KR20140118424A - Commercial frequency AC discharge magnetic stimulater - Google Patents

Abstract

The present invention relates to a commercial frequency alternating current discharge magnetic stimulator, comprising a input signal unit which enables 220 input voltage to be reduced to 9 voltage to be full-wave rectified to a diode bridge circuit; a zero cross switch (ZCS), wherein the signal from the input signal unit is input in a base of a first transistor of a differentiator, which amplifies the output of the differentiator, therefore, outputs 5 voltage of square wave whose pulse width is 500 μs at a zero point of the base of the first transistor; a magnetic output unit which enables 220 input voltage to be full-wave rectified to the diode bridge circuit and transmits pulse to a magnetic coil by being triggered to SCR.

Description

[0001] The present invention relates to a commercial frequency AC discharge magnetic stimulator,

The present invention relates to an input signal portion for reducing a 220V input voltage to 9V and subjecting it to full wave rectification by a diode bridge circuit; A zero voltage switch for inputting a signal of the input signal portion to the base of the first transistor of the differentiator and amplifying the output of the differentiator to output a 5V square wave having a pulse width of 500 mu at a point where the base of the first transistor becomes zero ZCS (Zero Cross Switch)); A magnetic output section for full-wave rectifying the 220V input voltage to the diode bridge circuit and triggering the SCR to transmit the pulse to the magnetic pole coil; An A / D converter for receiving a full-wave rectified output of the diode bridge circuit of the magnetic output unit and converting the rectified output into a digital signal, and an A / D converter for receiving the output of the A / D converter and the output of the ZCS (Zero Cross Switch) The SCR trigger pulse ratio of the zero voltage switch 20 (ZCS (zero cross switch)) is adjusted to a ratio of 1: 1 or 2N: 1 (N is a natural number) A pulse control unit for applying a trigger signal to the pulse signal; And the output of the magnetic output unit is controlled by the frequency output of the input power source.

As the aging of the population in Korea becomes worse, aging diseases such as neuralgia, Parkinson 's disease, Alzheimer' s syndrome (senile dementia) and stroke (stroke) become important concerns.

It is a rapidly increasing number of patients with neuropsychiatric disorders such as mental disturbances (depression, manic depression, emotional disturbance) caused by complex modern society. These diseases can be diagnosed and treated using HMPF (High-level Magnetic Field) Simple equipment has been proposed.

 Eddy current is generated when momentary strong magnetic field is transmitted to a conductor which permeates well like a human body, and the induced current is effective on each tissue of human body by electrophysiological mechanism. In addition, muscular tissues are stimulated by motor neurons connected to muscle tissue to exhibit muscle contraction effect, and electrophysiological effects on sensory nerve, blood and bone tissue.

The magnetic stimulator is a therapeutic device using such a magnetic field. The magnetic field is not only harmless to the human body but also penetrates deeply into the human body and stimulates nerve tissue and muscular tissue.

In particular, when the spinal nerve and peripheral nerves are treated with a magnetic field, stress-induced depression, insomnia, bipolar disorder, etc. can be treated.

Recently, as the demand of therapeutic and diagnostic magnetic stimulators with 20W output power with a pulse repetition rate of 100Hz or less has increased, maintenance and repair convenience as well as miniaturization of magnetic stimulator power supply device to satisfy user convenience and ease of output control And cost reduction are increasing.

The power supply of the conventional pulse magnetic stimulator is switched to meet the desired pulse repetition rate and the energy charged in the capacitor is applied to the coil probe discharge tube through the high voltage pulse transformer.

That is, DC is converted into pulse energy through a switching process, and then the pulse energy is supplied to the discharge tube.

Such a conventional method requires a rectifying part for converting AC to DC and a control part for controlling switching. The rectifying part is composed of a rectifying diode, a current limiting resistor, a smoothing capacitor, etc. In order to obtain good DC, And the switching unit is constituted by a high-speed switching device such as a high-priced syratron or IGBT and a control circuit, which is problematic in that an expensive manufacturing cost is required.

On the other hand, in order to treat the magnetic field penetrating deeply into the human body, the pulse width is narrow, the waveform having the fast rise time is the best, and the noise is less and the heat is less, Suitable.

Biphasic waveforms are suitable for this purpose. All PMF (Pulsed Magnetic Field) type magnetic stimulators at home and abroad use Biphasic type.

However, such a magnetic stimulator has a disadvantage in that the energy transfer efficiency is drastically reduced as the frequency (pulse repetition rate) is increased, and there is a problem that it is impossible to make various changes in pulse shape.

Disclosure of Invention Technical Problem [8] The present invention has been made to solve the above-mentioned problems, and it is an object of the present invention to provide a commercial frequency AC magnetic discharge stimulator capable of manufacturing at low cost, shortening a pulse rise time and making various shapes of pulses, The purpose is to provide.

According to an aspect of the present invention, there is provided an integrated circuit device comprising: an input signal unit for reducing the input power to perform full-wave rectification to a diode bridge circuit; A zero voltage switch (ZCS) for receiving an output of the input signal unit and outputting a zero voltage pulse; A magnetic output unit which is full-wave rectified by the diode bridge circuit and is triggered by the SCR to be applied to the primary side of the leakage transformer, and the discharge tube is connected to the secondary side of the leakage transformer; A zero crossing switch (ZCS) and a diode bridge circuit full-wave rectified output of the magnetic output section to obtain phase information and synchronize with the pulse signal of the zero voltage switch, A pulse control section for adjusting a ratio of the output pulse frequency of a zero voltage switch (ZCS) to 1: 1 or 1: (1 / 2N) (N is a natural number) to apply a trigger signal to the SCR of the magnetic output section And the output of the magnetic output unit is controlled by the frequency output of the input power source. The present invention is directed to a commercial frequency AC magnetic discharge magnetic stimulator.

The pulse control unit includes an A / D converter for receiving the full-wave rectified output of the diode bridge circuit of the magnetic output unit and converting the rectified output into a digital signal, and an A / D converter for converting the output of the A / D converter and the output of the ZCS And a DSP (digital signal processing) board for adjusting the output pulse rate of the zero voltage switch (ZCS) to apply a trigger signal to the SCR of the magnetic output unit And a magnetic resonance imaging apparatus.

According to the present invention, since the commercial frequency is modulated using pulses, it can be manufactured at a low cost. Since the thyristor can be turned on and off, it is possible to shorten the pulse rise time and make various shapes of pulses, There is an advantage that a commercial frequency AC magnetic discharge stimulator capable of reducing the energy transfer loss due to the increase of the repetition rate is provided.

BRIEF DESCRIPTION OF THE DRAWINGS FIG.
Fig. 2 is a diagram showing the pulse structure in the present invention
FIG. 3 is a diagram of the magnetic stimulator structure used in the present invention
FIG. 4 is a graph showing an SCR trigger signal graph
5 is a graph showing a comparison voltage waveform
6 is a graph showing the comparison voltage waveform
FIG. 7 shows a comparison voltage waveform when the output intensity is 50%
8 is a graph showing the comparison voltage waveform
9 to 11 are graphs showing the output characteristics of the magnetic stimulator according to the pulse repetition rate
Figures 12 and 13 show the output measurement graph of the magnetic stimulator when the pulse repetition rate is 60 Hz and the SCR conduction angle is 90 [
FIG. 14 is a graph showing the output characteristic curve of the magnetic stimulator according to the change of the pulse repetition rate
15 is a graph showing the magnetic stimulus output characteristics according to the cooling medium
16 is a graph showing the output characteristics of the magnetic stimulator according to the SCR conduction angle

Hereinafter, the present invention will be described with reference to the drawings. In the following description of the present invention, a detailed description of related arts or configurations will be omitted when it is determined that the gist of the present invention may be unnecessarily obscured will be.

It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory and are intended to be exemplary, self-explanatory, allowing for equivalent explanations of the present invention.

3 is a structural view of a magnetic stimulator used in the present invention, FIG. 4 is a graph of an SCR trigger signal, and FIG. 5 is a graph showing an output intensity 6 is a comparative voltage waveform at a frequency of 100% at a frequency of 5 Hz, FIG. 7 is a comparative voltage waveform at an output intensity of 50%, and FIG. 8 is a waveform of a comparison voltage at a frequency of 50% FIGS. 9 to 11 are graphs of output characteristics of the magnetic stimulator according to the pulse repetition rate. FIGS. 12 and 13 are graphs of the output of the magnetic stimulator when the pulse repetition rate is 60 Hz and the SCR conduction angle is 90.degree. FIG. 14 is a graph of the output characteristic of the magnetic stimulator according to the change of the pulse repetition rate, FIG. 15 is a graph of the output characteristic of the magnetic stimulator according to the cooling medium, A.

As shown in the drawing, the present invention relates to a commercial frequency AC magnetic induction magnetic stimulator, and is largely composed of an input signal unit 10, a zero voltage switch 20, a magnetic output unit 30, and a pulse control unit 40.

The AC magnetic discharge stimulator according to the present invention is a treatment device using a magnetic field. The magnetic field is not only harmless to the human body but also penetrates deeply into the human body, thereby stimulating nerve tissue and muscle tissue.

The present invention is a technique for discharging a magnetic stimulator using a commercial frequency alternating current (60 Hz) discharge. When the alternating current (60 Hz) of the primary side of the leakage transformer 330 of the magnetic output section 30 is controlled and pulsed, It is possible to provide a low-cost pulsed magnetic stimulator in which the pulse width is narrow, the rise time is fast, the noise is small, and the heat is little.

That is, the existing commercial frequency alternating current is directly switched from the primary side of the transformer of the magnetic output unit 30 to pulse, and the output of the magnetic stimulator is controlled by varying the pulse frequency.

The present invention includes a zero voltage switch 20 (ZCS (Zero Cross Switch)) for detecting zero voltage of an input power source sinewave for this purpose, and a pulse control unit 40 for accurately controlling an SCR trigger signal to a desired frequency And the magnetic output unit 30 is composed of the SCR 310, the leakage transformer 330, and the discharge tube 320.

The magnetic output unit 30 precisely switches the commercial frequency alternating current (60 Hz) from the primary side of the leakage transformer to the pulse control unit 40, thereby applying a high voltage pulse to the secondary discharge tube 320.

The input signal unit 10 of the present invention is a circuit unit that applies a sinusoidal signal of an input power source to the zero voltage switch 20 (ZCS (zero cross switch)). The input signal unit 10 reduces the 220V input voltage to 9V, And rectifies and outputs it.

The zero voltage switch 20 (ZCS) generates a pulse signal by detecting a zero voltage point of the input power source. In FIG. 1, the zero voltage switch 20 includes a differentiator 200 and an amplifier 210 are shown.

1, when the pulse signal of the input signal unit 10 is input to the base of the first transistor of the differentiator 200 and the output of the differentiator 200 is amplified by the amplifier 210, A 5V square wave having a pulse width of 500 mu s is output at the point where the base of the first transistor becomes zero.

The SCR 310 is used as a switching element for switching the full-wave rectified voltage from the input power source by the diode bridge circuit 300. The magnetic output unit 30 converts the switched low- A high-voltage leakage transformer 330 (primary: 220 V, secondary: 18 kV) for the neon transformer was used.

In addition, a reflux diode and a resistor are connected in parallel to the primary side of the leakage transformer in order to discharge the energy accumulated in the inductive load of the leakage transformer 330 to prevent the magnetic flux of the leakage transformer 330 from being saturated. The discharge tube 320 is connected to the secondary side of the discharge tube 320.

The discharge tube 320 is composed of a discharge bank and a coil probe as shown in FIG. 3, and is a known device for converting the energy of the secondary side of the leakage transformer into a magnetic pulse.

Generally, in order to stimulate the nerve with a magnetic pulse, the electric field induced by the time-varying magnetic field should be enough to stimulate the nerve. It is necessary to induce an electric field of several tens V / m or more in the nerve region, To induce an electric field, a magnetic field of 12 Tesla must be switched within a short time of 200 seconds from the shape of the magnetic pole coil to the nerve region from the epidermis.

In order to generate such a magnetic field, a coil of about 0.5 cm in diameter and several tens of turns must be capable of instantaneously flowing several thousand amperes.

A large amount of current is instantaneously applied to the coil to charge the capacitor and charge it temporarily to the coil. When current flows through the coil, it is generated in the magnetic field around the coil by the right hand rule of the fingering. The electric field is induced in the vertical direction.

When time varying magnetic field is applied around an electrical conductor such as metal, eddy current occurs in the conductor. The average electrical conductivity of the human body is about 0.3 Simens / m. In comparison, the electrical conductivity is very low, but it has the property of a conductor.

Therefore, when a time-varying magnetic field is applied around the human body, an eddy current can be induced in the human body like a general electric conductor. The eddy current induced by the time-varying magnetic field has the same effect as the direct current application using an electrode in the human body.

In the embodiment of the present invention, the coil probe has an inner diameter of 8 mm and an outer diameter of 10 mm. In order to prevent interference with the wire, the coil probe is primarily made of glass fiber with a withstand voltage of 1,500 V, 0.2 mm material was used. Secondly, withstand voltage of 5,000 V and thickness (t) of 0.2 mm were used for complete shielding.

The overall length of the coil was about 3.5 m, pressed at about 12 cm at the first end, about 60 cm at the rear end, and finally pressed at the last 6 cm end.

For various applications, the material durability was enhanced by heat treatment (650 ° C for 10 minutes) and the tip for 5 minutes (heat treatment for quenching) for various purposes. When pressed, the panel was pressed with 5.4 cm for the first and 6 cm for the second.

In the present invention, the coil probe is formed of a large-sized coil probe, a small-sized coil probe, and an eight-shaped coil probe so that the coil probe can be used depending on the application.

The large coil probe is made of Helix type probe using Litz wire (280 wires), the total turn number is 10turn, the diameter is 150mm, the coil inductance value is about 9H, and the maximum magnetic field strength is 1.2Tesla.

The large coil probe thus designed is designed and manufactured mainly for the treatment of large areas such as back, shoulder, waist, and abdomen.

Small coil probes were made of Helix type using Litz wire (180 wires). The total number of turns is 10 turn and the diameter is 100 mm. The inductance value of this coil is about 9H and the maximum magnetic field strength is 2.2Tesla.

Small coiled bows can be used for small areas such as the neck, elbow, and ankles, and for children.

The 8-shape coil probe was made by connecting two Helix types using Litz wire (150 wires).

The total turn number is 10 turn and the diameter is 80 mm. The inductance value of this coil is about 9H, and the maximum magnetic field strength is 1.2 Tesla.

The 8-coil probe can be used mainly for intensive treatment of the head or a specific area.

Such a coil probe is particularly important in the design of a magnetic stimulator because the magnetic field strength, frequency, train time, pause time and treatment time must be adjusted according to the type of the coil probe.

The pulse control unit 40 of the present invention is a circuit unit that applies a trigger signal to the SCR 310 of the magnetic output unit 30 and outputs the frequency of the input power at a pulse frequency for discharging the magnetic stimulator.

As described above, the input power source using the commercial power source is AC (60 Hz) pulsed by the zero voltage switch and input to the pulse control unit 40. The frequency of the input power is varied by the pulse control unit 40, ) As a trigger signal.

In order to match the phase of the trigger signal with the input of the magnetic output unit 30, the pulse controller 40 receives the input power and acquires the phase information to synchronize with the pulse signal of the zero voltage switch.

1, the pulse controller 40 receives an input power to the A / D converter 400 and shifts the phase of the trigger signal using the phase information of the A / D-converted input power source to synchronize And outputs it to the SCR 310.

The pulse control unit 40 receives the diode bridge circuit full-wave rectified output of the magnetic output unit 30 and the output of the zero voltage switch 20 (ZCS (zero cross switch)) to match the phase angles, The ratio of the output pulse to the SCR trigger pulse of the zero voltage switch 20 (ZCS (zero cross switch)) is adjusted to 1: 1 or 2N: 1 (N is a natural number).

As the SCR is triggered by the output pulse rate, the full-wave rectified input power is modulated with a pulse of 60 Hz or less and output.

Generally, the turn-on-off method of the SCR 310 is known to shorten the pulse rise time and make various shapes of pulses, and it is known that the energy transfer loss due to the increase of the pulse repetition rate can be reduced.

FIG. 1 shows an embodiment of the pulse controller 40, which will be described below.

In the conventional SCR trigger method, the analog trigger method using resistance, capacitance, OP-AMP and the like is the main method. However, the analog trigger method has many difficulties in response to the temperature characteristic of the circuit, aging, and power supply voltage noise.

In the present invention, unlike the conventional trigger method, an AC voltage is input to a main controller using an input voltage sensor without using a 1: 1 synchronous transformer and converted into a synchronous coordinate system voltage.

The measured voltage information is input to a DSP (Digital Signal Processing) board 420, which is a main processor, and the DSP 420 calculates the phase angle by the control angle conversion and the PI controller.

The phase angle is calculated by using a TTL logic device in FPGA (Field Programmable Gate Array) in DSP, and it is loaded as digital value in EPLD (Erasable Programmable Logic Devies). This digital value is pulsed by internal counter of EPLD Trigger on the gate of SCR.

As shown in the embodiment of FIG. 1, the pulse for directly triggering the phase angle created in the DSP to the SCR uses a device such as an FPGA, so that the circuit is very simple, and the linear control, which is a feature of the conventional analog method, Characteristics such as characteristics, aging, power supply voltage noise, and reliability enhancement.

The zero voltage signal of the alternating frequency of the commercial input power from the zero voltage switch 20 (ZCS) is received from the RTCC (Real Time Clock Count) of the DSP as shown in FIG. That is, 120 zero voltage pulse signals per second are applied to the RTCC of the DSP.

In the DSP, 120 zero-voltage signals per second received from the RTCC were applied to the SCR trigger circuit by dividing the zero voltage signal to the desired frequency as shown in Fig.

The pulse repetition rate is freely adjustable as shown in FIG.

Therefore, the trigger signal of the SCR is applied to the SCR gate at the desired frequency in the zero voltage of the input power source.

In the present invention, the pulse repetition rate and the magnetic stimulator output characteristics according to the SCR gate trigger conduction angle and charge / discharge voltage of the magnetic stimulator were compared.

Experiments were carried out with pulse repetition rate of 5Hz ~ 60hz to keep discharge stable and SCR gate trigger conduction angle of 40 ~ 200 °. The output was calculated by converting the coil probe of the magnetic stimulator output stage into a magnetic flux.

When the output intensity is 100% under the experimental conditions, the voltage charged in the capacitor bank of FIG. 3 is 1800V and the comparison voltage is 2.5V. As the output power decreases by 1%, the comparison voltage decreases by 0.00167V.

5 is a voltage waveform of the oscilloscope when the output intensity is 100%, that is, when 1800 V is charged in the capacitor bank. At this time, the comparison voltage is 2.5 V and the reference voltage is 2.5 V.

6 is a comparison voltage waveform of the capacitor bank when the output intensity is 100% and the frequency is 5 Hz, FIG. 7 is a comparison voltage waveform when the output intensity is 50%, FIG. Is a comparison voltage waveform.

9 to 11 show the magnetic stimulator output characteristics according to the pulse repetition rate. Each experimental data represents the average of the results of five experiments. The oscillation started at 5Hz and reached the maximum value at 60Hz, and especially 23W was obtained.

 As the pulse repetition rate increases, the output of the magnetic stimulator increases. The output increases almost linearly up to the pulse repetition rate of 60 Hz. The reason for this is that as the pulse repetition rate increases, the input energy increases. As the electron density in the discharge tube increases, the pumping rate to the upper level increases, and the density reversal increases.

FIGS. 12 and 13 show the result of measuring the output of the magnetic stimulator according to the pulse repetition rate when the pulse repetition rate of the magnetic stimulator is the highest at 60 Hz and the SCR gate trigger conduction angle is 90 degrees. It can be seen that the output is increased by up to 30 times in the other two cases.

FIG. 14 is a graph showing the results of experiments with the SCR gate trigger conduction angle changing from 30 ° to 145 ° by 15 ° at a pulse repetition rate of 60 Hz, and a maximum output was obtained at a conduction angle of 90 °.

Figure 16 shows the profile of a magnetic stimulator at SCR gate trigger conduction angles 45 [deg.], 90 [deg.] And 135 [deg.]. There was no significant change in the magnetic stimulus pulse width according to each conduction angle. Therefore, it is considered that the conduction angle does not greatly affect the pulse width of the magnetic stimulator.

It will be apparent to those skilled in the art that the present invention may be embodied in many other specific forms without departing from the spirit or essential characteristics thereof.

It will be apparent to those skilled in the art that various modifications and variations can be made in the present invention without departing from the spirit and scope of the invention as defined by the appended claims. It is to be understood that the technical spirit of the present invention is to the extent possible.

10: Input signal section 20: Zero voltage switch
30: magnetic output unit 40: pulse control unit
200: differentiator 210: amplifier
300: diode bridge 310: SCR
320: Discharge tube 330: Leakage transformer
400: A / D converter 420: DSP

Claims (2)

An input signal unit for reducing the input power source and subjecting it to full wave rectification by a diode bridge circuit;
A zero voltage switch (ZCS) for receiving an output of the input signal unit and outputting a zero voltage pulse;
A magnetic output unit which is full-wave rectified by the diode bridge circuit and is triggered by the SCR to be applied to the primary side of the leakage transformer, and the discharge tube is connected to the secondary side of the leakage transformer;
(ZCS) and a diode bridge circuit full-wave rectified output of the magnetic output unit to obtain phase information and synchronize with the pulse signal of the zero voltage switch, and then the zero voltage switch 20) (ZCS (Cross Cross Switch)) to a ratio of 1: 1 or 2N: 1 (N is a natural number) ratio of the output pulse to the SCR trigger pulse to apply a trigger signal to the SCR of the magnetic output unit
Composed
And the output of the magnetic output unit is controlled by the frequency output of the input power source. The apparatus of claim 1, wherein the pulse controller
An A / D converter for converting a full-wave rectified output of the diode bridge circuit of the magnetic output unit into a digital signal;
(ZCS) after the output of the A / D converter and the output of the zero crossing switch (ZCS) are received and the phase angles are matched with each other. And a DSP (digital signal processing) board for applying a trigger signal to the SCR of the magnetic output unit.

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