A transcranial M-TMAS stimulation device

Abstract

The present invention discloses a transcranial M-TMAS stimulation device. The controller is respectively connected to an ultrasonic transducer excitation source and a TMS magnetic stimulation excitation source, and is used to control the ultrasonic transducer excitation source to send an ultrasonic excitation signal to a phased array ultrasonic transducer, and the phased array ultrasonic transducer forms a focused sound field based on the ultrasonic excitation signal; it is also used to control the TMS magnetic stimulation excitation source to send an alternating current excitation signal to a TMS magnetic stimulation coil, and the TMS magnetic stimulation coil forms an alternating magnetic field based on the alternating current excitation signal; the focused sound field and the alternating magnetic field are coupled to form a magneto-acoustic coupled electric field, and the alternating magnetic field also generates an alternating electric field; the magneto-acoustic coupled electric field, the alternating electric field, and the focused sound field act on the patient together; wherein, a filter is arranged in the ultrasonic transducer excitation source for filtering out the interference signal generated by the TMS magnetic stimulation coil on the phased array ultrasonic transducer. Thus, when stimulating the patient, the magneto-acoustic coupled electric field, the alternating electric field, and the focused sound field act on the patient together, enhancing the stimulation intensity.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and particularly to a transcranial M-TMAS stimulation device. Background Art

[0002] Brain science neuromodulation technology is a biomedical engineering technology that uses implantable or non-implantable technologies and physical stimulation or drug means to change the activity of the nervous system, thereby improving the disease symptoms of patients and enhancing the quality of life. In addition to the application of drugs, technologies based on physical factors such as electricity, magnetism, light, and sound for nerve stimulation play an important role in the basic research of neuroscience and the clinical diagnosis and treatment of neurological and mental diseases. However, the problem is that in related technologies, the intensity of nerve stimulation based on physical factors such as electricity, magnetism, light, and sound is generally relatively weak and cannot meet the requirements. Summary of the Invention

[0003] The present invention provides a transcranial M-TMAS stimulation device to solve the problem of relatively weak stimulation intensity when performing nerve stimulation in the basic research of neuroscience and the clinical diagnosis and treatment of neurological and mental diseases in related technologies.

[0004] To solve the above problems, an embodiment of the present invention proposes a transcranial M-TMAS stimulation device, including:

[0005] A phased array ultrasonic transducer, a TMS magnetic stimulation coil, an ultrasonic transducer excitation source, a TMS magnetic stimulation excitation source, and a controller;

[0006] The controller is respectively connected to the ultrasonic transducer excitation source and the TMS magnetic stimulation excitation source, and is used to control the ultrasonic transducer excitation source to send an ultrasonic excitation signal to the phased array ultrasonic transducer, and the phased array ultrasonic transducer forms a focused sound field based on the ultrasonic excitation signal; it is also used to control the TMS magnetic stimulation excitation source to send an alternating current excitation signal to the TMS magnetic stimulation coil, and the TMS magnetic stimulation coil forms an alternating magnetic field based on the alternating current excitation signal; the focused sound field and the alternating magnetic field are coupled to form a magnetoacoustic coupled electric field, and the alternating magnetic field also generates an alternating electric field; the magnetoacoustic coupled electric field, the alternating electric field, and the focused sound field act on the patient together;

[0007] Wherein, a filter is provided in the ultrasonic transducer excitation source for filtering out the interference signal generated by the TMS magnetic stimulation coil on the phased array ultrasonic transducer.

[0008] Optionally, the ultrasonic transducer excitation source includes:

[0009] FPGA focusing delay module, I / O channel expansion module, multiple fundamental frequency control circuits, multiple LC oscillation circuits, and low-pass filters, where the fundamental frequency control circuits, the LC oscillation circuits, and the low-pass filters correspond one by one;

[0010] The controller is used to provide the focusing excitation parameters for each channel of the phased array ultrasonic transducer. The FPGA focusing delay module is used to calculate the focusing delay data for each channel according to the focusing excitation parameters of each channel, and output the PWM wave carrying the focusing delay data corresponding to each channel in combination with the focusing delay data of each channel. The PWM waves carrying the focusing delay data corresponding to each channel are input into the corresponding fundamental frequency control circuit through the I / O channel expansion module. Each of the LC oscillation circuits oscillates the DC source signal into a sine wave signal according to the fundamental frequency signal output by the fundamental frequency control circuit. After filtering the sine wave signal by the low-pass filter, it is output into the corresponding channel of the phased array ultrasonic transducer.

[0011] Optionally, the fundamental frequency control circuit includes:

[0012] Optocoupler circuit unit, NAND gate circuit unit, crystal oscillator unit, MOS transistor control unit, and MOS transistor. The input end of the optocoupler circuit unit is connected to the I / O channel expansion module, the output end of the optocoupler circuit unit is connected to the input end of the NAND gate circuit unit, the output end of the crystal oscillator unit is connected to the input end of the NAND gate circuit unit, the output end of the NAND gate circuit unit is connected to the MOS transistor control unit, and the MOS transistor is in an open state or a closed state according to the level signal output by the MOS transistor control unit to provide a fundamental frequency signal for the LC oscillation circuit.

[0013] Optionally, the LC oscillation circuit includes: a first LC oscillation circuit unit and a second LC oscillation circuit unit. The input end of the first LC oscillation circuit unit is used to input the DC source signal. The output end of the first LC oscillation circuit is respectively connected to the input end of the second LC oscillation circuit and the second end of the MOS transistor. The third end of the MOS transistor is grounded. The output end of the second LC oscillation circuit is connected to the input end of the low-pass filter, and the output end of the low-pass filter is connected to the corresponding element of the phased array ultrasonic transducer.

[0014] Optionally, the low-pass filter includes: a first capacitor, a second capacitor, a third capacitor, a first resistor, a second resistor, a third resistor, and a comparator. The output end of the LC oscillation circuit is connected to one end of the first capacitor. The other end of the first capacitor is respectively connected to one end of the second capacitor, one end of the first resistor, and one end of the third capacitor. The other end of the first resistor is grounded. The other end of the second capacitor and one end of the second resistor are commonly connected to the first input end of the comparator. The other end of the third capacitor and the other end of the second resistor are connected to the output end of the comparator. One end of the third resistor is connected to the second input end of the comparator.

[0015] Optionally, the ultrasonic transducer excitation source includes:

[0016] a focusing delay module, a DDS signal generation module, a plurality of first-stage operational amplifier modules, a plurality of second-stage power amplifier modules, and a plurality of band-pass filters. The first-stage operational amplifier modules and the second-stage power amplifier modules are correspondingly arranged, and the second-stage power amplifier modules correspond to two of the band-pass filters;

[0017] The controller is used to provide the focusing excitation parameters of each channel of the phased array ultrasonic transducer. The focusing delay module is used to obtain the focusing delay data corresponding to the focusing excitation parameters of each channel according to the focusing excitation parameters of each channel. The DDS signal generation module transmits a first excitation signal to each element of the phased array ultrasonic transducer according to the focusing delay data of each channel. The first-stage operational amplifier module is used to form two second excitation signals with the same amplitude and opposite phases from the first excitation signal. The second-stage power amplifier module is used to perform power amplification on the two second excitation signals with the same amplitude and opposite phases and then output them to the corresponding band-pass filters, and after being filtered by the band-pass filters, output them to the corresponding channels of the phased array ultrasonic transducer.

[0018] Optionally, the first-stage operational amplifier module includes: a DC-blocking and AC-coupling unit and an operational amplifier unit; the input end of the DC-blocking and AC-coupling unit is connected to the output end of the DDS signal generation module, and is used to convert the first excitation signal into an AC signal; the input end of the operational amplifier unit is connected to the output end of the DC-blocking and AC-coupling unit, and is used to convert the AC signal into two second excitation signals with the same amplitude and opposite phases.

[0019] Optionally, the secondary power amplification module includes: a first secondary power amplification unit and a second secondary power amplification unit. The input end of the first secondary power amplification unit is connected to the first output end of the primary operational amplification module, the output end is connected to the input end of the band-pass filter, and the output end of the band-pass filter is connected to one end of the phased array ultrasonic transducer; the input end of the second secondary power amplification unit is connected to the second output end of the primary operational amplification module, the output end is connected to the input end of the band-pass filter, and the output end of the band-pass filter is connected to the other end of the phased array ultrasonic transducer.

[0020] Optionally, both the first secondary power amplification unit and the second secondary power amplification unit include an input stage circuit, an excitation stage circuit, and an output stage circuit. The input end of the input stage circuit is connected to one of the output ends of the primary operational amplification module, and is used to suppress the zero drift of the second excitation signal. The excitation stage circuit is used to compensate for the zero-crossing distortion of the second excitation signal. The output stage circuit is used to amplify the excitation signal processed by the input stage circuit and the excitation stage circuit, and output it to the band-pass filter, and after being filtered by the band-pass filter, output it to the phased array ultrasonic transducer.

[0021] Optionally, the band-pass filter includes: a fourth capacitor, a fifth capacitor, a sixth capacitor, a first inductor, a second inductor, and a third inductor. One end of the fourth capacitor is connected to one of the output ends in the secondary power amplification module, the other end of the fourth capacitor is connected to one end of the first inductor, the other end of the first inductor is connected to one end of the second inductor, the other end of the second inductor is grounded, the fifth capacitor is connected in parallel with the second inductor, one end of the third inductor is connected to the other end of the first inductor, the other end of the third inductor is connected to one end of the sixth capacitor, and the other end of the sixth capacitor is connected to the phased array ultrasonic transducer.

[0022] The transcranial M-TMAS stimulation device according to an embodiment of the present invention includes: a phased array ultrasonic transducer, a TMS magnetic stimulation coil, an ultrasonic transducer excitation source, a TMS magnetic stimulation excitation source, and a controller; the controller is respectively connected to the ultrasonic transducer excitation source and the TMS magnetic stimulation excitation source, and is used to control the ultrasonic transducer excitation source to send an ultrasonic excitation signal to the phased array ultrasonic transducer, and the phased array ultrasonic transducer forms a focused sound field based on the ultrasonic excitation signal; it is also used to control the TMS magnetic stimulation excitation source to send an alternating current excitation signal to the TMS magnetic stimulation coil, and the TMS magnetic stimulation coil forms an alternating magnetic field based on the alternating current excitation signal; the focused sound field and the alternating magnetic field are coupled to form a magnetoacoustic coupled electric field, and the alternating magnetic field also generates an alternating electric field; the magnetoacoustic coupled electric field, the alternating electric field, and the focused sound field act on the patient together; wherein, a filter is provided in the ultrasonic transducer excitation source for filtering out the interference signal generated by the TMS magnetic stimulation coil on the phased array ultrasonic transducer. Thus, by the combined action of the ultrasonic transducer and the TMS magnetic stimulation coil on the patient, when stimulating the patient, the magnetoacoustic coupled electric field, the alternating electric field, and the focused sound field act on the patient together, enhancing the stimulation intensity. In addition, since the TMS magnetic stimulation coil interferes with the ultrasonic transducer, a filter is added to the ultrasonic transducer to filter out the interference signal generated by the TMS magnetic stimulation coil on the ultrasonic transducer, so that when corresponding stimulation is performed on the patient, the stimulation signal will not have spikes, affecting the stimulation effect.

[0023] It should be understood that the content described in this part is not intended to identify the key or important features of the embodiments of the present invention, nor is it used to limit the scope of the present invention. Other features of the present invention will become easily understood through the following description. BRIEF DESCRIPTION OF THE DRAWINGS

[0024] In order to more clearly illustrate the technical solutions in the embodiments of the present invention, the following will briefly introduce the drawings required for the description of the embodiments. Obviously, the drawings in the following description are only some embodiments of the present invention. For those of ordinary skill in the art, without creative efforts, other drawings can be obtained based on these drawings.

[0025] Figure 1 is a block diagram of the transcranial M-TMAS stimulation device according to an embodiment of the present invention;

[0026] Figure 2 is a schematic structural diagram of the transcranial M-TMAS stimulation device according to an embodiment of the present invention;

[0027] Figure 3 is a block diagram of the ultrasonic transducer excitation source in the transcranial M-TMAS stimulation device according to an embodiment of the present invention;

[0028] Figure 4It is a block diagram of an ultrasonic transducer excitation source in a transcranial M-TMAS stimulation device proposed in an embodiment of the present invention;

[0029] Figure 5 It is a circuit schematic diagram of an ultrasonic transducer excitation source in a transcranial M-TMAS stimulation device proposed in an embodiment of the present invention;

[0030] Figure 6 It is a block diagram of an ultrasonic transducer excitation source in a transcranial M-TMAS stimulation device proposed in another embodiment of the present invention;

[0031] Figure 7 It is a circuit schematic diagram of a fundamental frequency control circuit in an ultrasonic transducer excitation source in a transcranial M-TMAS stimulation device proposed in another embodiment of the present invention;

[0032] Figure 8 It is a block diagram of an ultrasonic transducer excitation source in a transcranial M-TMAS stimulation device proposed in another embodiment of the present invention;

[0033] Figure 9 It is a circuit schematic diagram of a power amplification module in an ultrasonic transducer excitation source in a transcranial M-TMAS stimulation device proposed in another embodiment of the present invention. Detailed implementation manners

[0034] In order to enable those skilled in the art to better understand the solution of the present invention, the technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present invention. Obviously, the described embodiments are only a part of the embodiments of the present invention, rather than all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those of ordinary skill in the art without creative efforts shall fall within the protection scope of the present invention.

[0035] It should be noted that the terms "first", "second", etc. in the specification and claims of the present invention and the above-mentioned drawings are used to distinguish similar objects, and do not necessarily need to describe a specific order or sequence. It should be understood that such data can be interchanged under appropriate circumstances so that the embodiments of the present invention described here can be implemented in an order different from those illustrated or described here. In addition, the terms "comprising" and "having" and any variations thereof are intended to cover non-exclusive inclusion. For example, a process, method, system, product or device that includes a series of steps or units does not necessarily have to be limited to those steps or units clearly listed, but may include other steps or units not clearly listed or inherent to these processes, methods, products or devices.

[0036] Figure 1 It is a block diagram of a transcranial M-TMAS stimulation device proposed in an embodiment of the present invention. AsFigure 1 As shown, the device includes:

[0037] A phased array ultrasonic transducer 201, a TMS magnetic stimulation coil 205, an ultrasonic transducer excitation source 202, a TMS magnetic stimulation excitation source 204, and a controller 203; the controller 203 is respectively connected to the ultrasonic transducer excitation source 202 and the TMS magnetic stimulation excitation source 204, and is used to control the ultrasonic transducer excitation source 202 to send out an ultrasonic excitation signal to the phased array ultrasonic transducer 201, and the phased array ultrasonic transducer 201 forms a focused sound field based on the ultrasonic excitation signal; it is also used to control the TMS magnetic stimulation excitation source 204 to send out an alternating current excitation signal to the TMS magnetic stimulation coil 205, and the TMS magnetic stimulation coil 205 forms an alternating magnetic field based on the alternating current excitation signal; the focused sound field and the alternating magnetic field are coupled to form a magnetoacoustic coupled electric field, and the alternating magnetic field also generates an alternating electric field; the magnetoacoustic coupled electric field, the alternating electric field, and the focused sound field act on the patient together; wherein, a filter 206 is provided in the ultrasonic transducer excitation source 202, which is used to filter out the interference signal generated by the TMS magnetic stimulation coil 205 on the phased array ultrasonic transducer 201.

[0038] It can be understood that, in combination with Figure 1 and Figure 2 as shown, the controller 203 can be a PC or an industrial control computer. By adjusting the pulse excitation parameters of each channel of the TMS magnetic stimulation coil 205 and the phased array ultrasonic transducer 201 through the PC / industrial control computer, a focused ultrasonic pulse signal with adjustable focal length and focal point position can be emitted by the transducer, and a corresponding induced electric field can be generated by the TMS magnetic stimulation coil 205. By adjusting the fixing device of the TMS magnetic stimulation coil 205 and the bracket of the phased array ultrasonic transducer 201, the relative position between the TMS magnetic stimulation coil 205 and the phased array ultrasonic transducer 201 can be adjusted, which can ensure that the focused sound field V and the alternating magnetic field B are perpendicular to each other and are in the same spatial position. At this time, a magnetoacoustic coupled electric field can be generated in the direction of the vector product of the focused sound field and the alternating magnetic field, which is E MA . At this time, the alternating coil will also generate a magnetic induction electric field E M in the target area to be stimulated. E M and E MA are in the same direction, and the intensities are superimposed to form a composite physical field E M +E MA in the same direction in the target area, further enhancing the intensity of the stimulating electric field; plus the original orthogonal focused ultrasonic field V, a focused composite field stimulation of a magnetoacoustic electric field, a magnetic induction electric field, and a focused sound field can be generated in the brain target area. Thus, the stimulation intensity is enhanced.

[0039] Among them, the AC excitation signal is an alternating current signal. After passing through the magnetic stimulation coil, the alternating current signal can generate an alternating magnetic field, and the alternating magnetic field generates an alternating induced electric field. Since the alternating magnetic field generated by the magnetic stimulation coil is likely to interfere with the ultrasonic transducer 201, a filter is provided in the ultrasonic transducer excitation source 202 to filter out the clutter generated by the magnetic field on the ultrasonic excitation signal, so that the ultrasonic transducer 201 can work normally.

[0040] The generation of the ultrasonic excitation signal and the processing process of the ultrasonic excitation signal will be introduced below. Optionally, as Figure 3 shown, the ultrasonic transducer excitation source 202 includes:

[0041] FPGA focusing delay module 102, I / O channel expansion module 103, multiple fundamental frequency control circuits 104, multiple LC oscillation circuits 105, multiple low-pass filters 2061, and the fundamental frequency control circuits 104, LC oscillation circuits 105, and low-pass filters 206 are in one-to-one correspondence;

[0042] The controller 203 is used to provide the focusing excitation parameters of each channel of the phased array ultrasonic transducer 201. The FPGA focusing delay module 102 is used to calculate the focusing delay data of each channel according to the focusing excitation parameters of each channel, and output the PWM wave carrying the focusing delay data corresponding to each channel in combination with the focusing delay data of each channel. The PWM wave carrying the focusing delay data corresponding to each channel is input into the corresponding fundamental frequency control circuit 104 through the I / O channel expansion module 103. Each LC oscillation circuit 105 oscillates the DC source signal into a sine wave signal according to the fundamental frequency signal output by the fundamental frequency control circuit 104. After the low-pass filter 2061 filters the sine wave signal, it is output to the corresponding channel of the phased array ultrasonic transducer 201.

[0043] It can be understood that the focusing excitation parameters of each channel of the phased array ultrasonic transducer, such as the number of excitation array elements, the width of the array elements, the spacing between the array elements, and the ultrasonic propagation medium for excitation, are controlled by the PC using the Quartus_Prime software. The FPGA focusing delay module 102 calculates the focusing delay data of each channel according to the focusing excitation parameters of each channel, and outputs PWM waves carrying the focusing delay data corresponding to each channel in combination with the focusing delay data of each channel. The PWM waves corresponding to each channel control the corresponding fundamental frequency control circuit 104 to output a fundamental frequency signal to the corresponding LC oscillation circuit 105, so that the LC oscillation circuit 105 oscillates the DC source signal into a sine wave signal based on the fundamental frequency signal and outputs it to the low-pass filter 2061. After being filtered by the low-pass filter 2061, it is output to the corresponding channel of the phased array ultrasonic transducer 201 for each array element to work. Using this excitation system can excite a sine wave with a high amplitude. Since the sine wave has zero high-frequency components, it can reduce the load heating and the vibration loss of the piezoelectric ceramic, and can significantly improve the service life of the phased array ultrasonic transducer.

[0044] It should be noted that the PWM wave output by the FPGA focusing delay module 102 only controls the fundamental frequency control circuit 104 to output a fundamental frequency signal to the corresponding LC oscillation circuit 105, so that the LC oscillation circuit 105 oscillates the DC source signal into a sine wave signal. The PWM wave not only carries the focusing delay information, but also can control the duty cycle of the excitation pulse of the phased array ultrasonic transducer. The main frequency of this module can reach 250 MHz, and it supports a maximum delay accuracy of 4 ns, and can accurately modulate the excitation waveform.

[0045] Optionally, as Figure 4 shown, the fundamental frequency control circuit 104 includes:

[0046] An optocoupler circuit unit 107, a NAND gate circuit unit 108, a crystal oscillator unit 109, a MOS transistor control unit 110, and a MOS transistor 111. The input end of the optocoupler circuit unit 107 is connected to the I / O channel expansion module 103, the output end of the optocoupler circuit unit 107 is connected to the input end of the NAND gate circuit unit 108, the output end of the crystal oscillator unit 109 is connected to the input end of the NAND gate circuit unit 108, the output end of the NAND gate circuit unit 108 is connected to the MOS transistor control unit 110, and the MOS transistor 111 is in an open state or a closed state according to the level signal output by the MOS transistor control unit 110 to provide a fundamental frequency signal for the LC oscillation circuit 105.

[0047] It should be noted that after the crystal oscillator unit 109 receives external pressure, it generates an electrical signal, that is, a fundamental frequency signal. The optocoupler circuit unit 107 receives the PWM signal output by the FPGA focusing delay module 102. The optocoupler in the optocoupler circuit unit 107 is in a conducting state or a disconnected state according to the level signal of the PWM wave, that is, the state of "0 or 1" is input to the input terminal of the NAND gate circuit unit 108. The state of the fundamental frequency signal "1" generated by the crystal oscillator unit 109 is input to the input terminal of the NAND gate circuit unit 108. Since the output terminal of the NAND gate circuit unit 108 is connected to the control terminal of the MOS transistor control unit 110, the signal output by the optocoupler circuit unit 107 controlled by the PWM signal and the fundamental frequency signal generated by the crystal oscillator unit 109 pass through the NAND gate circuit unit 108 and then output a control signal to the control terminal of the MOS transistor control unit 110. When the MOS transistor is turned on, a fundamental frequency signal is provided to the LC oscillation circuit 105. Among them, the circuit for generating the fundamental frequency signal can refer to the circuit Figure 5 。

[0048] Continue to refer to Figure 5 As shown in the figure, the optocoupler circuit unit 107 includes: a first power supply chip 112, an optocoupler 113, and a first capacitor C1. The first terminal 1 and the second terminal 2 of the optocoupler 113 respectively input PWM wave signals. The third terminal 3 of the optocoupler 113 is connected to the output terminal of the first power supply chip 112. The fourth terminal 4 of the optocoupler 113 is grounded. The fifth terminal 5 of the optocoupler 113 is connected to the NAND gate circuit unit 108. The first power supply chip 112 supplies power to the optocoupler 113. The output terminal of the first power supply chip 112 is also connected to one end of the first capacitor C1, and the other end of the first capacitor C1 is grounded.

[0049] Among them, the first power supply chip 112 supplies power to the optocoupler 113. When the first terminal 1 of the optocoupler 113 inputs a high level and the second terminal 2 inputs a low level, the optocoupler 113 conducts. Conversely, when the first terminal 1 of the optocoupler 113 inputs a low level and the second terminal 2 inputs a high level, the optocoupler 113 disconnects. That is to say, the PWM waves input to the first terminal 1 and the second terminal 2 of the optocoupler 113 differ by half a cycle. When the optocoupler 113 conducts, the fifth terminal 5 of the optocoupler 113 outputs a high level. When the optocoupler 113 disconnects, the fifth terminal 5 of the optocoupler 113 outputs a low level.

[0050] The NAND gate circuit unit 108 includes: a first NAND gate 114, a second NAND gate 115, a third NAND gate 116, and a first resistor R1. The first input terminal 1 of the first NAND gate 114 is connected to one end of the first resistor R1, and the other end of the first resistor R1 is connected to the second power supply VDD2. The first input terminal 1 of the first NAND gate 114 is connected to the second input terminal 2. The second input terminal 2 of the first NAND gate 114 is connected to the fifth terminal 5 of the optocoupler 113;

[0051] The output terminal 3 of the first NAND gate 114 is connected to the first input terminal 1 of the second NAND gate 115. The second input terminal 2 of the second NAND gate 115 is connected to the crystal oscillator unit 109. The output terminal 3 of the second NAND gate 115 is respectively connected to the first input terminal 1 and the second input terminal 2 of the third NAND gate 116. The output terminal 3 of the third NAND gate 116 is connected to the input terminal of the MOS transistor control unit 110.

[0052] Among them, when the optocoupler 113 is turned on, the fifth terminal 5 of the optocoupler 113 outputs a high level, which is then input to the second input terminal 2 of the first NAND gate 114. Both the first input terminal 1 and the second input terminal 2 of the first NAND gate 114 are at a high level, and thus the output terminal 3 of the first NAND gate 114 outputs a low level. When the optocoupler 113 is turned off, the fifth terminal 5 of the optocoupler 113 outputs a low level, which is then input to the second input terminal 2 of the first NAND gate 114. Both the first input terminal 1 and the second input terminal 2 of the first NAND gate 114 are at a low level. At this time, the output terminal 3 of the first NAND gate 114 outputs a high level.

[0053] When the output terminal 3 of the first NAND gate 114 is at a high level, that is, the first input terminal 1 of the second NAND gate 115 is at a high level. If the second input terminal 2 of the second NAND gate 115 is at a low level, then the output terminal 3 of the second NAND gate 115 is at a high level; if the second input terminal 2 of the second NAND gate 115 is at a high level, then the output terminal 3 of the second NAND gate 115 is at a low level.

[0054] When the output terminal 3 of the first NAND gate 114 is at a low level, that is, the first input terminal 1 of the second NAND gate 115 is at a low level. If the second input terminal 2 of the second NAND gate 115 is at a low level, then the output terminal 3 of the second NAND gate 115 is at a high level; if the second input terminal 2 of the second NAND gate 115 is at a high level, then the output terminal 3 of the second NAND gate 115 is at a high level.

[0055] When the output terminal 3 of the second NAND gate 115 is at a high level, both the first input terminal 1 and the second input terminal 2 of the third NAND gate 116 are at a high level, then the output terminal 3 of the third NAND gate 116 is at a low level. When the output terminal 3 of the second NAND gate 115 is at a low level, both the first input terminal 1 and the second input terminal 2 of the third NAND gate 116 are at a low level, then the output terminal 3 of the third NAND gate 116 is at a high level.

[0056] Continue to refer to Figure 5, the crystal oscillator unit 109 includes: a fourth NAND gate 117, a second resistor R2, a third resistor R3, a second capacitor C2, a third capacitor C3, and a fourth capacitor C4. One ends of the second capacitor C2 and the third capacitor C3 are both grounded. The other end of the second capacitor C2 is connected to one end of the fourth capacitor C4. The other end of the third capacitor C3 is connected to the other end of the fourth capacitor C4. The other end of the fourth capacitor C4 is also connected to one end of the second resistor R2. The other end of the second resistor R2 is connected to the output terminal 3 of the fourth NAND gate 117. One end of the fourth capacitor C4 is also connected to the first input terminal 1 and the second input terminal 2 of the fourth NAND gate 117. One end of the third resistor R3 is connected to the first input terminal 1 and the second input terminal 2 of the fourth NAND gate 117. The other end of the third resistor R3 is connected to the output terminal 3 of the fourth NAND gate 117. The output terminal of the fourth NAND gate is connected to the second input terminal 2 of the second NAND gate 115.

[0057] Among them, when charging the second capacitor C2, the third capacitor C3, and the fourth capacitor C4, both the first input terminal 1 and the second input terminal 2 of the fourth NAND gate 117 are at high level, and the output terminal 3 is at low level; when the second capacitor C2, the third capacitor C3, and the fourth capacitor C4 are fully charged, both the first input terminal 1 and the second input terminal 2 of the fourth NAND gate 117 are at low level, and the output terminal 3 is at high level; when the second capacitor C2, the third capacitor C3, and the fourth capacitor C4 are fully charged and start to discharge, both the first input terminal 1 and the second input terminal 2 of the fourth NAND gate 117 are at high level, and the output terminal 3 is at low level.

[0058] Continue to refer to Figure 5 , the MOS transistor control unit 110 includes: a fourth resistor R4, a fifth resistor R5, a sixth resistor R6, a fifth capacitor C5, a sixth capacitor C6, a first switching transistor Q1, and a second switching transistor Q2. Among them, one end of the parallel connection of the fourth resistor R4 and the fifth capacitor C5 is connected to the output terminal 3 of the third NAND gate 116, and the other end is respectively connected to the control terminals of the first switching transistor Q1 and the second switching transistor Q2. The source of the first switching transistor Q1 is connected to the third power supply VDD3 and one end of the sixth capacitor C6. The other end of the sixth capacitor C6 is grounded. The drain of the first switching transistor Q1 is respectively connected to the drain of the second switching transistor Q2 and one end of the fifth resistor R5. The source of the second switching transistor Q2 is grounded. The other end of the fifth resistor R5 is respectively connected to the control terminal of the MOS transistor 111 and one end of the sixth resistor R6. The other end of the sixth resistor R6 is grounded.

[0059] Among them, the first switching transistor Q1 is an NPN transistor, the second switching transistor Q2 is a PNP transistor, and the MOS transistor 111 is an NMOS transistor. When the output terminal 3 of the third NAND gate 116 outputs a high level, the first switching transistor Q1 is turned on, the second switching transistor Q2 is turned off, and the MOS transistor 111 is turned on. When the output terminal 3 of the third NAND gate 116 outputs a low level, the first switching transistor Q1 is turned off, the second switching transistor Q2 is turned off, and the MOS transistor 111 is turned off.

[0060] Continue to refer to Figure 5 , the LC oscillation circuit 105 includes: a first LC oscillation circuit unit and a second LC oscillation circuit unit. The input terminal of the first LC oscillation circuit unit is used to input a DC source signal. The output terminal of the first LC oscillation circuit is respectively connected to the input terminal of the second LC oscillation circuit and the second terminal of the MOS transistor 111. The third terminal of the MOS transistor 111 is grounded. The output terminal of the second LC oscillation circuit is connected to the input terminal of the low-pass filter 206. The output terminal of the low-pass filter 206 is connected to the corresponding array element of the phased array ultrasonic transducer 201.

[0061] Continue to refer to Figure 5, the first LC oscillation circuit unit includes: a Wheatstone bridge 118, a seventh capacitor C7, an eighth capacitor C8, a ninth capacitor C9, a seventh resistor R7, a first inductor L1, and a first diode D1. The first terminal 1 and the second terminal 2 of the Wheatstone bridge 118 are respectively connected to a DC source signal. The fourth terminal 4 of the Wheatstone bridge 118 is grounded. The third terminal 3 of the Wheatstone bridge 118 is respectively connected to one end of the seventh capacitor C7 and one end of the seventh resistor R7. The other end of the seventh capacitor C7 is grounded. The other end of the seventh resistor R7 is respectively connected to the fourth power supply VCC and the cathode of the first diode D1. The anode of the first diode D1 is connected to the first terminal 1 of the first inductor L1. The second terminal 2 of the first inductor L1 is grounded. The third terminal 3 of the first inductor L1 is respectively connected to one end of the eighth capacitor C8 and one end of the seventh capacitor C7. The other end of the eighth capacitor C8 is grounded. The fourth terminal 4 of the first inductor L4 is respectively connected to one end of the ninth capacitor C9 and the second LC oscillation circuit unit. The other end of the ninth capacitor C9 is grounded. The second LC oscillation circuit unit includes: a tenth capacitor C10, an eleventh capacitor C11, a twelfth capacitor C12, a thirteenth capacitor C13, a fourteenth capacitor C14, an eighth resistor R8, a ninth resistor R9, a tenth resistor R10, a second inductor L2, and a second diode D2. One end of the tenth capacitor C10 is connected to the other end of the ninth capacitor C9. The other end of the tenth capacitor C10 is connected to the first terminal 1 of the second inductor L2. The second terminal 2 of the second inductor L2 is connected to the anode of the second diode D2. The cathode of the second diode D2 is connected to one end of the eighth resistor R8. The other end of the eighth resistor R8 is connected to the end where the ninth resistor R9 and the eleventh capacitor C11 are in parallel. The other end where the ninth resistor R9 and the eleventh capacitor C11 are in parallel is connected to the third terminal 3 of the second inductor L2. The fourth terminal 4 of the second inductor L2 is respectively connected to one end of the twelfth capacitor C12. The other end of the twelfth capacitor C12 is connected to one end of the thirteenth capacitor C13. The other end of the twelfth capacitor C12 is grounded. The other end of the thirteenth capacitor C13 is connected to one end of the tenth resistor R10. One end of the tenth resistor R10 is grounded. The other end of the tenth resistor R10 is connected to the other end where the ninth resistor R9 and the eleventh capacitor C11 are in parallel. The fourth terminal 4 of the second inductor L2 is also connected to one end of the fourteenth capacitor C14. The other end of the fourteenth capacitor C14 is grounded. One end of the fourteenth capacitor C14 is connected to the phased array ultrasonic transducer 106.

[0062] Among them, the MOS transistor 111 is turned on at a high level, making the potential of the connection point v between the first LC oscillation circuit unit and the second LC oscillation circuit unit zero. At this time, there are currents in both the first inductor L1 and the second inductor L2, and their values are equal to the current passing through the MOS transistor 111, which plays a role in protecting the MOS transistor 111 from being burned out. After the MOS transistor 111 is turned on, the LC oscillation circuit 105 is equivalent to a parallel resonance.

[0063] When the MOS transistor 111 is at a low level, it is turned off, making the potential of the connection point v between the first LC oscillation circuit unit and the second LC oscillation circuit unit non-zero. After the MOS transistor 111 is turned off, the LC oscillation circuit 105 is equivalent to a series resonance. Then, a sine wave with a high amplitude is output.

[0064] The detailed derivation process is as follows:

[0065] When the MOS transistor is turned on, v is zero, and the first LC oscillation circuit unit and the second LC oscillation circuit unit are in parallel. At this time, That is to say, That is to say,

[0066] When the MOS transistor is turned off, the first LC oscillation circuit unit and the second LC oscillation circuit unit are in series. At this time,

[0067]

[0068] Among them, according to the volt-second balance condition, ΔI1 = ΔI2 = ΔI.

[0069] Since, Also because So,

[0070] Furthermore, t on = t off , and because t on + t off = T, so t on = t off = ΔT. Therefore, Also because Furthermore, v = 2v in .

[0071] Furthermore, when the MOS transistor is turned off, it is input with the original amplitude of 2v in , thereby increasing the amplitude of the finally output sine wave, and the amplitude is about ±200V.

[0072] The first terminal 1 and the second terminal 2 of the signal output device 119 output a DC source signal, the third terminal 3 and the fourth terminal 4 output a PWM wave, the fifth terminal 5 and the sixth terminal 6 are floating, that is, no signal is connected. When the first terminal 1 of the optocoupler 113 inputs a high level and the second terminal 2 inputs a low level, the optocoupler 113 conducts, and the fifth terminal 5 of the optocoupler outputs a high level. The first input terminal 1 and the second input terminal 2 of the first NAND gate 114 are both at a high level, and the output terminal 3 outputs a low level. The first input terminal 1 of the second NAND gate 115 is at a low level. At this time, regardless of whether the output terminal 3 of the fourth NAND gate 117 in the crystal oscillator unit 109 outputs a high level or a low level, the output terminal 3 of the second NAND gate 115 is at a high level. The first input terminal 1 and the second input terminal 2 of the third NAND gate are both at a high level, and the output terminal 3 is at a low level. At this time, the second switching transistor Q2 conducts, the first switching transistor Q1 is turned off, the MOS transistor 111 is turned off, and the first LC oscillation circuit unit and the second LC oscillation circuit unit are connected in series.

[0073] When the first terminal 1 of the optocoupler 113 inputs a low level and the second terminal 2 inputs a high level, the optocoupler 113 is turned off, and the fifth terminal 5 of the optocoupler outputs a low level. The first input terminal 1 and the second input terminal 2 of the first NAND gate 114 are both at a low level, and the output terminal 3 outputs a high level. The first input terminal 1 of the second NAND gate 115 is at a high level. At this time, when the output terminal 3 of the fourth NAND gate 117 in the crystal oscillator unit 109 outputs a high level, the output terminal 3 of the second NAND gate 115 is at a low level. The first input terminal 1 and the second input terminal 2 of the third NAND gate are both at a low level, and the output terminal 3 is at a high level. At this time, the second switching transistor Q2 is turned off, the first switching transistor Q1 conducts, the MOS transistor 111 conducts, and the first LC oscillation circuit unit and the second LC oscillation circuit unit are connected in parallel. When the output terminal 3 of the fourth NAND gate 117 in the crystal oscillator unit 109 outputs a low level, the output terminal 3 of the second NAND gate 115 is at a high level. The first input terminal 1 and the second input terminal 2 of the third NAND gate are both at a high level, and the output terminal 3 is at a low level. At this time, the second switching transistor Q2 conducts, the first switching transistor Q1 is turned off, the MOS transistor 111 is turned off, and the first LC oscillation circuit unit and the second LC oscillation circuit unit are connected in series.

[0074] Generally speaking, when the optocoupler 113 is turned on, regardless of whether the crystal oscillator unit 109 outputs a fundamental frequency signal, the MOS transistor 111 is in the off state; when the optocoupler 113 is turned off, the MOS transistor 111 is in the on state only when the crystal oscillator unit 109 outputs a fundamental frequency signal, and at other times, the MOS transistor 111 is in the off state. Thus, the on and off states of the optocoupler 113 and the fundamental frequency signal output by the crystal oscillator unit 109 determine whether the MOS transistor 111 is turned on. The optocoupler 113 functions as a switch in this circuit system. When the optocoupler 113 is turned on, since the LC oscillation circuit 105 does not receive the fundamental frequency signal, it does not perform the work of oscillating sinusoidally. In other words, the entire system is in a non-operating state. When the optocoupler 113 is turned off, when the LC oscillation circuit 105 receives the fundamental frequency signal, that is, when the MOS transistor is turned on, it does not oscillate sinusoidally. After the LC oscillation circuit 105 receives the fundamental frequency signal, that is, after the MOS transistor is turned on and then off, it oscillates sinusoidally. That is to say, the PWM wave output by the FPGA focusing delay module 102 only controls the on and off states of the optocoupler 113.

[0075] Since the input signal of the LC oscillation circuit 105 is a DC source signal, the amplitude is higher than that of the square wave signal in the prior art. The traditional phased array ultrasonic transducer can provide a high-frequency sinusoidal excitation with an amplitude of ±20 to ±50V and a square wave excitation of ±100V, while the sinusoidal wave excited by this system is a high-frequency sinusoid of ±200V, and the power is 16 times that of the traditional excitation source.

[0076] It should be noted that the fundamental frequency control circuit 104 and the LC oscillation circuit 105 also include a voltage stabilizing circuit unit 120, as Figure 5 shown. The voltage stabilizing circuit unit 120 includes a fifteenth capacitor C15, a sixteenth capacitor C16, a seventeenth capacitor C17, and a voltage regulator 121. Thus, the first excitation signal is a high-amplitude signal with zero high-frequency components, which can reduce the load heating and the vibration loss of the piezoelectric ceramic, and can significantly improve the service life of the phased array ultrasonic transducer.

[0077] Optionally, continue to refer to Figure 5, the low-pass filter 206 includes: a first capacitor C1, a second capacitor C2, a third capacitor C3, a first resistor R1, a second resistor R2, a third resistor R3, and a comparator. The output terminal of the LC oscillation circuit 105 is connected to one end of the first capacitor C1. The other end of the first capacitor C1 is respectively connected to one end of the second capacitor C2, one end of the first resistor R1, and one end of the third capacitor C3. The other end of the first resistor R1 is grounded. The other end of the second capacitor C2 and the other end of the first resistor R1 are commonly connected to the first input terminal of the comparator. The other end of the third capacitor C3 and the other end of the second resistor R2 are connected to the output terminal of the comparator. One end of the third resistor R3 is connected to the second input terminal of the comparator. Thus, the signal output by the LC oscillation circuit 105 can be filtered by the low-pass filter 206 to output a smooth excitation signal to excite the phased array ultrasonic transducer 201. This can avoid the influence of the magnetic field generated by the magnetic stimulation magnetic ring on the function of the phased array ultrasonic transducer 201. Thus, a high-amplitude excitation signal can be obtained through this excitation source.

[0078] In another embodiment, as Figure 6 shown, the ultrasonic transducer excitation source 202 includes:

[0079] a focusing delay module 302, a DDS signal generation module 303, a plurality of first-stage operational amplifier modules 304, a plurality of second-stage power amplifier modules 305, and a plurality of band-pass filters 2062. The first-stage operational amplifier modules 304 and the second-stage power amplifier modules 305 are correspondingly arranged, and the second-stage power amplifier modules 305 are corresponding to two band-pass filters 2062;

[0080] The controller 203 is used to provide the focusing excitation parameters of each channel of the phased array ultrasonic transducer 201. The focusing delay module 302 is used to obtain the focusing delay data corresponding to the focusing excitation parameters of each channel according to the focusing excitation parameters of each channel. The DDS signal generation module 303 emits a first excitation signal to each element of the phased array ultrasonic transducer 201 according to the focusing delay data of each channel. The first-stage operational amplifier module 304 is used to form two second excitation signals with the same amplitude and opposite phases from the first excitation signal. The second-stage power amplifier module 305 is used to perform power amplification on the two second excitation signals with the same amplitude and opposite phases and then output them to the corresponding band-pass filters 2062. After being filtered by the band-pass filters 2062, they are output to the corresponding channels of the phased array ultrasonic transducer 201.

[0081] It can be understood that the DDS signal generation module 303 has extremely high phase accuracy and waveform accuracy, and other waveforms can also be input to it in a programming manner for various waveform requirements to excite the ultrasonic phased array transducer. The output accuracy of other waveforms completely depends on the waveform accuracy stored by the user himself.

[0082] Among them, the DDS signal generation module 303 can output a first excitation signal, that is, the first excitation signal can be any one of a sine wave excitation signal, a square wave excitation signal, a triangular wave excitation signal, a Gaussian pulse excitation signal, a stepped wave excitation signal, and a bell-shaped wave excitation signal. It should be noted that the following content will be described by taking the DDS signal generation module 303 generating a sine wave excitation signal as an example.

[0083] The controller 203 can use the Keil uVersion5 software to control the focusing excitation parameters of each channel of the phased array ultrasonic transducer 201. Among them, the focusing excitation parameters can be parameters such as the number of excitation array elements, the element width, the element spacing, and the excitation ultrasonic propagation medium. After the focusing excitation parameters are determined, the focusing delay module 302 can obtain the focusing delay data corresponding to the focusing excitation parameters of each channel according to the focusing excitation parameters of each channel, and send the focusing delay data to the DDS signal generation module 303. The DDS signal generation module 303 transmits the first excitation signal carrying the delay data to each channel according to the focusing delay data corresponding to the focusing excitation parameters of each channel. The first excitation signal forms two second excitation signals with the same amplitude and opposite phases after passing through the first-stage operational amplifier module 304. The two second excitation signals with the same amplitude and opposite phases are power-amplified by the second-stage power amplifier module 305 and then output to the corresponding channels of the phased array ultrasonic transducer 201.

[0084] Based on this, the ultrasonic transducer generally uses a 64-element focusing transducer or a phased array focusing ultrasonic transducer, and the main frequency generally uses 100k~1MHz, and the frequency is selected based on the stimulation depth of the object to be measured. The STM32H743 single-chip microcomputer is used to calculate the focusing delay to obtain the corresponding focusing delay data. The main frequency of this module can reach 500MHz, and it supports a maximum delay accuracy of 2ns. After outputting the delay data, it is then separately transmitted for each channel through the DDS signal generation module 303. The DDS signal generation module 303 can support a maximum phase delay transmission of π / 8192 cycles. The number of sine channels transmitted by the DDS signal generation module 303 is the same as the number of transducer array elements to ensure that each channel can independently excite each element. The multi-channel high-frequency sine excitation with delay transmitted by the DDS signal generation module 303 will each pass through the first-stage operational amplifier module 304, providing two groups of sine signals with the same frequency, the same amplitude, and a phase difference of half a cycle for the second-stage power amplifier module 305, making the signal frequency finally output by the second-stage power amplifier module 305 more accurate.

[0085] Optionally, as Figure 7As shown in the figure, the first-stage operational amplification module 304 includes: a DC-blocking and AC-coupling unit 307 and an operational amplifier unit 308; the input end of the DC-blocking and AC-coupling unit 307 is connected to the output end of the DDS signal generation module 303, and is used to convert the first excitation signal into an AC signal; the input end of the operational amplifier unit 308 is connected to the output end of the DC-blocking and AC-coupling unit 307, and is used to convert the AC signal into two second excitation signals with the same amplitude and opposite phases.

[0086] Continue to refer to Figure 7 , the DC-blocking and AC-coupling unit 307 includes: a first resistor R1, a first capacitor C1, and a potentiometer RPI. One end of the first resistor R1 is connected to the output end of the DDS signal generation module 303, and the other end is grounded; one end of the first capacitor C1 is connected to one end of the first resistor R1, and the other end is connected to the sixth end of the potentiometer RPI. The fourth end of the potentiometer RPI is grounded, and the fifth end of the potentiometer RPI is connected to the input end of the operational amplifier unit 308.

[0087] For example, if the first excitation signal output by the DDS signal generation module 303 is a 0-220 mV sine signal, then it is converted into a ±110 mV AC sine signal after passing through the DC-blocking and AC-coupling unit 307. Among them, the function of the potentiometer RPI is to make the amplification factor of the operational amplifier unit 308 adjustable. The function of the first capacitor C1 is to block DC and couple AC.

[0088] Continue to refer to Figure 7 , the operational amplifier unit 308 includes: a first amplifier 309, a second amplifier 310, a third amplifier 311, a second resistor R2, a third resistor R3, a fourth resistor R4, a fifth resistor R5, a sixth resistor R6, a seventh resistor R7, an eighth resistor R8, a ninth resistor R9, and a tenth resistor R10; the positive input end of the first amplifier 309 is connected to the output end of the DC-blocking and AC-coupling unit 307, and the negative input end is connected to one end of the second resistor R2. The other end of the second resistor R2 is grounded; the output end of the first amplifier 309 is respectively connected to one end of the third resistor R3 and one end of the fourth resistor R4. One end of the third resistor R3 is connected to one end of the second resistor R2;

[0089] The other end of the fourth resistor R4 is connected to the positive input end of the second amplifier 310. The negative input end of the second amplifier 110 is respectively connected to one end of the fifth resistor R5 and one end of the sixth resistor R6. The other end of the fifth resistor R5 is grounded, and the other end of the sixth resistor R6 is connected to the output end of the second amplifier 310. The output end of the second amplifier 310 is also connected to one end of the seventh resistor R7. The other end of the seventh resistor R7 is connected to the first input end (P3 SMA) of the second-stage power amplification module 305;

[0090] The output terminal of the first amplifier 309 is also connected to one end of the eighth resistor R8. The other end of the eighth resistor R8 is respectively connected to one end of the ninth resistor R9 and the inverting input terminal of the third amplifier 111. The non-inverting input terminal of the third amplifier 311 is grounded. The other end of the ninth resistor R9 is connected to the output terminal of the third amplifier 311. The output terminal of the third amplifier 311 is also connected to one end of the tenth resistor R10. The other end of the tenth resistor R10 is connected to the second input terminal (P4SMA) of the secondary power amplification module 305.

[0091] It should be noted that since the amplitude of the first excitation signal output by the DDS signal generation module 303 (such as 220 mVpp) is relatively low, while the amplitude of the finally actual required waveform is relatively high (such as 110 V), and the single-phase amplitude of the first excitation signal will become 110 mV after passing through the DC-blocking and AC-coupling unit 307. Due to the insufficient bandwidth product of the existing amplifiers, it is necessary to set the first amplifier 309, the second amplifier 310, and the third amplifier 311. Thus, the first excitation signal is amplified once after passing through the first amplifier 309, and then amplified once after passing through the second amplifier 310 or the third amplifier 311, and finally input into the secondary power amplification module 305 to meet the final amplitude requirement and prevent signal distortion.

[0092] Continue to refer to Figure 7 , the operational amplifier unit 308 further includes a thirteenth capacitor C13, a fourteenth capacitor C14, a fifteenth capacitor C15, a sixteenth capacitor C16, a seventeenth capacitor C17, and an eighteenth capacitor C18.

[0093] Continue to refer to Figure 7 , the first-stage operational amplification module 104 further includes a power supply module. The power supply module includes a Wheatstone bridge 320, a nineteenth capacitor C19, a twentieth capacitor C20, a twenty-first capacitor C21, a twenty-second capacitor C22, a twenty-third capacitor C23, a twenty-fourth capacitor C24, a twenty-fifth capacitor C25, and a twenty-sixth capacitor C26, a twenty-eighth resistor R28 and a twenty-ninth resistor R29, as well as a first power supply chip 321 and a second power supply chip 322.

[0094] Optionally, refer to Figure 8, the secondary power amplification module 305 includes: a first secondary power amplification unit 3051 and a second secondary power amplification unit 3052. The input end of the first secondary power amplification unit 3051 is connected to the first output end of the primary operational amplification module 304, and the output end is connected to the input end of the band-pass filter 2062. The output end of the band-pass filter 2062 is connected to one end of the phased array ultrasonic transducer 201. The input end of the second secondary power amplification unit 3052 is connected to the second output end of the primary operational amplification module 304, and the output end is connected to the input end of the band-pass filter 2062. The output end of the band-pass filter 2062 is connected to the other end of the phased array ultrasonic transducer 201.

[0095] Optionally, as Figure 9 shown, both the first secondary power amplification unit 3051 and the second secondary power amplification unit 3052 include an input stage circuit 312, an excitation stage circuit 313, and an output stage circuit 314. The input end of the input stage circuit 312 is connected to one of the output ends of the primary operational amplification module 304, and is used to suppress the zero drift of the second excitation signal. The excitation stage circuit 313 is used to compensate for the zero-crossing distortion of the second excitation signal. The output stage circuit 314 is used to amplify the excitation signal processed by the input stage circuit 312 and the excitation stage circuit 313, and output it to the band-pass filter 2062. After being filtered by the band-pass filter 2062, it is output to the phased array ultrasonic transducer 201. The excitation stage circuit 313 includes: a first voltage stabilizing circuit 315, a second constant current source 316, a first constant voltage source 317, a second voltage stabilizing circuit 318, and a tube vibration elimination circuit 319.

[0096] Optionally, as Figure 9 shown, the band-pass filter 2062 includes: a fourth capacitor c4, a fifth capacitor c5, a sixth capacitor c6, a first inductor l1, a second inductor l2, and a third inductor l3. One end of the fourth capacitor c4 is connected to one of the output ends in the secondary power amplification module 305. The other end of the fourth capacitor c4 is connected to one end of the first inductor l1. The other end of the first inductor l1 is connected to one end of the second inductor l2. The other end of the second inductor l2 is grounded. The fifth capacitor c5 is connected in parallel with the second inductor l2. One end of the third inductor l3 is connected to the other end of the first inductor l1. The other end of the third inductor l3 is connected to one end of the sixth capacitor c6. The other end of the sixth capacitor c6 is connected to the phased array ultrasonic transducer 201. For the detailed circuit connection, reference can be made to Figure 9 , which will not be elaborated here.

[0097] It should be noted that after the DDS signal generation module 303 generates the first excitation signal with focusing delay data, the first excitation signal is input into the DC-blocking and AC-coupling unit 307 through the input terminal (P2 SMA) of the DC-blocking and AC-coupling unit 307. The DC-blocking and AC-coupling unit 307 filters out the DC signal of the first excitation signal and outputs an AC signal to the positive input terminal of the first amplifier 309. After being amplified by the first amplifier 309 through operation, it is output to the positive input terminal of the second amplifier 310. After being amplified by the second amplifier 310, it is output through the other end of the seventh resistor R7, and to the negative input terminal of the third amplifier 311. After being amplified by the third amplifier 311, it is output through the other end of the tenth resistor R10. Furthermore, after passing through the first-stage operation amplification module 304, the first excitation signal forms a second excitation signal with the same frequency, the same amplitude, but opposite phase.

[0098] The first and second excitation signals are input into the first two-stage power amplification unit 3051, and the second and second excitation signals are input into the second two-stage power amplification unit 3052. Since the operating principles of the first two-stage power amplification unit 3051 and the second two-stage power amplification unit 3052 are the same, therefore, only the first two-stage power amplification unit 3051 is taken as an example to illustrate, and the operating principle of the second two-stage power amplification unit 3052 can refer to the operating principle of the first two-stage power amplification unit 3051.

[0099] Among them, the first and second excitation signals pass through the input-stage circuit 312 in the first two-stage power amplification unit 3051. The first and second excitation signals are input to the base of the first triode Q1 in the differential amplification circuit in the input-stage circuit 312, and the base of the second triode Q2 is grounded. Furthermore, the differential amplification circuit differentially amplifies the first and second excitation signals and the ground signal. When there is interference to the first and second excitation signals from the ground, the differential amplification circuit can suppress the zero drift of the first and second excitation signals.

[0100] Thus, after passing through the differential amplification circuit, a part of the first and second excitation signals flows through the third triode Q3 to the base of the seventh triode Q7 in the excitation stage, and the other part flows through the fourth triode Q4 to the base of the fifth triode Q5 in the excitation stage.

[0101] The seventh triode Q7 in the excitation stage 313 is the mirror current source of the third triode Q3, and the eighth triode Q8 is a constant voltage source. The eighth triode Q8 forms a clamping control for the fifth triode Q5. The sixth capacitor C6 is a decoupling capacitor. The second voltage stabilizing circuit 318 and the tube oscillation elimination circuit 319 in the excitation stage 313 compensate for the distorted first and second excitation signals, and then output the signal to the output stage 314. After being power-amplified by the OCL power amplifier circuit of the output stage 314, since the two-stage power amplification module 105 partially uses a BTL bridge push-pull circuit, the two ends of the load phased array ultrasonic transducer 106 are respectively connected to the output ends of the two-stage power amplification unit 3051 and the second two-stage power amplification unit 3052. The output of one power amplification unit is the mirror image output of the other power amplification unit, that is, the signals applied to the two ends of the load only differ by 180° in phase. Furthermore, the voltage obtained on the load will be twice the original single-ended output voltage, so that the output power will increase by 4 times compared with the traditional ultrasonic transducer excitation circuit.

[0102] It can be understood that the purpose of the differential amplifier circuit is to stabilize the static operating point, amplify the differential-mode signal and suppress the common-mode signal, and finally play a role in suppressing zero drift. The excitation stage 313 is a triode base bias circuit that provides the base DC current for the triode, making each transistor in a slightly conducting state. Once an input signal is added, it immediately enters the linear working area, eliminating the crossover distortion of the subsequent OCL power amplifier circuit. The output stage 314 is an OCL (Output CapacitorLess) power amplifier circuit, which is the main body of this power amplification module and is used to amplify sine pulses. The first advantage of this circuit is to overcome the shortcoming that the static current of the single-transistor input stage transistor flows through the negative feedback network; the second advantage is to utilize the mutual cancellation of the emitter junction voltages of the differential pair to obtain a low offset voltage; the third advantage is that its linearity is far superior to that of the single-transistor input stage circuit; the fourth advantage is that the circuit omits large capacitors, improves the low-frequency response, and is conducive to realizing integration. Finally, this module can output high-voltage high-frequency sine pulses with focusing delay information, which can be used for the excitation of the phased array ultrasonic transducer after hardware delay compensation. The power supply module in the first-stage operational amplifier module 304 and the two-stage power amplification module 305 provides the required DC output, jointly constituting a rectifier filter circuit. The power supply is provided by a customized toroidal transformer. Finally, filtering is performed through the band-pass filter 2062, so that the phased array ultrasonic transducer 201 is avoided from the magnetic field interference of the magnetic ring.

[0103] Generally speaking, after setting the relevant parameters of the phased array ultrasonic transducer 201 through the controller 203, the focusing delay can be automatically calculated, and the DDS signal generation module 303 is used to transmit multi-channel sine signals. For example, when exciting a 64-channel ultrasonic transducer, the DDS signal generation module 303 transmits 64-channel sine pulses with timing information. After 64-channel first-stage amplification, 128-channel sine pulses with adjustable amplitude are output. Among them, there are a total of 64 groups of signals, and each group of signals contains a pulsed sine wave passing through a first-stage non-inverting amplifier and a pulsed sine wave passing through a first-stage inverting amplifier. The 128-channel sine pulses pass through the OCL push-pull power amplification circuit. Among them, the 64-channel non-inverting pulsed sine waves act on one end of the ultrasonic transducer, and the 64-channel inverting pulses act on the other end of the ultrasonic transducer. Finally, the high-voltage high-frequency sine waves with timing information at both ends act together on the phased array ultrasonic transducer to form a BTL bridge circuit to complete the focusing excitation.

[0104] Therefore, the excitation source provided in this embodiment has a higher precise frequency.

[0105] Through the ultrasonic transducers provided in the above two embodiments, ultrasonic signals with high amplitude or high frequency can be provided. By adding a filter, it is possible to avoid the interference caused by the zero-point pulses coupled in any metal object due to the ultra-high current flowing through the magnetic stimulation coil generated by the TMS during excitation. Among them, the output frequency of the ultrasonic transducer can be 500 kHz, and the output frequency of the TMS magnetic stimulation coil can be 10 kHz. This ensures the normal operation of the ultrasonic transducer and the TMS magnetic stimulation coil.

[0106] In summary, the transcranial M-TMAS stimulation device according to the embodiments of the present invention includes: a phased array ultrasonic transducer, a TMS magnetic stimulation coil, an ultrasonic transducer excitation source, a TMS magnetic stimulation excitation source, and a controller; the controller is respectively connected to the ultrasonic transducer excitation source and the TMS magnetic stimulation excitation source, and is used to control the ultrasonic transducer excitation source to send an ultrasonic excitation signal to the phased array ultrasonic transducer, and the phased array ultrasonic transducer forms a focused sound field based on the ultrasonic excitation signal; it is also used to control the TMS magnetic stimulation excitation source to send an alternating current excitation signal to the TMS magnetic stimulation coil, and the TMS magnetic stimulation coil forms an alternating magnetic field based on the alternating current excitation signal; the focused sound field and the alternating magnetic field are coupled to form a magnetoacoustic coupled electric field, and the alternating magnetic field also generates an alternating electric field; the magnetoacoustic coupled electric field, the alternating electric field, and the focused sound field act on the patient together; wherein, a filter is provided in the ultrasonic transducer excitation source to filter out the interference signal generated by the TMS magnetic stimulation coil on the phased array ultrasonic transducer. Thus, by the combined action of the ultrasonic transducer and the TMS magnetic stimulation coil on the patient, when stimulating the patient, the magnetoacoustic coupled electric field, the alternating electric field, and the focused sound field act on the patient together, enhancing the stimulation intensity. In addition, since the TMS magnetic stimulation coil interferes with the ultrasonic transducer, a filter is added to the ultrasonic transducer to filter out the interference signal generated by the TMS magnetic stimulation coil on the ultrasonic transducer, so that when performing corresponding stimulation on the patient, the stimulation signal will not have spikes, affecting the stimulation effect.

[0107] It should be understood that various forms of the processes shown above can be used, steps can be reordered, added, or deleted. For example, the steps described in the present invention can be executed in parallel, sequentially, or in a different order, as long as the desired results of the technical solution of the present invention can be achieved, and no limitation is made herein.

[0108] The above specific embodiments do not constitute a limitation to the protection scope of the present invention. Those skilled in the art should understand that various modifications, combinations, sub-combinations, and substitutions can be made according to design requirements and other factors. Any modifications, equivalent substitutions, and improvements made within the spirit and principle of the present invention shall be included within the protection scope of the present invention.

Claims

1. A transcranial M-TMAS stimulation device, characterized in that, Comprising: a phased array ultrasonic transducer, a TMS magnetic stimulation coil, an ultrasonic transducer excitation source, a TMS magnetic stimulation excitation source, and a controller; The controller is respectively connected to the ultrasonic transducer excitation source and the TMS magnetic stimulation excitation source, and is used to control the ultrasonic transducer excitation source to send an ultrasonic excitation signal to the phased array ultrasonic transducer, and the phased array ultrasonic transducer forms a focused sound field based on the ultrasonic excitation signal; it is also used to control the TMS magnetic stimulation excitation source to send an alternating current excitation signal to the TMS magnetic stimulation coil, and the TMS magnetic stimulation coil forms an alternating magnetic field based on the alternating current excitation signal; the focused sound field and the alternating magnetic field are coupled to form a magnetoacoustic coupled electric field, and the alternating magnetic field also generates an alternating electric field; the magnetoacoustic coupled electric field, the alternating electric field, and the focused sound field act on the patient together; Wherein, a filter is provided in the ultrasonic transducer excitation source for filtering out the interference signal generated by the TMS magnetic stimulation coil on the phased array ultrasonic transducer.

2. The transcranial M-TMAS stimulation device according to claim 1, characterized in that, The ultrasonic transducer excitation source includes: an FPGA focusing delay module, an I / O channel expansion module, a plurality of fundamental frequency control circuits, a plurality of LC oscillation circuits, and a plurality of low-pass filters, and the fundamental frequency control circuits, the LC oscillation circuits, and the low-pass filters are in one-to-one correspondence; The controller is used to provide the focusing excitation parameters of each channel of the phased array ultrasonic transducer. The FPGA focusing delay module is used to calculate the focusing delay data of each channel according to the focusing excitation parameters of each channel, and output a PWM wave carrying the focusing delay data corresponding to each channel in combination with the focusing delay data of each channel. The PWM wave carrying the focusing delay data corresponding to each channel is input into the corresponding fundamental frequency control circuit through the I / O channel expansion module. Each of the LC oscillation circuits oscillates the DC source signal into a sine wave signal according to the fundamental frequency signal output by the fundamental frequency control circuit, and after filtering the sine wave signal by the low-pass filter, it is output into the corresponding channel of the phased array ultrasonic transducer.

3. The transcranial M-TMAS stimulation device according to claim 2, wherein, The fundamental frequency control circuit includes: an optocoupler circuit unit, a NAND gate circuit unit, a crystal oscillator unit, a MOS transistor control unit, and a MOS transistor. The input end of the optocoupler circuit unit is connected to the I / O channel expansion module, the output end of the optocoupler circuit unit is connected to the input end of the NAND gate circuit unit, the output end of the crystal oscillator unit is connected to the input end of the NAND gate circuit unit, the output end of the NAND gate circuit unit is connected to the MOS transistor control unit, and the MOS transistor is in an open state or a closed state according to the level signal output by the MOS transistor control unit to provide a fundamental frequency signal for the LC oscillation circuit.

4. The transcranial M-TMAS stimulation device according to claim 3, wherein The LC oscillation circuit includes: a first LC oscillation circuit unit and a second LC oscillation circuit unit. The input end of the first LC oscillation circuit unit is used to input the DC source signal. The output end of the first LC oscillation circuit is connected to the input end of the second LC oscillation circuit and the second end of the MOS transistor respectively. The third end of the MOS transistor is grounded. The output end of the second LC oscillation circuit is connected to the input end of the low-pass filter. The output end of the low-pass filter is connected to the corresponding element of the phased array ultrasonic transducer.

5. The transcranial M-TMAS stimulation device according to claim 2, wherein The low-pass filter includes: a first capacitor, a second capacitor, a third capacitor, a first resistor, a second resistor, a third resistor and a comparator. The output end of the LC oscillation circuit is connected to one end of the first capacitor. The other end of the first capacitor is respectively connected to one end of the second capacitor, one end of the first resistor and one end of the third capacitor. The other end of the first resistor is grounded. The other end of the second capacitor and the other end of the first resistor are connected together to the first input end of the comparator. The other end of the third capacitor and the other end of the second resistor are connected to the output end of the comparator. One end of the third resistor is connected to the second input end of the comparator.

6. The transcranial M-TMAS stimulation device according to claim 1, wherein, The ultrasonic transducer excitation source includes: a focusing delay module, a DDS signal generation module, a plurality of first-stage operational amplifier modules, a plurality of second-stage power amplifier modules and a plurality of band-pass filters. The first-stage operational amplifier modules and the second-stage power amplifier modules are correspondingly arranged. The second-stage power amplifier modules correspond to two of the band-pass filters. The controller is used to provide the focusing excitation parameters of each channel of the phased array ultrasonic transducer. The focusing delay module is used to obtain the focusing delay data corresponding to the focusing excitation parameters of each channel according to the focusing excitation parameters of each channel. The DDS signal generation module transmits a first excitation signal to each element of the phased array ultrasonic transducer according to the focusing delay data of each channel. The first-stage operational amplifier module is used to form two second excitation signals with the same amplitude and opposite phases from the first excitation signal. The second-stage power amplifier module is used to perform power amplification on the two second excitation signals with the same amplitude and opposite phases and then output them to the corresponding band-pass filters. After being filtered by the band-pass filters, they are output to the corresponding channels of the phased array ultrasonic transducer.

7. The transcranial M-TMAS stimulation device according to claim 6, wherein, The first-stage operational amplifier module includes: a DC blocking and AC coupling unit and an operational amplifier unit. The input end of the DC blocking and AC coupling unit is connected to the output end of the DDS signal generation module and is used to convert the first excitation signal into an AC signal. The input end of the operational amplifier unit is connected to the output end of the DC blocking and AC coupling unit and is used to convert the AC signal into two second excitation signals with the same amplitude and opposite phases.

8. The transcranial M-TMAS stimulation device according to claim 6, wherein The secondary power amplification module includes: a first secondary power amplification unit and a second secondary power amplification unit. The input end of the first secondary power amplification unit is connected to the first output end of the primary operational amplification module, and the output end is connected to the input end of the band-pass filter. The output end of the band-pass filter is connected to one end of the phased array ultrasonic transducer; the input end of the second secondary power amplification unit is connected to the second output end of the primary operational amplification module, and the output end is connected to the input end of the band-pass filter. The output end of the band-pass filter is connected to the other end of the phased array ultrasonic transducer.

9. The transcranial M-TMAS stimulation device according to claim 8, characterized in that, Both the first secondary power amplification unit and the second secondary power amplification unit include an input stage circuit, an excitation stage circuit, and an output stage circuit. The input end of the input stage circuit is connected to one of the output ends of the primary operational amplification module, and is used to suppress the zero drift of the second excitation signal. The excitation stage circuit is used to compensate for the second excitation signal with zero-crossing distortion. The output stage circuit is used to amplify the excitation signal processed by the input stage circuit and the excitation stage circuit, and output it to the band-pass filter, and after being filtered by the band-pass filter, output it to the phased array ultrasonic transducer.

10. The transcranial M-TMAS stimulation device according to claim 6, characterized in that, The band-pass filter includes: a fourth capacitor, a fifth capacitor, a sixth capacitor, a first inductor, a second inductor, and a third inductor. One end of the fourth capacitor is connected to one of the output ends in the secondary power amplification module, the other end of the fourth capacitor is connected to one end of the first inductor, the other end of the first inductor is connected to one end of the second inductor, the other end of the second inductor is grounded, the fifth capacitor is connected in parallel with the second inductor, one end of the third inductor is connected to the other end of the first inductor, the other end of the third inductor is connected to one end of the sixth capacitor, and the other end of the sixth capacitor is connected to the phased array ultrasonic transducer.

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