Pulse ultrasound hemorrhagic shock emergency system and control method
Patent Information
- Application Number
- CN202610867765.8
- Authority / Receiving Office
- CN · China
- Patent Type
- Applications(China)
- Current Assignee / Owner
- Filing Date
- 2026-06-16
- Publication Date
- 2026-09-15
Smart Images
Figure CN122745486A_ABST
Abstract
Description
Technical Field
[0001] This application relates to the field of medical device technology, and in particular to a pulsed ultrasound emergency treatment system and control method for hemorrhagic shock. Background Technology
[0002] Hemorrhagic shock is a critical condition caused by massive blood loss, resulting in insufficient effective circulating blood volume, inadequate tissue perfusion, and multiple organ dysfunction. Traditional treatments include rapid fluid resuscitation, blood transfusion, and the use of vasoactive drugs, but these methods suffer from problems such as high drug dependence, complex equipment, and poor operational timeliness, making them particularly difficult to implement quickly in pre-hospital or field emergency scenarios.
[0003] In recent years, ultrasound technology has been gradually applied to clinical treatment due to its non-invasiveness and controllability. Among related technologies, ultrasound is often used for tissue repair or thrombolysis. However, for patients with hemorrhagic shock, the above-mentioned technologies are difficult to rapidly raise and stabilize blood pressure, which can easily lead to the patient missing the optimal rescue time. Summary of the Invention
[0004] Therefore, it is necessary to provide a pulsed ultrasound emergency treatment system and control method for hemorrhagic shock that can solve the above-mentioned technical problems.
[0005] In a first aspect, this application provides a pulsed ultrasound emergency treatment system for hemorrhagic shock, which includes a main unit, a controller, a connecting cable, and an ultrasound generator; the main unit is used to integrate a power module and a signal processing unit to provide stable power and regulate ultrasound parameters; the controller is used to determine key parameters and optimize the key parameters based on blood pressure feedback values; the connecting cable is used to transmit control signals and power; the ultrasound generator is used to generate low-intensity pulsed ultrasound signals based on key parameters and apply them to the patient's carotid triangle area through an ultrasound transducer to regulate the patient's blood pressure.
[0006] In one embodiment, the aforementioned key parameters include a first parameter and a second parameter; the controller is further configured to determine the key parameter as the first parameter when a first triggering condition is met; the first triggering condition includes a systolic blood pressure less than 60 mmHg, a blood pressure drop of more than 30 mmHg in a short period of time, and / or an emergency scenario where there are no other means of raising blood pressure; the first parameter includes an ultrasound frequency of 1-2 MHz, a pulse frequency of 50-220 Hz, a duty cycle of 5%-55%, and an effective sound intensity of 0.5-3.5 W / cm²;
[0007] If the second triggering conditions are met, the key parameters are determined as the second parameters; the second triggering conditions include systolic blood pressure rising to greater than 80-90 mmHg, blood pressure fluctuating between 70-100 mmHg and / or the need to reduce tissue thermal damage; the second parameters include ultrasound frequency of 2-4 MHz, pulse frequency of 50-200 Hz, duty cycle of 10%-55%, and effective sound intensity of 0.5-3.5 W / cm².
[0008] In one embodiment, the host is configured to be powered by a DC power supply through a power module and converted to an adjustable DC level through a flyback PWM switching power supply circuit; it is also configured to sequentially convert the power supply to the required voltage at each stage through a multi-stage DC-DC power management module.
[0009] In one embodiment, the ultrasonic transducer is connected to the ultrasonic generator through an LC-type resonant matching network. The LC-type resonant matching network has a 1nF resonant capacitor connected in parallel across the ultrasonic transducer to widen the interval between the series and parallel resonant frequencies of the resonant network.
[0010] In one embodiment, the signal processing unit in the host computer includes a microcontroller, a signal sampling and processing module, and a phase difference detection circuit. The microcontroller is used to adjust the frequency of the drive signal to control the intermittent operation of the ultrasonic transducer, and to dynamically adjust the frequency of the drive signal based on phase difference information to track the resonant frequency of the ultrasonic transducer in real time. The signal sampling and processing module is used to acquire the voltage and current signals of the LC-type resonant matching network and monitor the operating status of the ultrasonic transducer. The phase difference detection circuit is used to detect the magnitude of the phase difference between the voltage and current in the LC-type resonant matching network.
[0011] In one embodiment, the ultrasonic generator includes a flyback PWM switching power supply module, a switching transistor drive circuit, a push-pull Class B power amplifier circuit, an impedance matching network, and an ultrasonic transducer. The flyback PWM switching power supply module provides a stable DC voltage. The push-pull Class B power amplifier circuit amplifies the output signal of the flyback PWM switching power supply module to drive the entire resonant network to operate normally. The impedance matching network adjusts the series and parallel resonant frequencies, optimizes the system's resonant characteristics, and ensures the ultrasonic transducer operates within a specific frequency range.
[0012] Secondly, this application also provides a control method for a pulsed ultrasound hemorrhagic shock emergency system, applied to the pulsed ultrasound hemorrhagic shock emergency system of the first aspect described above, the method comprising:
[0013] The system controls the power supply module to output stable electrical energy and the signal processing unit to generate regulation commands, enabling the controller, connecting lines, and ultrasound generator to work in tandem. It receives key parameters transmitted from the controller, which determines and optimizes these parameters based on blood pressure feedback. The signal processing unit converts these key parameters into drive signals, which are then transmitted to the ultrasound generator via the connecting lines. The system acquires the operating status of the ultrasound generator and transducer monitored by the signal processing unit, and adjusts the drive signal frequency based on the monitored LC-type resonant matching network voltage, current signals, and phase difference information to enable the ultrasound transducer to operate. Finally, it controls the ultrasound generator to generate low-intensity pulsed ultrasound signals based on the key parameters, which are then applied to the patient's carotid triangle via the ultrasound transducer to regulate the patient's blood pressure.
[0014] In one embodiment, the key parameters transmitted by the receiving controller include:
[0015] The key parameters sent by the controller are received through the connection line. If the key parameter is the first parameter, then the first parameter is the ultrasonic frequency of 1-2MHz, the pulse frequency of 50-220Hz, the duty cycle of 5%-55%, and the effective sound intensity of 0.5-3.5W / cm².
[0016] If the key parameter is the second parameter, then the second parameter is an ultrasonic frequency of 2-4MHz, a pulse frequency of 50-200Hz, a duty cycle of 10%-55%, and an effective sound intensity of 0.5-3.5W / cm².
[0017] Thirdly, this application also provides a computer device. The computer device includes a memory and a processor, the memory storing a computer program, and the processor executing the computer program to implement the method steps described in the second aspect.
[0018] Fourthly, this application also provides a computer-readable storage medium. This computer-readable storage medium stores a computer program thereon, which, when executed by a processor, implements the method steps of the second aspect described above.
[0019] Fifthly, this application also provides a computer program product. This computer program product includes a computer program that, when executed by a processor, implements the method steps described in the second aspect.
[0020] The aforementioned pulsed ultrasound hemorrhagic shock emergency system and control method adopt an integrated architecture of a main unit, controller, connecting cable, and ultrasound generator. The main unit integrates a power module and signal processing unit, solving the problems of complexity, unstable power supply, and poor operational timeliness of traditional emergency equipment. The controller can determine and dynamically optimize key parameters according to blood pressure status, solving the problems of lack of dynamic adjustment capability and easy under- or over-regulation in traditional solutions. The ultrasound generator generates low-intensity pulsed ultrasound according to key parameters, which acts on the carotid triangle area through a transducer to activate the baroreflex mechanism, solving the problem that existing ultrasound technology lacks a non-invasive control solution for hemorrhagic shock, and achieving non-invasive, precise, and efficient blood pressure control. Attached Figure Description
[0021] Figure 1 This is one of the structural schematic diagrams of a pulsed ultrasound hemorrhagic shock emergency system;
[0022] Figure 2 This is the second schematic diagram of a pulsed ultrasound emergency system for hemorrhagic shock.
[0023] Figure 3 Overall block diagram of the system design;
[0024] Figure 4 This is a structural diagram of a flyback switching power supply.
[0025] Figure 5 The figure shows the reactance and frequency variation of the LC resonant matching method and the resonant network.
[0026] Figure 6 This is a design schematic of a phase detection circuit;
[0027] Figure 7 This is a structural diagram of a push-pull Class B power amplifier.
[0028] Figure label:
[0029] 1. Ultrasound generator, 2. Connecting cable (data transmission cable and power cable), 3. Controller, 4. Display (human-machine interface), 5. Switch, 6. Carotid triangle area. Detailed Implementation
[0030] To make the objectives, technical solutions, and advantages of this application clearer, the following detailed description is provided in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and not intended to limit the scope of this application.
[0031] This application provides a pulsed ultrasound emergency treatment system for hemorrhagic shock, such as... Figure 1 and Figure 2As shown, the system includes a main unit, a controller, connecting cables, and an ultrasound generator. The main unit integrates a power module and a signal processing unit, providing stable power and regulating ultrasound parameters. The controller determines key parameters and optimizes them based on blood pressure feedback. The connecting cables transmit control signals and power. The ultrasound generator generates low-intensity pulsed ultrasound signals based on key parameters, which are then applied to the patient's carotid triangle via an ultrasound transducer to regulate blood pressure.
[0032] The system mainly consists of an STM32F407ZGT6 microcontroller, a DMG80480T070_05WTC serial port display, a flyback PWM switching power supply module, a switching transistor driver circuit, a push-pull Class B power amplifier circuit, an impedance matching network, a signal sampling and processing module, and a phase difference detection circuit. Specifically... Figure 3 As shown.
[0033] The STM32 microcontroller is responsible for adjusting the frequency of the drive signal in real time and controlling the intermittent operation of the transducer. The PWM switching power supply module provides a stable DC voltage, and its output is amplified by a Class B power amplifier circuit to drive the entire resonant network to operate normally. The resonant network consists of an impedance matching network and an ultrasonic transducer. The impedance matching network optimizes the resonant characteristics of the system by adjusting the series and parallel resonant frequencies to ensure that the transducer operates efficiently within a specific frequency range. The signal sampling and processing module collects the voltage and current signals of the matching network and monitors the operating status of the ultrasonic transducer.
[0034] In an exemplary embodiment, the key parameters of this application embodiment include a first parameter and a second parameter; the controller is further configured to determine the key parameter as the first parameter when a first triggering condition is met; the first triggering condition includes systolic blood pressure less than 60 mmHg, blood pressure dropping more than 30 mmHg in a short period of time and / or being in an emergency scenario where there are no other means of raising blood pressure; the first parameter includes an ultrasonic frequency of 1-2 MHz, a pulse frequency of 50-220 Hz, a duty cycle of 5%-55%, and an effective sound intensity of 0.5-3.5 W / cm²;
[0035] If the second triggering conditions are met, the key parameters are determined as the second parameters; the second triggering conditions include systolic blood pressure rising to greater than 80-90 mmHg, blood pressure fluctuating between 70-100 mmHg and / or the need to reduce tissue thermal damage; the second parameters include ultrasound frequency of 2-4 MHz, pulse frequency of 50-200 Hz, duty cycle of 10%-55%, and effective sound intensity of 0.5-3.5 W / cm².
[0036] Specifically, the first parameter for blood pressure selection is as follows:
[0037] Triggering conditions: A significant decrease in systolic blood pressure (e.g., <60 mmHg), indicating the patient is in the early stages of hemorrhagic shock with unstable vital signs, requiring emergency vasopressor administration. Rapid blood pressure decline (e.g., a drop of >30 mmHg in a short period) necessitates swift intervention to prevent organ inadequate perfusion. In pre-hospital emergency care or battlefield environments where no other vasopressor methods (e.g., medication, intravenous fluids) are available, the combination of parameters with the strongest vasopressor effect should be prioritized.
[0038] Features: Lower ultrasound frequency (1–2 MHz): Deeper penetration, allowing for more effective stimulation of the carotid sinus baroreceptors. Higher pulse frequency (50–220 Hz): High-frequency pulses more strongly activate the baroreflex arc, rapidly triggering a vasoconstrictive response.
[0039] Duty cycle (5%–55%) and sound intensity (0.5–3.5 W / cm²) are adjustable: In the early stages of shock, the duty cycle and sound intensity can be appropriately increased (e.g., duty cycle > 30%, sound intensity > 2 W / cm²) to enhance nerve reflex intensity and accelerate blood pressure recovery.
[0040] The situation regarding switching the second parameter for blood pressure is as follows:
[0041] Applicable scenarios: Blood pressure has initially risen and needs to be kept stable to avoid excessive pressure increase or tissue damage.
[0042] Triggering conditions: Systolic blood pressure has risen to a safe range (e.g., >80–90 mmHg), but it still needs to be kept stable to prevent blood pressure from dropping again. If blood pressure fluctuations occur (e.g., systolic blood pressure fluctuates between 70–100 mmHg), parameters need to be adjusted to avoid blood pressure being too high or too low. After prolonged use of parameter 1, it is necessary to reduce the potential thermal damage to tissues or nerve fatigue caused by ultrasound and switch to a gentler parameter combination.
[0043] Features: High ultrasound frequency (2–4MHz): shallower penetration depth, reducing the impact on deep tissues while maintaining stimulation of the carotid sinus.
[0044] Slightly lower pulse frequency (50–200Hz): Reduces the intensity of nerve stimulation and avoids excessive activation of the baroreflex, which could lead to a sudden rise in blood pressure.
[0045] Duty cycle (10%–55%) and sound intensity (0.5–3.5 W / cm²) optimization: During the maintenance phase, the duty cycle (e.g., <30%) and sound intensity (e.g., <2 W / cm²) can be appropriately reduced to decrease energy consumption and the risk of tissue damage, while maintaining stable blood pressure.
[0046] Duty cycle and sound intensity are key parameters for regulating ultrasound energy transmission and nerve stimulation intensity, and directly affect the blood pressure regulation effect.
[0047] The effects of duty cycle are as follows: An increased duty cycle (e.g., from 20% to 50%) results in a longer "on" time for the ultrasound pulse per unit time, increasing total energy transfer and providing stronger stimulation to the carotid sinus baroreceptors, thus activating the baroreflex more quickly and raising blood pressure. A decreased duty cycle (e.g., from 50% to 10%) reduces ultrasound energy accumulation, avoids neural adaptive fatigue (prolonged high-intensity stimulation leads to decreased receptor sensitivity), and is suitable for gentle stimulation during the maintenance phase.
[0048] The effect of sound intensity:
[0049] Increased sound intensity (e.g., from 1W / cm² → 3W / cm²): Increased ultrasound energy per unit area enhances mechanical and thermal effects, which can more strongly stimulate the nerve endings of the carotid sinus, accelerate vasoconstriction and increase heart rate, thereby rapidly raising blood pressure.
[0050] Decreased sound intensity (e.g., from 3 W / cm² to 1 W / cm²): Reduces the risk of tissue thermal damage, avoids excessive activation of the baroreflex leading to high blood pressure or arrhythmia, and is suitable for long-term maintenance therapy.
[0051] The optimization logic of dynamic adjustment: early stage of shock (critical state of hypotension): high duty cycle (e.g., 40–55%) + high sound intensity (e.g., 2.5–3.5 W / cm² → rapid increase in blood pressure).
[0052] After blood pressure rises (maintenance phase): reduce duty cycle (e.g., 15–30%) + moderate sound intensity (e.g., 1–2 W / cm²) → stabilize blood pressure and reduce side effects.
[0053] Feedback adjustment: By monitoring blood pressure changes in real time, if the upward trend of blood pressure is slowed down or decreased, the duty cycle and sound intensity can be finely adjusted (e.g., duty cycle ±10%, sound intensity ±0.5W / cm²) to form a closed-loop optimization.
[0054] As shown in Table 1, Table 1 shows the correspondence between blood pressure status, parameter selection, and duty cycle / sound intensity adjustment.
[0055] Table 1
[0056] stage Blood pressure status Parameter selection Duty cycle / sound intensity modulation Emergency period <60 mmHg (critical) Parameter 1 (1–2MHz) Duty cycle (>30%), high sound intensity (>2W / cm²) → rapid voltage boost Maintenance period 80–100 mmHg (fluctuation) Parameter 2 (2–4MHz) Medium duty cycle (15–30%), medium sound intensity (1–2 W / cm²) → stabilize blood pressure Optimization period Blood pressure fluctuations or trends slow down Dynamic adjustment Based on real-time blood pressure feedback, fine-tuning is performed at ±10% duty cycle and ±0.5 W / cm² → closed-loop control.
[0057] In an exemplary embodiment, the host of this application embodiment is used to be powered by a DC power supply through a power supply module and converted to an adjustable DC level through a flyback PWM switching power supply circuit; it is also used to convert the power supply to the required voltage at each stage through a multi-stage DC-DC power management module.
[0058] Specifically, such as Figure 4 As shown, a flyback switching power supply mainly consists of a switching transistor and drive circuit, a clamping circuit, a transformer, a filter circuit, and a sampling and PID control module.
[0059] The STM32 microcontroller generates a 40kHz PWM square wave, which is amplified by the switching transistor driver circuit and then controls the switching transistor Q1 to turn on and off, thereby modulating and transmitting electrical energy. When Q1 is on, one end of the transformer's primary winding is connected to a 24V DC power supply, and the other end is grounded. Electrical energy accumulates in the primary winding, forming a magnetic field. When Q1 is off, the current in the primary winding drops rapidly, generating an induced electromotive force at Np in the secondary winding. At this time, diode D1 conducts, and the electrical energy in the secondary winding is rectified by D1 and filtered by C1 to be converted into stable DC power, which is then applied to the load.
[0060] To ensure the load voltage remains stable at the desired value, the system employs a negative feedback control mechanism: First, the load voltage is sampled through a voltage divider resistor and fed back to the STM32 microcontroller. The PID control algorithm dynamically adjusts the duty cycle of the PWM square wave based on the error between the sampled voltage and the target voltage, thereby precisely controlling the on-time of the switching transistor and ultimately outputting a stable load voltage.
[0061] The system is powered by a 24V DC power supply. This voltage is converted to an adjustable DC level in the flyback switching power supply circuit to regulate and control the system power. Since some chips in the system require 12V and ±5V DC voltages, a multi-stage DC-DC power management module is designed to sequentially convert the 24V power supply to the required voltages at each stage, providing stable power support for all devices within the system.
[0062] In this embodiment of the application, the power management module adopts the following solution:
[0063] The ETA2893 is used to convert 24V to 12V. This chip features a wide input voltage range, high conversion efficiency, low heat generation, and a maximum output capacity of 3A, meeting the power supply requirements of all 12V chips in the system.
[0064] The LMZ12003 is used to convert 12V to 5V. As a highly integrated modular voltage regulator, it features high output power, high conversion efficiency, and low voltage ripple, making it suitable for powering core digital circuits.
[0065] The MAX860 is used to implement 5V to -5V conversion. It adopts a charge pump structure and has the advantages of low power consumption, low noise, and simple peripheral circuitry, making it suitable for providing negative voltage to analog devices.
[0066] In an exemplary embodiment, the ultrasonic transducer of this application is connected to the ultrasonic generator through an LC-type resonant matching network. The LC-type resonant matching network has a 1nF resonant capacitor connected in parallel across the ultrasonic transducer to widen the interval between the series and parallel resonant frequencies of the resonant network.
[0067] Specifically, the LC-type resonant matching scheme adopted in this application, through matching design, ensures that the series and parallel resonant frequencies of the resonant network containing the transducer are far apart and within a reasonable interval, thus giving the ultrasonic transducer a wider effective operating frequency range. This achieves a comprehensive consideration of expanding the effective operating range while primarily focusing on reducing the reactive power loss of the transducer and improving system efficiency, laying the foundation for future functional expansion to achieve multi-frequency ultrasonic control.
[0068] Traditional resonant matching designs primarily focus on reducing the reactive power loss of the transducer, often neglecting the optimized control of the series and parallel resonant frequencies. This design approach results in a narrow effective tracking range for the frequency tracking system, making it highly susceptible to mistracking or detuning when the transducer frequency deviates. To address this issue, if the series and parallel resonant frequencies of the resonant network containing the transducer can be spaced far apart and within a reasonable interval through resonant matching design, the frequency tracking system will have a wider effective tracking range. As long as this range exceeds the actual deviation range of the transducer's operating frequency, the stability of the frequency tracking system will be significantly improved, and problems such as detuning and mistracking will be less likely to occur.
[0069] The LC-type resonant matching scheme adopted in this application comprehensively considers the needs of reducing transducer reactive losses and expanding the effective frequency tracking range. The LC resonant matching method and the reactance and frequency variation of the resonant network are shown below. Figure 5 As shown, a 1nF resonant capacitor C is connected in parallel across the transducer. p The parallel resonant frequency F of the resonant network can be calculated. p1 As shown in formula (1):
[0070] (1)
[0071] From the above formula, we can see that: F p1 Compared to F p Slightly reduced, closer to F s At the same time, the capacitor also effectively reduces the equivalent impedance of the transducer at this frequency, as measured at F... p1 The vibration effect remains good. Furthermore, the resonant network, due to the introduction of L... p The resonant network will exhibit two new series resonant frequencies F. s1 and F s2 Series resonant frequency F s It will move to the left to F s1 The position, and a new series resonant frequency F will appear above the parallel resonant frequency. s2 With the matching inductor L s Increase, F s1 and F s2They will all move to the left. When using the phase method for frequency tracking, F s1 and F s2 The distance is the reliable tracking range of the system, which can be adjusted by adjusting L. p The size changes.
[0072] In LC resonant matching, to make the resonant network purely resistive, the theoretical inductance Lp required for resonant matching can be calculated. During operation, its internal dynamic inductance, dynamic capacitance, and resonant frequency will continuously change with external factors such as load and temperature. The value of the matching inductance Lp calculated according to the theoretical formula will also change. Therefore, static LC resonant matching can only reduce reactive power generation to a certain extent.
[0073] In LC resonant matching, this application comprehensively balances the factors of reducing reactive power and expanding the effective operating range of the resonant frequency tracking system. Experimental verification shows that, on the one hand, the system's useless power consumption is significantly suppressed, improving the overall efficiency; on the other hand, Fs1 and Fs2 are both far from the parallel resonant frequency, effectively widening the frequency tracking interval.
[0074] In an exemplary embodiment, the signal processing unit in the host computer includes a microcontroller, a signal sampling and processing module, and a phase difference detection circuit. The microcontroller is used to adjust the frequency of the drive signal to control the intermittent operation of the ultrasonic transducer, and to dynamically adjust the frequency of the drive signal based on phase difference information to track the resonant frequency of the ultrasonic transducer in real time. The signal sampling and processing module is used to acquire the voltage and current signals of the LC-type resonant matching network and monitor the operating status of the ultrasonic transducer. The phase difference detection circuit is used to detect the magnitude of the phase difference between the voltage and current in the LC-type resonant matching network.
[0075] Specifically, the phase detection circuit needs to continuously extract the magnitude of the phase difference between the voltage and current in the resonant network, as well as their lead-lag relationship. The design diagram of the phase detection circuit is shown below. Figure 6 As shown.
[0076] The voltage and current signals in the resonant network are sampled by a voltage divider resistor and a Hall current sensor, respectively. Since the signal amplitude output by the Hall current sensor is relatively small, which is not conducive to subsequent processing, it needs to be amplified by a non-inverting amplifier. The amplified current sampling signal and the voltage sampling signal are then passed together through a bandpass filter with the same parameters to filter out noise and retain the dominant frequency component.
[0077] The two filtered signals are fed into a zero-crossing detection circuit and converted into square wave signals with the same frequency and phase. Then, the voltage square wave and the current square wave are each split into two paths: one path is used to determine the lead or lag relationship through a D flip-flop; the other path is used to extract the absolute value of the phase difference through an XOR gate and a low-pass filter.
[0078] The microcontroller dynamically adjusts the frequency of the drive signal based on this phase difference information. Combining this with the curve of the resonant network's reactance versus frequency, we can see that: when the phase difference is not zero, if the voltage phase leads the current, the circuit is inductive, and the drive frequency should be appropriately increased; if the voltage lags the current, the circuit is capacitive, and the drive frequency should be decreased.
[0079] Design of voltage and current sampling circuits: Voltage sampling is performed using a resistor divider method.
[0080] Because the resonant network voltage amplitude is high under high power operation, the sampling voltage also increases accordingly. To ensure the stable operation of subsequent circuits, a clamping diode is introduced into the voltage sampling circuit to limit the amplitude of the sampling signal to ±5V, thereby effectively preventing circuit damage caused by overvoltage. The current in the resonant network is sampled by a Hall current detection chip, which converts the alternating current signal into a voltage signal in phase with it.
[0081] This circuit uses I+ and I− connected in series to a resonant network to acquire the current signal in the resonant network and convert it into a voltage signal Vp in phase with the original current. Subsequently, a differential amplifier circuit amplifies the AC component of Vp. The positive input of the differential amplifier is connected to Vp, while the negative input is connected to a DC reference voltage generated by a resistor divider.
[0082] Bandpass filter design: Before the voltage and current sampling signals are sent to the zero-crossing detection circuit and converted into square wave signals, a filtering circuit is needed to remove low-frequency and high-frequency noise from the signals. Since the phase detection circuit needs to accurately extract the phase relationship between voltage and current, the filtering circuit must avoid introducing additional phase deviation. Therefore, this application designs two eighth-order bandpass filters. The voltage and current sampling signals are processed by bandpass filters of the same structure, thereby ensuring that the phase relationship between the filtered signals remains unchanged.
[0083] Design of the zero-crossing detection circuit: To extract the phase difference information between the sampled voltage and current, the filtered analog signal must first be converted into a square wave signal with the same frequency and phase for subsequent phase comparison and frequency tracking control. Therefore, this application selects a single-channel comparator with high-speed response and high detection accuracy, which can effectively meet the requirements of zero-crossing detection for response speed and accuracy.
[0084] Design scheme of D flip-flop and XOR gate circuit: After obtaining the square wave signals of sampled voltage and current, a D flip-flop is used to detect the lead-lag relationship between voltage and current. The voltage square wave and current square wave are used as the clock signal and input signal of the chip, respectively. When the current leads the voltage, the D flip-flop samples a high level on the rising edge of the voltage and outputs a high value, indicating that the resonant network is capacitive, otherwise it is inductive. The microcontroller can determine the electrical characteristics of the current resonant network by reading the level state of the D flip-flop output, and dynamically adjust the frequency of the ultrasonic drive signal accordingly, thereby achieving fast and stable tracking of the resonant frequency. Then, the XOR gate performs logical operations on the voltage and current square wave signals to extract the phase difference information between them. The two inputs of the XOR gate are connected to the voltage square wave and current square wave signals, respectively, and its output is a pulse signal with a duty cycle proportional to the phase difference. This square wave signal is then processed by a low-pass filter and converted into a DC voltage proportional to the phase difference for sampling by the microcontroller, thereby realizing the quantitative detection of the phase difference and closed-loop feedback of frequency control.
[0085] Ultimately, the STM32 microcontroller reads the output levels of the D flip-flop and XOR gate circuit, adjusts the frequency of the ultrasonic drive signal according to the detection results, and thus achieves real-time tracking of the resonant frequency of the ultrasonic transducer.
[0086] In one exemplary embodiment, the ultrasonic generator of this application includes a flyback PWM switching power supply module, a switching transistor drive circuit, a push-pull Class B power amplifier circuit, an impedance matching network, and an ultrasonic transducer; wherein, the flyback PWM switching power supply module is used to provide a stable DC voltage; the push-pull Class B power amplifier circuit is used to amplify the output signal of the flyback PWM switching power supply module to drive the entire resonant network to operate normally; the impedance matching network is used to adjust the series and parallel resonant frequencies, optimize the resonant characteristics of the system, and ensure that the ultrasonic transducer operates within a specific frequency range.
[0087] Specifically, the design of the push-pull Class B power amplifier is as follows:
[0088] like Figure 7 As shown, a push-pull Class B power amplifier mainly includes: power switching transistors and their driving circuits, a center-tapped transformer, complementary PWM control signals, and a DC power supply section.
[0089] The STM32 microcontroller outputs two complementary PWM drive signals (PWM+ and PWM-), which, after being amplified by the drive circuit, control the on / off state of power switches Q2 and Q3, respectively. Since the two signals are complementary, Q2 and Q3 are always in opposite operating states. When Q2 is on and Q3 is off, the drain of Q2 is connected to ground, and the DC power supply outputs a negative half-cycle power square wave through the center-tapped transformer; conversely, when Q3 is on and Q2 is off, the output is a positive half-cycle power square wave. Therefore, the output Vout ultimately forms alternating positive and negative power square waves to drive the ultrasound transducer. By adjusting the frequencies of PWM+ and PWM-, dynamic control of the ultrasound transducer's operating frequency can be achieved, allowing for optimal regulation based on clinical needs.
[0090] The system's human-computer interaction interface is designed as follows:
[0091] A 7-inch serial port screen, DMG8048T070_05W, was selected as the system's human-machine interface, establishing a communication connection with the main control microcontroller, STM32F407ZGT6, via a USART interface. Users can set the startup status and power parameters through the touch interface. In the future, settings such as duty cycle adjustment, control duration, and frequency selection will be introduced according to clinical needs.
[0092] This application also provides a control method for a pulsed ultrasound hemorrhagic shock emergency system, applied to the pulsed ultrasound hemorrhagic shock emergency system as described above. The specific composition of the system is described in detail above.
[0093] The method in this embodiment includes: controlling the power module to output stable electrical energy and controlling the signal processing unit to generate regulation commands, linking the controller, connecting lines, and ultrasound generator to work together; receiving key parameters transmitted by the controller; the key parameters are determined and optimized by the controller based on blood pressure feedback values; converting the key parameters into drive signals through the signal processing unit and transmitting them to the ultrasound generator via the connecting lines; acquiring the operating status of the ultrasound generator and ultrasound transducer monitored by the signal processing unit, adjusting the drive signal frequency based on the monitored LC-type resonant matching network voltage, current signals, and phase difference information to enable the ultrasound transducer to operate; controlling the ultrasound generator to generate low-intensity pulse ultrasound signals based on the key parameters, and applying them to the patient's carotid triangle area through the ultrasound transducer to regulate the patient's blood pressure.
[0094] The key parameters transmitted by the receiving controller include: key parameters sent by the receiving controller via the connection line. If the key parameter is the first parameter, the first parameter is an ultrasonic frequency of 1-2MHz, a pulse frequency of 50-220Hz, a duty cycle of 5%-55%, and an effective sound intensity of 0.5-3.5W / cm². If the key parameter is the second parameter, the second parameter is an ultrasonic frequency of 2-4MHz, a pulse frequency of 50-200Hz, a duty cycle of 10%-55%, and an effective sound intensity of 0.5-3.5W / cm².
[0095] In one embodiment, a computer device is provided, which may be a terminal. The computer device includes a processor, memory, input / output interface, communication interface, display unit, and input device. The processor, memory, and input / output interface are connected via a system bus, and the communication interface, display unit, and input device are connected to the system bus via the input / output interface. The processor of the computer device provides computing and control capabilities. The memory of the computer device includes a non-volatile storage medium and internal memory. The non-volatile storage medium stores an operating system and computer programs. The internal memory provides an environment for the operation of the operating system and computer programs in the non-volatile storage medium. The input / output interface of the computer device is used for exchanging information between the processor and external devices. The communication interface of the computer device is used for wired or wireless communication with external terminals; wireless communication can be achieved through Wi-Fi, mobile cellular networks, NFC (Near Field Communication), or other technologies. When the computer program is executed by the processor, it implements a control method for a pulsed ultrasound hemorrhagic shock emergency system. The display unit of the computer device is used to form a visually visible image and may be a display screen, a projection device, or a virtual reality imaging device. The display screen can be an LCD screen or an e-ink screen. The input device of the computer device can be a touch layer covering the display screen, or buttons, trackballs, or touchpads set on the casing of the computer device, or external keyboards, touchpads, or mice, etc.
[0096] In one embodiment, a computer device is provided, including a memory and a processor. The memory stores a computer program, and the processor executes the computer program to perform the following steps: controlling a power module to output stable electrical energy and controlling a signal processing unit to generate regulation commands, coordinating the operation of a controller, connecting lines, and an ultrasound generator; receiving key parameters transmitted by the controller; the key parameters being determined and optimized by the controller based on blood pressure feedback values; converting the key parameters into drive signals through the signal processing unit and transmitting them to the ultrasound generator via the connecting lines; acquiring the operating status of the ultrasound generator and ultrasound transducer monitored by the signal processing unit, and adjusting the drive signal frequency based on the monitored LC-type resonant matching network voltage, current signals, and phase difference information to enable the ultrasound transducer to operate; controlling the ultrasound generator to generate low-intensity pulsed ultrasound signals based on the key parameters, and applying them to the patient's carotid triangle through the ultrasound transducer to regulate the patient's blood pressure.
[0097] In one embodiment, a computer-readable storage medium is provided, on which a computer program is stored. When executed by a processor, the computer program performs the following steps: controlling a power supply module to output stable electrical energy and controlling a signal processing unit to generate regulation commands, thereby coordinating the operation of a controller, connecting lines, and an ultrasound generator; receiving key parameters transmitted by the controller; the key parameters being determined and optimized by the controller based on blood pressure feedback values; converting the key parameters into drive signals via the signal processing unit and transmitting them to the ultrasound generator via the connecting lines; acquiring the operating status of the ultrasound generator and ultrasound transducer monitored by the signal processing unit, and adjusting the drive signal frequency based on the monitored LC-type resonant matching network voltage, current signals, and phase difference information to enable the ultrasound transducer to operate; controlling the ultrasound generator to generate low-intensity pulsed ultrasound signals based on the key parameters, and applying these signals to the patient's carotid triangle via the ultrasound transducer to regulate the patient's blood pressure.
[0098] It should be noted that the user information (including but not limited to user device information, user personal information, etc.) and data (including but not limited to data used for analysis, data stored, data displayed, etc.) involved in this application are all information and data authorized by the user or fully authorized by all parties, and the collection, use and processing of related data must comply with the relevant laws, regulations and standards of the relevant countries and regions.
[0099] Those skilled in the art will understand that all or part of the processes in the above embodiments can be implemented by a computer program instructing related hardware. The computer program can be stored in a non-volatile computer-readable storage medium, and when executed, it can include the processes of the embodiments described above. Any references to memory, databases, or other media used in the embodiments provided in this application can include at least one of non-volatile and volatile memory. Non-volatile memory can include read-only memory (ROM), magnetic tape, floppy disk, flash memory, optical memory, high-density embedded non-volatile memory, resistive random access memory (ReRAM), magnetic random access memory (MRAM), ferroelectric random access memory (FRAM), phase change memory (PCM), graphene memory, etc. Volatile memory can include random access memory (RAM) or external cache memory, etc. By way of illustration and not limitation, RAM can take many forms, such as Static Random Access Memory (SRAM) or Dynamic Random Access Memory (DRAM). The databases involved in the embodiments provided in this application may include at least one type of relational database and non-relational database. Non-relational databases may include, but are not limited to, blockchain-based distributed databases. The processors involved in the embodiments provided in this application may be general-purpose processors, central processing units, graphics processing units, digital signal processors, programmable logic devices, quantum computing-based data processing logic devices, etc., and are not limited to these.
[0100] The technical features of the above embodiments can be combined in any way. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.
[0101] The embodiments described above are merely illustrative of several implementation methods of this application, and while the descriptions are specific and detailed, they should not be construed as limiting the scope of this patent application. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of this application, and these all fall within the protection scope of this application. Therefore, the protection scope of this application should be determined by the appended claims.
Claims
1. A pulsed ultrasound hemorrhagic shock emergency system, characterized in that, The system includes a host, a controller, connecting cables, and an ultrasonic generator; The host unit is used to integrate a power module and a signal processing unit to provide stable power and regulate ultrasound parameters. The controller is used to determine key parameters and optimize the key parameters based on blood pressure feedback values. The connecting line is used to transmit control signals and electrical energy; The ultrasound generator is used to generate low-intensity pulsed ultrasound signals based on the key parameters, and then apply them to the patient's carotid triangle area through an ultrasound transducer to regulate the patient's blood pressure.
2. The pulsed ultrasound hemorrhagic shock first aid system of claim 1, wherein, The key parameters include a first parameter and a second parameter; the controller is also used for, Under the condition of meeting the first triggering condition, the key parameter is determined as the first parameter; the first triggering condition includes systolic blood pressure less than 60 mmHg, blood pressure drop greater than 30 mmHg in a short period of time and / or being in an emergency situation where there are no other means of raising blood pressure; the first parameter includes ultrasound frequency of 1-2 MHz, pulse frequency of 50-220 Hz, duty cycle of 5%-55%, and effective sound intensity of 0.5-3.5 W / cm². Under the condition that the second triggering condition is met, the key parameter is determined as the second parameter; the second triggering condition includes systolic blood pressure rising to greater than 80-90 mmHg, blood pressure fluctuating between 70-100 mmHg and / or the need to reduce tissue thermal damage; the second parameter includes ultrasound frequency of 2-4 MHz, pulse frequency of 50-200 Hz, duty cycle of 10%-55%, and effective sound intensity of 0.5-3.5 W / cm².
3. The pulsed ultrasound hemorrhagic shock first aid system of claim 1, wherein, The host is used to be powered by DC power through a power module and converted to an adjustable DC level through a flyback PWM switching power supply circuit; it is also used to convert the power supply to the required voltage at each stage through a multi-stage DC-DC power management module.
4. The pulsed ultrasound hemorrhagic shock emergency system according to claim 1, characterized in that, The ultrasonic transducer is connected to the ultrasonic generator through an LC-type resonant matching network. A 1nF resonant capacitor is connected in parallel across the ultrasonic transducer to widen the interval between the series and parallel resonant frequencies of the resonant network.
5. The pulsed ultrasound hemorrhagic shock emergency system according to claim 4, characterized in that, The signal processing unit in the host computer includes a microcontroller, a signal sampling and processing module, and a phase difference detection circuit. The microcontroller is used to adjust the frequency of the drive signal, control the intermittent operation of the ultrasonic transducer, and dynamically adjust the frequency of the drive signal according to the phase difference information to track the resonant frequency of the ultrasonic transducer in real time. The signal sampling and processing module is used to collect the voltage and current signals of the LC type resonant matching network and monitor the working status of the ultrasonic transducer. The phase difference detection circuit is used to detect the magnitude of the phase difference between voltage and current in the LC type resonant matching network.
6. The pulsed ultrasound hemorrhagic shock emergency system according to claim 1, characterized in that, The ultrasonic generator includes a flyback PWM switching power supply module, a switching transistor drive circuit, a push-pull Class B power amplifier circuit, an impedance matching network, and the ultrasonic transducer; wherein... The flyback PWM switching power supply module is used to provide a stable DC voltage; The push-pull Class B power amplifier circuit is used to amplify the output signal of the flyback PWM switching power supply module to drive the entire resonant network to work normally. The impedance matching network is used to adjust the series and parallel resonant frequencies, optimize the resonant characteristics of the system, and ensure that the ultrasonic transducer operates within a specific frequency range.
7. A control method for a pulsed ultrasound hemorrhagic shock emergency system, applied to the pulsed ultrasound hemorrhagic shock emergency system as described in any one of claims 1 to 6, characterized in that, The method includes: The control power module outputs stable electrical energy, and the control signal processing unit generates regulation commands to coordinate the operation of the controller, connecting lines, and ultrasonic generator. The receiver receives key parameters transmitted by the controller; these key parameters are determined and optimized by the controller based on blood pressure feedback values; the signal processing unit converts these key parameters into drive signals, which are then transmitted to the ultrasound generator via a connection line. The signal processing unit acquires the operating status of the ultrasonic generator and the ultrasonic transducer monitored by the signal processing unit, and adjusts the driving signal frequency according to the monitored LC type resonant matching network voltage, current signal and phase difference information to enable the ultrasonic transducer to operate. The ultrasound generator is controlled to generate low-intensity pulsed ultrasound signals according to the key parameters, which are then applied to the patient's carotid triangle area through an ultrasound transducer to regulate the patient's blood pressure.
8. The control method according to claim 7, characterized in that, The key parameters transmitted by the receiving controller include: The controller sends key parameters via the connection line. If the key parameter is the first parameter, then the first parameter is an ultrasonic frequency of 1-2MHz, a pulse frequency of 50-220Hz, a duty cycle of 5%-55%, and an effective sound intensity of 0.5-3.5W / cm². If the key parameter is the second parameter, then the second parameter is an ultrasonic frequency of 2-4MHz, a pulse frequency of 50-200Hz, a duty cycle of 10%-55%, and an effective sound intensity of 0.5-3.5W / cm².
9. A computer device comprising a memory and a processor, wherein the memory stores a computer program, characterized in that, When the processor executes the computer program, it implements the steps of the method according to any one of claims 7 to 8.
10. 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 according to any one of claims 7 to 8.