CN216455042U - Portable magnetic stimulation motion evoked potential acquisition system - Google Patents
Portable magnetic stimulation motion evoked potential acquisition system Download PDFInfo
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- CN216455042U CN216455042U CN202220811936.2U CN202220811936U CN216455042U CN 216455042 U CN216455042 U CN 216455042U CN 202220811936 U CN202220811936 U CN 202220811936U CN 216455042 U CN216455042 U CN 216455042U
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Abstract
The utility model belongs to the technical field of magnetic therapy, and discloses a portable magnetic stimulation motion evoked potential acquisition system, which comprises a trigger circuit, a singlechip control circuit, an isolation circuit, a transmission circuit and two sampling circuits, wherein the input of the trigger circuit is connected with a control panel in a transcranial magnetic stimulation host, and the output of the trigger circuit is connected with the singlechip control circuit; the single chip microcomputer control circuit is connected with the two sampling circuits, the single chip microcomputer control circuit is connected with the transmission circuit through the isolation circuit, and the transmission circuit is connected with an upper computer in the transcranial magnetic stimulation host through a USB interface; each sampling circuit consists of a front-end filtering and amplifying circuit and an ADC (analog-to-digital converter) circuit, wherein the front-end filtering and amplifying circuit consists of a differential amplifying circuit and an operational amplifying circuit. The utility model provides a thereby the lower difficult collection of flesh electricity original signal voltage and subsidiary clutter lead to gathering the great problem of voltage error.
Description
Technical Field
The utility model relates to the technical field of medical equipment, concretely relates to portable magnetic stimulation motion evoked potential collection system for myoelectric potential is gathered.
Background
Magnetic Motor Evoked Potentials (MEPs) are one method of detecting pyramidal tract function and peripheral nerve motor conduction function. The Transcranial Magnetic Stimulation (TMS) host machine controls the magnetic field coil to form a magnetic field to stimulate a cerebral cortex movement area, then a magnetic stimulation movement evoked potential acquisition device (MEP device) is used for acquiring movement evoked potentials on hands of a testee, the magnetic stimulation is painless, the operation is simple, the brain stimulation method is non-invasive, the testee has no pain or discomfort, the hands can be twitched along with the stimulation rhythm almost without feeling, and the magnetic stimulation is a mark for birth of transcranial magnetic stimulation technology.
However, the existing MEP devices generally use ADCs to directly sample human body signals or perform ADC sampling after signal processing of simple amplification and filtering, and the two sampling methods have obvious defects. According to literature and practical experience, when the myoelectric potential is too small, the amplitude is usually within 0-5 mV, various clutter such as ultralow frequency (close to direct current), 50HZ power frequency interference, high-frequency interference signals and the like are mixed, if the two sampling modes are used for sampling, the error of the detected myoelectric voltage is large, and the condition that the burr cannot meet the accurate acquisition requirement exists, so that misdiagnosis occurs in the treatment process of a doctor.
SUMMERY OF THE UTILITY MODEL
In order to solve the problem of the influence of the electromyographic signal undersize and the burr is more, the upper and lower circuit is related, the utility model provides a portable magnetic stimulation motion evoked potential collection system.
The utility model discloses a following technical scheme realizes. A portable magnetic stimulation motion evoked potential acquisition system comprises a trigger circuit, a single chip microcomputer control circuit, an isolation circuit, a transmission circuit and two sampling circuits, wherein the input of the trigger circuit is connected with a control panel in a transcranial magnetic stimulation host, and the output of the trigger circuit is connected with the single chip microcomputer control circuit; the single chip microcomputer control circuit is connected with the two sampling circuits, the single chip microcomputer control circuit is connected with the transmission circuit through the isolation circuit, and the transmission circuit is connected with an upper computer in the transcranial magnetic stimulation host through a USB interface; each sampling circuit consists of a front-end filtering and amplifying circuit and an ADC (analog to digital converter) circuit, the input of the front-end filtering and amplifying circuit of each sampling circuit is connected with 5 electrode plates through 5 electrode wires, the ADC circuit has two inputs, the output of the front-end filtering and amplifying circuit of each sampling circuit is connected with one input of the ADC circuit, the output of the ADC circuit is connected with the input of a single chip microcomputer control circuit, and the front-end filtering and amplifying circuit consists of a differential amplifying circuit and an operational amplifying circuit.
More specifically, the 5 electrode lines on each sampling circuit are respectively IN1+, IN1-, IN2+, IN 2-and COM.
More specifically, the trigger circuit is input through a connector, the input comprises two paths of trigger + and trigger-, the trigger + and the trigger-are connected to two poles of a bidirectional TVS tube and a first capacitor, the trigger + is connected to a pin 1 of a photoelectric coupler after being connected with a first resistor in series, the trigger-is connected to a pin 2 of the photoelectric coupler, a pin 3 of the photoelectric coupler is grounded, and a pin 4 of the photoelectric coupler is connected to a second resistor and then is connected to a port PB0 of the singlechip control circuit. The utility model adopts the photoelectric coupler as the coupling device to separate the upper and lower circuits, and the upper and lower circuits are not affected, thereby increasing the robustness and safety of the circuit and reducing the coupling between the circuits; meanwhile, the bidirectional TVS tube is adopted to prevent the high-energy transient overvoltage pulse from possibly occurring in the transcranial magnetic stimulation host, so that the components of the lower circuit are protected.
More specifically, the input of the differential amplification circuit is an electrode line IN1+ and an electrode line IN1+, the electrode line IN1+ is connected with one end of a second capacitor, the other end of the second capacitor is connected with one end of a third resistor and a pin 1 of the differential amplifier IN common, the electrode line IN 1-is connected with one end of a third capacitor, the other end of the third capacitor is connected with the other end of the third resistor and a pin 4 of the differential amplifier IN common, a pin 2 and a pin 3 of the differential amplifier are connected with a fourth resistor IN common, a pin 8 of the differential amplifier is connected with a 5V power supply, a pin 5 of the differential amplifier is connected with 0V, a pin 6 of the differential amplifier is grounded, and a pin 7 of the differential amplifier is the output of the differential amplification circuit.
More specifically, the operational amplifier circuit is composed of an operational amplifier, a fifth resistor, a sixth resistor, a first filter capacitor and a second filter capacitor, wherein a pin 3 of the operational amplifier is connected with a pin 7 of the differential amplifier, a pin 1 of the operational amplifier is connected with a pin 2 and is also connected with one end of the fifth resistor, the other end of the fifth resistor is connected with one end of the sixth resistor and one end of the fourth filter capacitor, the other end of the fourth filter capacitor is grounded, the other end of the sixth resistor is connected with one end of the fifth filter capacitor and the output of the operational amplifier circuit, the other end of the fifth filter capacitor is grounded, a pin 8 of the operational amplifier is connected with a 5V power supply, and a pin 4 of the operational amplifier is connected with 0V.
More specifically, the isolation circuit comprises an isolator, pins 6 and 7 of the isolator are respectively connected with pins 16 and 17 of an MCU controller in the singlechip control circuit, pins 1 and 8 of the isolator are respectively connected with a 5V power supply and a 3.3V power supply, and pins 4 and 5 of the isolator are respectively connected with 0V; pins 2 and 3 of the isolator are connected with pins 2 and 3 of the transmission circuit chip to be used as transmission circuit input.
More specifically, the transmission circuit chip employs CH340 CU.
More specifically, the isolator is an ADUM3201 isolator.
Has the advantages that: compared with the prior art, the utility model discloses a multi-level amplifying and filtering circuit, on the basis that does not reduce stability effectual collection motion evoked potential and eliminated smuggleing secretly the clutter burr inside the electric potential. The trigger circuit uses the photoelectric coupler as a coupling device to separate the upper circuit and the lower circuit, and the upper circuit and the lower circuit are not influenced, so that the robustness and the safety of the circuits are improved, and the coupling between the circuits can be reduced; meanwhile, a bidirectional TVS tube is adopted to prevent a transcranial magnetic stimulation host from generating high-energy transient overvoltage pulses and protect components of a lower circuit. The isolation circuit is used for eliminating 50HZ power frequency interference in direct current converted from mains supply, so that errors of voltage measurement are reduced, and the use safety is ensured. The problem of myoelectricity original signal voltage lower difficult collection and attached clutter such as high frequency noise, ultralow frequency noise, 50Hz power frequency interference and consequently lead to the collection voltage error great is solved.
Drawings
Fig. 1 is a schematic diagram of a frame of a magnetic stimulation exercise evoked potential acquisition system and a transcranial magnetic stimulation host of the present invention.
Fig. 2 is a diagram of a flip-flop circuit.
Fig. 3 is a front-end filter amplifying circuit diagram.
FIG. 4 is a circuit diagram of ADC analog-to-digital conversion;
FIG. 5 is a circuit diagram of a single chip microcomputer control circuit;
FIG. 6 is a diagram of an isolation circuit and a transmission circuit.
Reference numerals: the circuit comprises a connector P1, a bidirectional TVS tube T1, a first capacitor C1, a first resistor R1, a second resistor R2, a photoelectric coupler U1, a second capacitor C2, a third resistor R3, a differential amplifier U2, a third capacitor C3, a fourth resistor R4, an operational amplifier U3, a fifth resistor R5, a sixth resistor R6, a first filter capacitor C4, a second filter capacitor C5, an ADC chip U4, an MCU controller U5, a seventh resistor R7, a sixth capacitor C6, a key S1, an eighth resistor R8, a crystal oscillator Y1, an isolator U6, a transmission circuit chip U7 and a USB port P2
Detailed Description
The present invention will be described in further detail with reference to the accompanying drawings.
Referring to fig. 1, a portable magnetic stimulation motion evoked potential acquisition system comprises a trigger circuit, a singlechip control circuit, an isolation circuit, a transmission circuit and two sampling circuits, wherein the input of the trigger circuit is connected with a control panel in a transcranial magnetic stimulation host, and the output of the trigger circuit is connected with the singlechip control circuit; the single chip microcomputer control circuit is connected with the two sampling circuits, the single chip microcomputer control circuit is connected with the transmission circuit through the isolation circuit, and the transmission circuit is connected with an upper computer in the transcranial magnetic stimulation host through a USB interface; each sampling circuit consists of a front-end filtering and amplifying circuit and an ADC (analog to digital converter) circuit, the input of the front-end filtering and amplifying circuit of each sampling circuit is connected with 5 electrode plates through 5 electrode wires, the ADC circuit has two inputs, the output of the front-end filtering and amplifying circuit of each sampling circuit is connected with one input of the ADC circuit, the output of the ADC circuit is connected with the input of a single chip microcomputer control circuit, and the front-end filtering and amplifying circuit consists of a differential amplifying circuit and an operational amplifying circuit.
More specifically, the 5 electrode lines on each sampling circuit are respectively IN1+, IN1-, IN2+, IN 2-and COM.
As shown in fig. 2, the trigger circuit is input by a connector P1, the input includes two ways of trigger + and trigger-, the trigger + and trigger-are connected to two poles of the bidirectional TVS tube T1 and the first capacitor C1, the trigger + is connected to a pin 1 of the photocoupler U1 after being connected in series with the first resistor R1, and the trigger-is connected to a pin 2 of the photocoupler U1. The 3 feet of the photoelectric coupler U1 are grounded, the 4 feet of the photoelectric coupler U1 are connected with a second resistor R2 and then connected with a PB0 port of the singlechip control circuit to generate external interruption, and the type of the photoelectric coupler U1 is PC 817. The existing trigger circuit usually does not adopt an isolation measure, which causes great influence on a lower circuit when a higher circuit has short circuit and other problems. Compared with other trigger circuits, the circuit adopts the photoelectric coupler U1 as a coupling device to separate the upper circuit and the lower circuit, and the influence is not generated between the upper circuit and the lower circuit, so that the robustness and the safety of the circuit are improved, and the coupling between the circuits can be reduced; meanwhile, a bidirectional TVS (transient voltage suppressor) T1 is adopted to prevent a transcranial magnetic stimulation host from generating high-energy transient overvoltage pulses and protect components of a lower circuit.
Referring to fig. 3, the front-end filter amplifier circuit is composed of a differential amplifier circuit and an operational amplifier circuit, and the inputs of the differential amplifier circuit are an electrode line IN1+ and an electrode line IN 1-. The electrode line IN1+ is connected with one end of a second capacitor C2, the other end of the second capacitor C2 is connected with one end of a third resistor R3 and a pin 1 of a differential amplifier U2 IN a common mode, the electrode line IN 1-is connected with one end of a third capacitor C3, the other end of the third capacitor C3 is connected with the other end of the third resistor R3 and a pin 4 of the differential amplifier U2 IN a common mode, a pin 2 and a pin 3 of the differential amplifier U2 are connected with a fourth resistor R4, a pin 8 of the differential amplifier U2 is connected with a 5V power supply, a pin 5 of the differential amplifier U2 is connected with 0V, a pin 6 of the differential amplifier U2 is grounded, a pin 7 of the differential amplifier U2 is output of the differential amplifier circuit, and the model number of the differential amplifier U2 is ADS 8422.
The operational amplifier circuit is composed of an operational amplifier U3, a fifth resistor R5, a sixth resistor R6, a first filter capacitor C4 and a second filter capacitor C5, wherein a pin 3 of the operational amplifier U3 is connected with a pin 7 of the differential amplifier U2, a pin 1 of the operational amplifier U3 is connected with a pin 2 and is also connected with one end of the fifth resistor R5, the other end of the fifth resistor R5 is connected with one end of the sixth resistor R6 and one end of the fourth filter capacitor C4, the other end of the fourth filter capacitor C4 is grounded, the other end of the sixth resistor R6 is connected with one end of the fifth filter capacitor C5 and the output of the operational amplifier circuit, the other end of the fifth filter capacitor C5 is grounded, a pin 8 of the operational amplifier U3 is connected with a 5V power supply, a pin 4 of the operational amplifier U3 is connected with 0V, and the model TLC of the operational amplifier U3 is 2272.
Referring to fig. 4 and 5, the ADC analog-to-digital conversion circuit includes an ADC chip U4, the ADC chip U4 is in the model number of ADS1292, a pin 4 of the ADC chip U4 is connected to an output of the operational amplifier circuit in one of the sampling circuits, and a pin 6 of the ADC chip U4 is connected to an output of the operational amplifier circuit in the other sampling circuit. Pins 12, 28 and 29 of the ADC chip U4 are respectively connected with a 5V power supply; pins 14 and 23 of the ADC chip U4 are respectively connected with a 3.3V power supply; pins 9, 10, 11, 24 and 27 of the ADC chip U4 are connected with 0V; pins 18, 19, 20, 21 and 22 of the ADC chip U4 are connected as outputs to pins 20, 23, 21, 22 and 15 of the MCU controller U5, respectively.
Compared with direct sampling and simple filtering amplification resampling of other MEP products, in the first-stage circuit, if the electromyographic signals collected by the electrode plates are directly input into the high-power amplifier, zero drift of the output signals can be caused due to the existence of noise, and therefore the input end adopts an RC differential circuit to filter low-frequency signals and then adopts a differential amplifier U2 to amplify the amplitude of the voltage, eliminate common-mode interference of the two input ends and reduce the burrs of the signals. In the second stage circuit, an operational amplifier U3 is used for impedance matching of the input differential amplification circuit, zero drift suppression and further voltage amplification, and two filter capacitors are used for filtering high-frequency signals. The electromyographic signals can be directly sampled by using an ADC (analog-to-digital converter) after passing through a front-end filtering and amplifying circuit.
The ADC analog-to-digital conversion circuit samples the ADS1292 chip and mainly functions to convert analog signals output by a previous stage into digital signals which can be identified by a singlechip control circuit. The original myoelectric respiration signal enters an ADS1292 chip from pins IN1P and IN2P after being subjected to most interference filtering by a differential amplification circuit and operational amplification, the ADS1292 chip performs A/D conversion and amplification on the acquired original signal, and the data is sent to a singlechip control circuit IN a frame format through two data pins SPI _ MISO and SPI _ MOSI.
Referring to fig. 5, the single chip microcomputer control circuit includes an MCU controller U5, the model of the MCU controller U5 is STM32F103RCT6, and the input of the MCU controller U5 is the output of the two sampling circuits. A pin 26 of the MCU controller U5 is connected to the trigger circuit as a PB0 port, a pin 7 of the MCU controller U5 is connected to one end of a seventh resistor R7, a sixth capacitor C6 and a button S1, the other end of the seventh resistor R7 is connected to 3.3V, and the other end of the sixth capacitor C6 and the button S1 is connected to 0V. A pin 5 of the MCU controller U5 is connected to one end of an eighth resistor R8, a crystal oscillator Y1, a seventh capacitor C7 and an eighth capacitor C8 which are connected in series, and the middle of the seventh capacitor C7 and the eighth capacitor C8 which are connected in series is grounded; the other end of the eighth resistor R8, the crystal oscillator Y1 and the eighth capacitor C8 is connected with a pin 6 of the MCU controller U5. The 1 pin of the MCU controller U5 is connected with a 3.3V power supply. Pins 16 and 17 of the MCU controller U5 are outputs and are connected with a transmission circuit.
Referring to fig. 6, the isolation circuit includes an isolator U6, pins 6 and 7 of the isolator U6 are respectively connected to pins 16 and 17 of the MCU controller U5, pins 1 and 8 of the isolator U6 are respectively connected to a 5V power supply and a 3.3V power supply, and pins 4 and 5 of the isolator U6 are respectively connected to 0V. Pins 2 and 3 of the isolator U6 are connected to pins 2 and 3 of the transmission circuit chip U7 as transmission circuit inputs. The transmission circuit chip U7 adopts CH340CU, the 5 pins and the 6 pins of the transmission circuit chip U7 are connected with the 3 pins and the 2 pins of the USB port P2, the 16 pins of the transmission circuit chip U7 are connected with a 5V power supply, and the 1 pin of the transmission circuit chip U7 is connected with 0V. The isolator U6 is used as an isolation measure to increase security.
In this embodiment, the transmission circuit is a serial-to-USB output circuit, and the USB-to-serial circuit with CH340C as the core mainly functions to realize USB-to-serial conversion. The isolation circuit has the main function of eliminating 50HZ power frequency interference in direct current converted from commercial power and reducing errors of voltage measurement. Isolator U6 is an ADUM3201 isolator, and the primary function of the electrical isolation centered on the ADUM3201 isolator is to satisfy the safety requirements of the medical system to use isolation to protect the operator, patient, or the system itself. The ADUM3201 isolator is used, the internal voltage stabilizer can work under a 5V USB power supply and a 3.3V power supply provided by a system, and the ADUM3201 isolator can centralize and isolate all functions required by the USB in the medical equipment, does not need additional elements, and can be directly plugged into a USB interface of a PC for use without modifying a host or peripheral software.
The above description is only a preferred embodiment of the present invention and is not intended to limit the present invention, and various modifications and changes may be made by those skilled in the art. Any modification, equivalent replacement, or improvement made within the spirit and principle of the present invention should be included in the protection scope of the present invention.
Claims (6)
1. A portable magnetic stimulation motion evoked potential acquisition system is characterized by comprising a trigger circuit, a singlechip control circuit, an isolation circuit, a transmission circuit and two sampling circuits, wherein the input of the trigger circuit is connected with a control panel in a transcranial magnetic stimulation host, and the output of the trigger circuit is connected with the singlechip control circuit; the single chip microcomputer control circuit is connected with the two sampling circuits, the single chip microcomputer control circuit is connected with the transmission circuit through the isolation circuit, and the transmission circuit is connected with an upper computer in the transcranial magnetic stimulation host through a USB interface; each sampling circuit consists of a front-end filtering and amplifying circuit and an ADC (analog-to-digital converter) circuit, the input of the front-end filtering and amplifying circuit of each sampling circuit is connected with 5 electrode plates through 5 electrode wires, the ADC circuit has two inputs, the output of the front-end filtering and amplifying circuit of each sampling circuit is connected with one input of the ADC circuit, the output of the ADC circuit is connected with the input of a singlechip control circuit, and the front-end filtering and amplifying circuit consists of a differential amplifying circuit and an operational amplifying circuit; the 5 electrode lines on each sampling circuit are respectively IN1+, IN1-, IN2+, IN 2-and COM; the trigger circuit is input through a connector, the input comprises two trigger + and trigger-circuits, the trigger + and the trigger-circuits are connected to two poles of a bidirectional TVS tube and a first capacitor, the trigger + is connected to a pin 1 of a photoelectric coupler after being connected with a first resistor in series, the trigger-circuit is connected to a pin 2 of the photoelectric coupler, a pin 3 of the photoelectric coupler is grounded, and a pin 4 of the photoelectric coupler is connected to a second resistor and then is connected to a port PB0 of the singlechip control circuit.
2. The portable magnetic stimulation exercise evoked potential acquisition system according to claim 1, wherein the inputs of the differential amplification circuit are electrode line IN1+ and electrode line IN1+, electrode line IN1+ is connected with one end of a second capacitor, the other end of the second capacitor is connected with one end of a third resistor and a pin 1 of a differential amplifier IN common, electrode line IN 1-is connected with one end of a third capacitor, the other end of the third capacitor is connected with the other end of the third resistor and a pin 4 of the differential amplifier IN common, a pin 2 and a pin 3 of the differential amplifier are connected with a fourth resistor, a pin 8 of the differential amplifier is connected with a 5V power supply, a pin 5 of the differential amplifier is connected with 0V, a pin 6 of the differential amplifier is connected with ground, and a pin 7 of the differential amplifier is the output of the differential amplification circuit.
3. The portable magnetic stimulation motion-evoked potential collection system according to claim 2, wherein the operational amplifier circuit is composed of an operational amplifier, a fifth resistor, a sixth resistor, a first filter capacitor and a second filter capacitor, wherein 3 pins of the operational amplifier are connected with 7 pins of the differential amplifier, 1 pin of the operational amplifier is connected with 2 pins and is also connected with one end of the fifth resistor, the other end of the fifth resistor is connected with one end of the sixth resistor and one end of the fourth filter capacitor, the other end of the fourth filter capacitor is grounded, the other end of the sixth resistor is connected with one end of the fifth filter capacitor and the output of the operational amplifier circuit, the other end of the fifth filter capacitor is grounded, 8 pins of the operational amplifier are connected with a 5V power supply, and 4 pins of the operational amplifier are connected with 0V.
4. The portable magnetic stimulation exercise evoked potential acquisition system according to claim 1, characterized in that the isolation circuit comprises an isolator, pins 6 and 7 of which are respectively connected with pins 16 and 17 of the MCU controller in the singlechip control circuit, pins 1 and 8 of which are respectively connected with a 5V power supply and a 3.3V power supply, and pins 4 and 5 of which are respectively connected with 0V; pins 2 and 3 of the isolator are connected with pins 2 and 3 of the transmission circuit chip to be used as transmission circuit input.
5. The portable magnetic stimulation motion-evoked potential acquisition system according to claim 4, wherein the transmission circuit chip adopts CH340 CU.
6. The system of claim 4, wherein the isolator is an ADUM3201 isolator.
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN116139409A (en) * | 2023-04-17 | 2023-05-23 | 江西朴拙医疗设备有限公司 | Anti-interference magnetic therapy detection system, threshold detection method and all-in-one machine |
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN116139409A (en) * | 2023-04-17 | 2023-05-23 | 江西朴拙医疗设备有限公司 | Anti-interference magnetic therapy detection system, threshold detection method and all-in-one machine |
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