equipment for implementing the process. Figure 1 One or more processes and / or boxes Figure 1 The steps of the function specified in one or more boxes.

[0067] It should also be noted that the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, method, article, or apparatus. Without further limitation, an element defined by the phrase "comprising one..." does not exclude the presence of other identical elements in the process, method, article, or apparatus that includes said element.

[0068] This specification may be described in the general context of computer-executable instructions, such as program units, that are executed by a computer. Generally, program units include routines, programs, objects, components, data structures, etc., that perform a specific task or implement a specific abstract data type. This specification may also be practiced in distributed computing environments, where tasks are performed by remote processing devices connected via a communication network. In distributed computing environments, program units may reside in local and remote computer storage media, including storage devices.

[0069] The various embodiments in this specification are described in a progressive manner. Similar or identical parts between embodiments can be referred to mutually. Each embodiment focuses on describing the differences from other embodiments. In particular, the system embodiments are basically similar to the method embodiments, so the description is relatively simple; relevant parts can be referred to the descriptions in the method embodiments.

[0070] The above description is merely an embodiment of this specification and is not intended to limit the scope of one or more embodiments of this specification. Various modifications and variations can be made to one or more embodiments of this specification by those skilled in the art. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principle of one or more embodiments of this specification should be included within the scope of the claims of one or more embodiments of this specification.

Claims

1. A spiral ultrasonic thrombolysis microprobe, characterized in that: The transducer in the ultrasonic thrombolysis microprobe adopts a coplanar array form, which contains multiple independent array elements. The array elements are filled with insulating material and interconnected by electrodes. The ultrasonic thrombolysis microprobe is also equipped with a catheter and a miniature thermocouple temperature sensor. The catheter has a self-sealing valve at its end. The catheter is used to directly introduce thrombolytic drugs or microbubbles into the lesion and to dissipate heat at the front end of the transducer. The miniature thermocouple temperature sensor is used to monitor the transducer's operating temperature in real time and to provide feedback through the control circuit to achieve closed-loop temperature control.

2. The spiral ultrasonic thrombolysis microprobe as described in claim 1, characterized in that: The ultrasonic thrombolytic microprobe uses a circular planar piezoelectric ceramic wafer, which is divided into multiple independent array elements by laser cutting or micro-milling.

3. The spiral ultrasonic thrombolysis microprobe as described in claim 1, characterized in that: The number of array elements is 4 to 9.

4. The spiral ultrasonic thrombolysis microprobe as described in claim 3, characterized in that: The number of conduits is two, one used as an input channel and the other as an output channel; Alternatively, the number of catheters is one, which is used as the input channel. The output channel selects the original external support sheath as the return channel, and the gap at the front end is used as the return path, so that the overall probe forms a coaxial double-layer catheter structure.

5. The spiral ultrasonic thrombolysis microprobe as described in claim 1, characterized in that: The miniature thermocouple temperature sensor is placed between the metal electrode layer on the back of the probe and the ceramic layer of the transducer, or located at the cut of the transducer, close to the heating area.

6. The spiral ultrasonic thrombolysis microprobe as described in claim 1, characterized in that: The control circuit includes a differential amplifier, an RC low-pass filter, a cold junction compensation and ADC acquisition module. The temperature signal is differentially amplified by the differential amplifier, filtered by the RC low-pass filter, and then enters the cold junction compensation and ADC acquisition module to realize temperature reading. The system main controller performs dynamic power adjustment based on real-time temperature data: when the probe temperature exceeds the preset threshold, the ultrasonic output duty cycle is reduced. If the probe temperature exceeds the safety limit, immediately shut down the transmission channel and restart it after the temperature recovers.

7. A spiral ultrasonic circuit system, applied to the probe as described in any one of claims 1 to 6, characterized in that: The system adopts an analog phase-shifting single-channel split architecture, which is based on a single-channel power amplifier and achieves a spiral sound field through a multi-branch phase-shifting circuit network in the subsequent stage. The phase-shifting circuit network adopts an adjustable second-order balanced structure based on transformer coupling and a two-stage RC network.

8. A spiral ultrasonic circuit system as described in claim 7, characterized in that: The transformer uses a 1:2 turns ratio and grounds its center tap to generate positive and negative excitation signals with equal amplitude and opposite polarity, forming a differential output. This balanced topology, combined with the subsequent RC network, enables continuous phase shift adjustment of the output signal from -π to π at a fixed operating frequency.

9. A spiral ultrasonic circuit system, applied to the probe as described in any one of claims 1 to 6, characterized in that: It adopts a digital phase-controlled multi-channel architecture, which is composed of multiple phase-shifting circuit networks. Each transducer array element is equipped with an independent phase-shifting unit. The phase of each channel is configured synchronously by the controller to realize a dynamically switchable positive and negative spiral sound field. Alternatively, the architecture implements multi-channel direct digital frequency synthesis within the FPGA, generating independently adjustable phase waveform signals using a phase accumulator and waveform lookup table, which are then output to each power amplifier channel via a DAC.

10. A spiral ultrasonic circuit system as described in claim 9, characterized in that: Phase modulation is achieved within the FPGA through four DDS channels. Each DDS channel is controlled by an independent phase accumulator, and arbitrary offsets from 0° to 360° can be achieved by writing different phase control words. The FPGA internally uses lookup table logic to simultaneously drive multi-channel synchronous updates, realizing the generation of clockwise / counterclockwise rotating sound fields and dynamically variable speed rotating sound fields.

11. A control method for a spiral ultrasonic circuit system, applied to the system as described in claim 7 or 9, characterized in that, Includes the following steps: After the system is powered on, it detects and determines the number of connected transducer array elements and loads parameters, including initial phase mapping, scanning direction, and single excitation duration. After initialization is complete, the system enters a waiting state, ready to receive external trigger signals. When a trigger signal is received, the system immediately starts ultrasonic excitation. During the activation process, if the system detects that the user has changed the parameters in real time, it will seamlessly switch to the new configuration in the next control cycle to achieve dynamic adjustment of the scanning mode. When the preset excitation time ends, the system stops outputting and jumps back to the trigger waiting state to prepare for the next treatment cycle.

12. The control method for a spiral ultrasonic circuit system as described in claim 11, characterized in that: The helical sound field generated by the transducer array can have multiple modes by using different phase control methods; whereby the phase of array element n is defined as: , It can be a constant or a function of time; When rotated clockwise ; When rotated counterclockwise ; When in dynamic control It enables spiral scanning with angular velocity acceleration or deceleration.

13. A computer device comprising a memory, a processor, and a computer program stored in the memory and executable on the processor, characterized in that, When the processor executes the computer program, it implements the steps of the method as described in claim 11.

14. A computer-readable storage medium having a computer program stored thereon, characterized in that, When the computer program is executed by a processor, it implements the steps of the method as described in claim 11.

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