KR20240083850A - Magnetic stimulation device with motor-evoked potentials conversion function - Google Patents

Abstract

The present invention relates to a magnetic stimulation device having an mep conversion function and, more specifically, to a magnetic stimulation device including a function of converting a stimulation protocol of a second magnetic stimulation device distinguished from a first magnetic stimulation device into a stimulation protocol of the first magnetic stimulation device. the present invention has an advantage of maintaining consistency of tms treatment in a hospital and home by allowing a stimulation condition applied from the magnetic stimulation device for hospital and a stimulation condition applied from the magnetic stimulation device for home to be unified.

Description

Magnetic stimulation device with motor-evoked potentials (MEP) conversion function {Magnetic stimulation device with motor-evoked potentials conversion function}

The present invention relates to a magnetic stimulation device with a MEP conversion function, and more specifically, to a function of converting the stimulation protocol of a second magnetic stimulation device, which is distinct from the first magnetic stimulation device, into the stimulation protocol of the first magnetic stimulation device. It relates to magnetic stimulation devices, including:

Transcranial magnetic stimulation (TMS) is a brain stimulation technique that activates or inhibits nerve cells in a specific area of the brain using local magnetic field waves induced on the surface of the head outside the body. The principle of TMS is to apply a strong flow of electricity to an electromagnetic coil to generate a magnetic field with an intensity of several Tesla. This is a method of stimulating the brain by transmitting the fluctuating energy of magnetic field waves to the brain and inducing depolarization in nerve cells up to several centimeters below the coil.

TMS is a representative non-invasive brain stimulation technique, and its therapeutic application is being actively studied for depression, insomnia, obsessive-compulsive disorder, movement disorders, dementia, and brain dysfunction that do not respond well to drug treatment and psychotherapy.

Typically, the recommended treatment time for TMS is once a day, 5 days a week, for approximately 20 minutes, which requires frequent treatment. For example, when magnetic stimulation therapy for about 20 to 50 minutes a day is applied repeatedly over several days to central nervous diseases such as stroke or spinal cord injury, effects on nerve plasticity or nerve regeneration and functional recovery have been reported.

However, since the existing transcranial magnetic stimulation device is not movable, it is difficult to meet this treatment cycle due to the domestic medical market situation. Therefore, there is a need to introduce a miniaturized TMS treatment device that can be easily used at home.

TMS treatment measures the user's MEP (Motor Evoked Potential) using a hospital TMS device, and treatment is performed according to a stimulation prescription with a preset cycle and intensity based on the measured MEP.

Korean Patent Publication No. 10-2120113 (Title of invention: Helmet-type magnetic stimulation device)

The purpose of the magnetic stimulation device of the present invention is to present a technology that allows a stimulation protocol based on a hospital TMS device to be compatible with the at-home device in implementing a home-use TMS device.

In addition, the magnetic stimulation device of the present invention includes a function of converting the TMS stimulation protocol implemented in the second magnetic stimulation device, which is a separate device from the first magnetic stimulation device, into the TMS stimulation protocol implemented in the first magnetic stimulation device. The purpose is to present a device.

The magnetic stimulation device according to an embodiment of the present invention for solving the above-described problems is a first magnetic stimulation device that provides non-invasive treatment by applying a magnetic field to intracranial nerve cells or scalp cells, and is applied to the user's head. It is worn and includes an applicator unit including a magnetic generating coil therein, and a stimulation generator unit connected to the applicator unit to generate magnetic stimulation, wherein the stimulation generator unit is a high voltage generator unit that converts the input power supplied from the power supply unit into high voltage. and an energy storage unit that stores the high voltage generated from the high voltage generator, and an electrical connection relationship between the energy storage unit and the magnetic generating coil is controlled to provide energy or not to provide energy to generate a plurality of magnetic pulses. It includes a switching unit that generates and a control unit that controls the high voltage generator and the switching unit according to a first stimulation protocol, wherein the control unit sets a second stimulation protocol of the second magnetic stimulation device that is distinct from the first magnetic stimulation device. Based on this, determine the first stimulation protocol.

In addition, in the magnetic stimulation device according to an embodiment of the present invention, the first stimulation protocol includes the maximum output electric field value and output intensity data of the first magnetic stimulation device, and the second stimulation protocol includes the second magnetic stimulation device. Includes the maximum output electric field value and output intensity data, wherein the control unit, the maximum output electric field value of the first magnetic stimulation device, the maximum output electric field value of the second magnetic stimulation device, and the output intensity of the second magnetic stimulation device Based on the data, the output intensity of the first magnetic stimulation device can be calculated.

In addition, in the magnetic stimulation device according to an embodiment of the present invention, the control unit controls the second magnetic stimulation device according to the proportion of the maximum output electric field value of the second magnetic stimulation device and the maximum output electric field value of the first magnetic stimulation device. The output intensity of the first magnetic stimulation device can be calculated by converting the output intensity of the stimulation device.

According to the magnetic stimulation device of the present invention described above, the stimulation conditions applied from the hospital magnetic stimulation device and the stimulation conditions applied from the home magnetic stimulation device can be unified, thereby maintaining consistency of TMS treatment in the hospital and at home. There is an advantage to having it.

Additionally, according to the magnetic stimulation device of the present invention, the stimulation protocol of the second magnetic stimulation device that is distinct from the first magnetic stimulation device may be converted into the stimulation protocol of the first magnetic stimulation device, from different magnetic stimulation devices. There is an advantage in allowing consistent TMS treatment to be performed even when TMS stimulation is applied.

Additionally, according to the magnetic stimulation device of the present invention, there is an advantage in allowing users to receive TMS treatment through a miniaturized magnetic stimulation device at home without visiting a separate medical institution.

Figure 1 is a configuration diagram showing a first magnetic stimulation device, which is a helmet-type magnetic stimulation device according to an embodiment of the present invention.
Figure 2 is a perspective view showing a helmet-type applicator unit according to an embodiment of the present invention.
Figure 3 is an exploded view showing the case portion of the helmet-type applicator portion according to an embodiment of the present invention.
Figure 4 is an exploded perspective view of a helmet-type applicator portion according to an embodiment of the present invention.
Figure 5 is a view showing a helmet-type applicator portion according to an embodiment of the present invention as seen from the bottom.
Figure 6 is a configuration diagram showing a stimulus generator according to an embodiment of the present invention.
Figure 7 is a circuit diagram schematically showing the circuit included in the stimulus generator according to an embodiment of the present invention.
Figure 8 is a diagram illustrating an exemplary pulse generated by one embodiment of the present invention.
Figure 9 shows a schematic configuration of a second magnetic stimulation device, which is a conventional magnetic stimulation device for hospital use.

The advantages and features of the present invention and methods for achieving them will become clear by referring to the embodiments described in detail below along with the accompanying drawings. However, the present invention is not limited to the embodiments disclosed below and will be implemented in various different forms. The present embodiments only serve to ensure that the disclosure of the present invention is complete and that common knowledge in the technical field to which the present invention pertains is not limited. It is provided to fully inform those who have the scope of the invention, and the present invention is only defined by the scope of the claims.

Although first, second, etc. are used to describe various components, these components are of course not limited by these terms. These terms are merely used to distinguish one component from another. Therefore, it goes without saying that the first component mentioned below may also be a second component within the technical spirit of the present invention.

In the following embodiments, terms such as include or have mean that the features or components described in the specification exist, and do not exclude in advance the possibility of adding one or more other features or components.

In the drawings, the sizes of components may be exaggerated or reduced for convenience of explanation. For example, the size and shape of each component shown in the drawings are arbitrarily shown for convenience of explanation, so the present invention is not necessarily limited to what is shown.

Like reference numerals refer to like elements throughout the specification.

Each feature of the various embodiments of the present invention can be partially or fully combined or combined with each other, and as can be fully understood by those skilled in the art, various technical interconnections and operations are possible, and each embodiment may be implemented independently of each other. It may be possible to conduct them together due to a related relationship.

Hereinafter, the magnetic stimulation device with the MEP conversion function of the present invention will be described in detail with reference to the attached drawings.

The magnetic stimulation device of the present invention includes a function for converting a TMS stimulation protocol implemented in a second magnetic stimulation device, which is a separate device from the first magnetic stimulation device, into a TMS stimulation protocol implemented in the first magnetic stimulation device. The purpose is to present

Here, the first magnetic stimulation device is an at-home magnetic stimulation device according to an embodiment of the present invention, and the second magnetic stimulation device is a conventional hospital magnetic stimulation device. Figure 1 shows a schematic configuration of a first magnetic stimulation device, which is a helmet-type magnetic stimulation device according to an embodiment of the present invention, and Figure 9 shows a schematic configuration of a second magnetic stimulation device, which is a conventional hospital magnetic stimulation device. It shows.

According to the magnetic stimulation device of the present invention, the stimulation conditions applied from the hospital magnetic stimulation device and the stimulation conditions applied from the home magnetic stimulation device can be unified, so that TMS treatment can be performed consistently at the hospital and at home. .

First, the first magnetic stimulation device, which is an at-home magnetic stimulation device of the present invention, will be described in detail with reference to FIGS. 1 to 8.

Figure 1 is a configuration diagram showing a helmet-type magnetic stimulation device 1000 according to an embodiment of the present invention.

The helmet-type applicator unit 100 is a helmet-type device worn on the user's head and is an applicator that provides non-invasive treatment by applying a magnetic field to intracranial nerve cells or scalp cells.

The stimulation generator 200 is a device that generates a magnetic stimulation signal so that the helmet-type applicator unit 100 applies a magnetic field to intracranial nerve cells or scalp cells. The stimulation generating unit 200 may be connected to the helmet-type applicator unit 100 and the connecting unit 300.

The connection unit 300 is a conduit that transmits the magnetic stimulation signal generated from the stimulation generator 200 to the helmet-type applicator unit 100, and serves to electrically connect the helmet-type applicator unit 100 and the stimulation generator 200. Do it. The connection unit 300 may include a connector that is detachable from the terminal on the helmet-type applicator unit 100 or the terminal on the stimulation generating unit 200.

Figure 2 is a perspective view showing the helmet-type applicator part 100 according to an embodiment of the present invention, and Figure 3 is an exploded view of the case part 110 of the helmet-type applicator part 100 according to an embodiment of the present invention. It is an exploded view, Figure 4 is an exploded perspective view of the helmet-type applicator part 100 according to an embodiment of the present invention, and Figure 5 is a view of the helmet-type applicator part 100 according to an embodiment of the present invention from the bottom. This is a drawing showing.

The helmet-type applicator unit 100 of the present invention provides non-invasive treatment by applying a magnetic field to intracranial nerve cells or scalp cells. 1 to 3, the helmet-type applicator unit 100 according to an embodiment of the present invention includes a case unit 110, a coil fixing unit 120, a magnetic generating coil 130, and a cooling unit 140. and a coil cover member 150.

The case portion 110 is a helmet-shaped case member mounted on the two upper parts of the human body, and is coupled to the lower case portion 111 disposed at a predetermined distance apart from the upper part of the skull and the upper part of the lower case portion 111. It includes an upper case portion 112 forming an internal space 113.

The lower case portion 111 and the upper case portion 112 are formed to be convex upward so as to contact the two sides of the human body and can be mounted on the human scalp at a predetermined distance apart. The lower case part 111 and the upper case part 112 form a cooling space through the cooling part 140 and the internal space 113 in which the magnetic generating coil 130 is installed.

The case portion 110 may further include a blower cover 114 mounted on the blower 141, which will be described later, and the blower cover 114 is the upper case portion 112 as shown in FIG. 3. Alternatively, it may be coupled to the blower 141.

The coil fixing part 120 is a member that supports or fixes the magnetic generating coil 130, and is formed on the lower case part 111 as shown in FIG. 3. The coil fixing part 120 may be formed integrally with the lower case part 111, or may be formed as a separate member and be seated and fixed on the lower case part 111.

The coil fixing part 120 includes a first support part 121 formed to support the outer circumference of the magnetic generating coil 130 when the magnetic generating coil 130 is seated on the coil fixing part 120, and a magnetic generating coil. It includes a second support portion 122 supporting the inner circumference of 130.

The first support part 121 and the second support part 122 are components that support the magnetic generating coil 130 so that it can be stably seated in a set position, and the magnetic generating coil 130 is aligned with the lower case portion 111. It serves to prevent movement in one direction. The first support part 121 and the second support part 122 are preferably formed to have a height corresponding to the height of the magnetic generating coil 130 or the coil diameter of the magnetic generating coil 130.

As shown in FIG. 5 , a bent portion may be formed on the first support portion 121 to facilitate the user inserting or withdrawing the self-generating coil 130 from the coil fixing portion 120.

In addition, the coil fixing part 120 may further include a third support part 123 formed between the first support part 121 and the second support part 122 to support the lower surface of the magnetic generating coil 130. . The third support part 123 keeps the magnetic generating coil 130 spaced apart from the lower case part 111 by a predetermined distance. The third support portion 123 serves to form a space at a predetermined interval below the magnetic generating coil 130 so that the fluid that cools the magnetic generating coil 130 can flow in or out from the cooling hole 142, which will be described later. do.

As shown in FIG. 5, the third support portion 123 may be a plurality of radial rib members connecting the annular first support portion 121 and the second support portion 122. However, the third support portion 123 is not limited to this illustrated shape, and may have a shape different from that shown as long as it is capable of supporting the seated magnetic generating coil 130.

The magnetic generating coil 130 is a member that is seated on the coil fixing unit 120 and generates a magnetic field, and is a coil wound to have a predetermined diameter. The output of the magnetic field generated from the self-generating coil 130 can be adjusted to treat various indications such as depression, autism, dementia, insomnia, and hair loss.

In the helmet-type magnetic stimulation device of one embodiment of the present invention, the magnetic generating coil 130 is illustrated as having an overall oval shape, but is not limited thereto. The self-generating coil 130 may be a coil wound to have various shapes such as circular, oval, figure-8, disk-shaped, polygonal, or butterfly-shaped, and the magnetic generating coil 130 encompasses the general shape of a conventional TMS coil. must be understood as

The cooling unit 140 cools the magnetic generating coil 130 by generating a flow of fluid, that is, air, in the internal space of the case unit. The cooling unit 140 includes a blower 141 that blows air to the magnetic generating coil 130, a cooling hole 142, and a fluid guide unit 143.

The blower 141 is installed in the upper case part 112 to generate air flow in the internal space 113 of the case part 110. The blower 141 is a device that blows heat into the internal space 113 to cool the heat generated from the magnetic generating coil 130, and includes cooling means such as a fan or blower.

The blower 141 is installed in the front or rear of the upper case portion 112 and generates an air flow in the inner space 113 by introducing air into the inner space of the case portion or discharging air from the inner space.

The cooling hole 142 is an open hole formed in the lower case portion 111 to introduce air into the internal space 113 or to discharge air from the internal space. Figure 4 shows that the cooling hole 142 is formed through the lower case portion 111.

The cooling hole 142 is preferably formed in an area between the first support part 121 and the second support part 122 of the coil fixing part 120. Additionally, the cooling hole 142 is preferably formed below the magnetic generating coil 130. Additionally, the cooling hole 142 may be formed adjacent to the second support portion 122 supporting the inner circumference of the magnetic generating coil 130, as shown in FIG. 5 .

The cooling hole 142 may be formed as an annular hole along the circumference of the annular second support portion 122 as shown, or may be formed as an arbitrarily shaped hole spaced at a predetermined interval.

As shown in FIG. 5, the cooling hole 142 is located on the lower side of the magnetic generating coil 130, in the area between the first support part 121 and the second support part 122, especially the magnetic generating coil 130. When formed adjacent to the second support portion 122 supporting the inner circumference of the coil, outside air flows in from the central lower part of the coil, cools the entire lower surface of the magnetic generating coil 130, and then flows to the outside through the blower 141. may be discharged. This configuration and arrangement of the cooling unit 140 is advantageous in that it can achieve uniform cooling of the magnetic generating coil 130, which is a heating element.

Additionally, the cooling unit 140 may further include a fluid guide unit 143 that guides fluid flowing in or out of the cooling hole 142. The fluid guide portion 143 may be a rib member that extends from the cooling hole 142 and guides fluid. The fluid guide unit 143 defines an area through which air introduced from the cooling hole 142 or air discharged from the cooling hole 142 mainly passes.

As shown in FIG. 5, the fluid guide portion 143 may be a rib member installed upright on the lower case portion 12. The fluid guide portion 143 may be formed in a similar form to the third support portion 123 that supports the lower surface of the magnetic generating coil 130. The fluid guide portion 143 may be a plurality of radial rib members formed between the annular first support portion 121 and the second support portion 122, and may be arranged alternately with the third support portion 123. However, the fluid guide part 143 is not limited to this illustrated form, and is of a form that allows the fluid flowing in from the cooling hole 142 to spread uniformly around the magnetic generating coil 130, as shown in the figure. Of course, it can have other shapes.

The cooling unit 140 described above, especially the cooling hole 142 and the fluid guide unit 143, are technical features for maintaining the cooling performance of the helmet-type applicator unit 100 of the present invention to the maximum. The lower surface of the self-generating coil 130 is a part that is close to the human body and is a part where maximum heat generation occurs. In particular, in the case of cooling fluid circulation in which the fluid flowing in from the cooling hole 142 flows out of the blower 141, the cooling hole 142 and the fluid guide portion 143 are formed by a magnetic generating coil ( 130), it is an essential component that allows first contact with the lower surface, so the cooling efficiency in this area can be greatly improved.

Meanwhile, the helmet-type applicator unit 100 according to an embodiment of the present invention may include a coil cover member 150. The coil cover member 150 is a member that covers at least a portion of the magnetic generating coil 130.

FIG. 6 is a configuration diagram showing the stimulus generator 200 according to an embodiment of the present invention, and FIG. 7 schematically shows a circuit included in the stimulus generator 200 according to an embodiment of the present invention. This is a circuit diagram.

The stimulation generator 200 is a device that generates a magnetic stimulation signal that is transmitted to the helmet-type applicator unit 100 so that the helmet-type applicator unit 100 applies a magnetic field to intracranial nerve cells or scalp cells.

The stimulation generator 200 includes a high voltage generator 220 that converts the input power supplied from the power supply unit 210 into high voltage, an energy storage unit 230 that stores the high voltage generated by the high voltage generator 220, and an energy storage unit. It includes a switching unit 240 that controls the energy stored in the unit 230 to be discharged to the self-generating coil 130.

The power unit 210 is a part that is electrically connected to an external input power source and has a first voltage, and includes a high voltage generator 220, a control unit 250 to be described later, a storage unit 260, a communication unit 270, and an input unit 280. , supplies power to the display unit 290.

The high voltage generator 220 is a converter that converts the input power supplied from the power supply unit 210 into high voltage. The high voltage generator 220 converts the input power of the first voltage supplied from the power supply unit 210 into output power of the second voltage. Here, the output power of the second voltage may range from approximately 300 V to 2000 V.

The energy storage unit 230 stores the high voltage generated from the high voltage generator 220. The energy storage unit 230 may include a capacitor charged by the output power of the high voltage generator 220. The energy storage unit 230 includes at least one capacitor, and the capacitor has a capacitance in the range of 20 μF to 200 μF and may be configured to be charged at a voltage of 300 V to 2000 V.

The capacitance of the capacitor may be in the range of 20 μF to 200 μF, preferably in the range of 30 μF to 100 μF, more preferably in the range of 40 μF to 70 μF.

The capacitor can be charged to a voltage of at least 100, 300, 500 or 1000 V or more. The breakdown voltage of the capacitor may be in the range of approximately 150% of the charging voltage. For example, the withstand voltage of the capacitor may be 900V or 1200V or more.

The switching unit 240 controls the electrical connection relationship between the energy storage unit 230 and the magnetic generating coil 130 to provide energy or not to provide energy, thereby generating a plurality of magnetic pulses. In other words, the switching unit 240 performs a function of controlling the charging voltage stored in the capacitor of the energy storage unit 230 to be instantaneously discharged to the magnetic generating coil 130, which is an inductor, and controls the charging and discharging cycle of the LC resonance circuit. By doing so, multiple magnetic pulses are generated. The self-generating coil 130 has an inductance in the range of 10 μH to 500 μH, and the capacitor of the energy storage unit 230 can generate an instantaneous current of 100 A or more in the self-generating coil 130 to generate a plurality of impulses.

The inductance of the coil may range from 10 μH to 500 μH, preferably from 30 μH to 300 μH, more preferably from 70 μH to 150 μH.

The capacitor can provide a current pulse discharge of at least 100, 300, 500 or 1000 A or more. The current may correspond to the value of the peak flux density of the magnetic field generated by the coil.

The switching unit 240 may be any type of switch such as a diode, MOSFET, JFET, IGBT, BJT, thyristor, or a combination thereof.

FIG. 7 illustrates a circuit for providing a high-power pulse to the magnetic generating coil 130 of the helmet-type applicator unit 100.

The proposed circuit includes an energy storage unit 230, for example, for charging the capacitor from the high voltage generator 220, and a switching unit 240, for example for repeatedly switching a switch and for generating a time-varying magnetic field. It includes discharging the capacitor with the magnetic generating coil 130. Referring to FIG. 7, it includes a serial connection to the switching unit 240 and the magnetic generating coil 130. The switching unit 240 and the magnetic generating coil 130 may be connected in parallel with a capacitor that is the energy storage unit 230. The energy storage unit 230 is charged by the high voltage generator 220, and the energy storage unit 230 can then be discharged to the magnetic generating coil 130 through the switching unit 240.

The control unit 250 controls the high voltage generator 220 and the switching unit 240 according to at least one operation mode. Here, at least one operation mode may be determined based on the storage unit 260, the communication unit 270, or the user input unit 280.

Figure 8 is a diagram illustrating an exemplary pulse generated by one embodiment of the present invention.

The control unit 250 generates a plurality of magnetic pulses through the switching unit 240, and the plurality of magnetic pulses include a first section that generates a plurality of impulses and a second section that does not generate an impulse. Additionally, the first section and the second section are repeated multiple times.

Figure 8 illustrates a treatment duty cycle of 10%, with a repetition rate of 10 Hz. Active treatment continues for T1 in the first interval. The active treatment cycle may be referred to as a train. T1 of the first interval may last 2 seconds. Passive treatment continues during T2 in the second interval. The second interval, T2, can last 18 seconds. After T2, cycle T1 is repeated. In this exemplary treatment, a cycle including active and passive cycles may last 20 seconds. Active treatment followed by passive treatment may be referred to as a burst, i.e. a burst comprises one train and a cycle with no magnetic field applied to the patient. Burst time (T3) is equal to T1 + T2. T2 may last for the period of at least one magnetic pulse in the train. A train contains a plurality of pulses, i.e. at least two pulses. Bursts can be applied repeatedly to the patient.

The repetition rate of treatment cycle T1 may range from 0.1 Hz to 50 Hz, more preferably from 1 Hz to 40 Hz, more preferably from 5 Hz to 30 Hz. If the frequency is less than 1Hz, it can provide a soothing function to intracranial nerve cells or scalp cells. If the frequency is 10Hz or higher, it can be given the function of activating intracranial nerve cells or scalp cells. The repetition rate of this treatment cycle can be selectively applied depending on the indication.

The plurality of impulses in the first section may have a magnetic flux density in the range of 0.2 to 2 Tesla, preferably in the range of 0.3 to 1.5 Tesla, more preferably in the range of 0.5 to 1.0 Tesla.

The impulse generated at this time may have a period in the range of 50 ㎲ to 500 ㎲, preferably in the range of 100 ㎲ to 400 ㎲, and more preferably in the range of 200 ㎲ to 300 ㎲.

The storage unit 260 stores data supporting various functions of the helmet-type magnetic stimulation device 1000. The storage unit 260 can store a plurality of application programs (application programs or applications) running on the helmet-type magnetic stimulation device 1000, data for the operation of the helmet-type magnetic stimulation device 1000, and commands. there is. Additionally, the storage unit 260 may temporarily or permanently store input/output data. Additionally, the storage unit 260 can store data related to display and sound. Here, the storage unit 260 is a flash memory type, hard disk type, multimedia card micro type, or card type memory (for example, SD or XD memory, etc.). ), RAM (Random Access Memory), SRAM (Static Random Access Memory), ROM (Read-Only Memory, ROM), EEPROM (Electrically Erasable Programmable Read-Only Memory), PROM (Programmable Read-Only Memory), magnetic It may include at least one type of storage medium among memory, magnetic disk, and optical disk.

Meanwhile, the application program is stored in the storage unit 260, is installed on the stimulation generating unit 200 of the helmet-type magnetic stimulation device 1000, and is used by the control unit 250 to control the helmet-type magnetic stimulation device 1000. It can be driven to perform an operation (or function).

The communication unit 270 may include one or more modules that enable communication between the helmet-type magnetic stimulation device 1000 and the communication system and between the helmet-type magnetic stimulation device 1000 and the user terminal. Additionally, the communication unit may include one or more modules that connect the helmet-type magnetic stimulation device 1000 to one or more networks. This communication unit may include at least one of a wireless Internet module and a short-range communication module.

The control unit 250 controls the overall operation of the helmet-type magnetic stimulation device 1000 based on at least one of user information input through the user input unit 280, information about the treatment time, and information about the frequency of the pulse magnetic field. can do.

The display unit 290 displays (outputs) information processed by the helmet-type magnetic stimulation device 1000. For example, the display unit 290 displays execution screen information of an application running on the helmet-type magnetic stimulation device 1000, information related to the results of treatment, or a UI (User Interface), GUI (Graphic) according to this execution screen information. User Interface) information can be displayed. The display unit 290 can implement a touch screen by forming a layered structure or being integrated with the touch sensor. This touch screen functions as a user input unit 280 that provides an input interface between the stimulus generator 200 and the user, and can simultaneously provide an output interface between the stimulus generator 200 and the user.

Meanwhile, Figure 9 shows a schematic configuration of a second magnetic stimulation device, which is a conventional magnetic stimulation device for hospital use.

The first magnetic stimulation device 1000 of the present invention has a control function that allows the prescription made based on the hospital magnetic stimulation device, which is the second magnetic stimulation device shown in FIG. 9, to be compatible with the first at-home magnetic stimulation device of the present invention. Includes. The at-home magnetic stimulation device according to an embodiment of the present invention has a motor-evoked potentials (MEP) conversion function.

In general, the user's MEP (Motor Evoked Potential) is measured, and the intensity of the electric field of the magnetic stimulation device is controlled to apply up to 80% to 120% of MT (motor threshold).

Here, MEP is measured in proportion to the intensity of the electric field (V/m). In order to convert the second stimulation protocol of the second hospital magnetic stimulation device to the first stimulation protocol of the first magnetic stimulation device for home use, it is necessary to set the MEP value of each magnetic stimulation device. The MEP value of each magnetic stimulation device can be determined by measurement through an electric field meter.

For example, the MEP value of each magnetic stimulation device can be the electric field value measured at 10 Hz at a distance of 2 cm above the center of the coil or transducer using the same electric field meter. This is an exemplary value and the scope of the present invention is not limited to this, but in order to set the MEP value of each magnetic stimulation device, the MEP value can be set by measuring the electric field under the same conditions for each coil or transducer.

At this time, in the case of a circular coil, the center of the coil can be used as the reference point, and in the case of a modified coil shape such as an 8-shaped coil, the representative value of the MEP can be determined by using the point with the highest average measured value as the reference point. .

The control unit 250 generates the first stimulation protocol of the first magnetic stimulation device 1000 through motor-evoked potentials (MEP) conversion based on the second stimulation protocol of the second magnetic stimulation device. The control unit 250 determines the first stimulation protocol based on the second stimulation protocol of the second magnetic stimulation device that is distinct from the first magnetic stimulation device.

The first stimulation protocol of the first magnetic stimulation device 1000 includes the voltage charged in the energy storage unit 230, the current applied from the energy storage unit 230 to the magnetic generation coil 130, and the switching unit 240. ) can be determined by the repetition rate and pulse width that control. The first stimulation protocol includes the maximum output electric field (V/m) value and output intensity (intensity) of the first magnetic stimulation device.

The control unit 250 may determine the first stimulation protocol in the following manner. The control unit 250 receives the maximum output electric field (V/m) value and output intensity (intensity) data of the second magnetic stimulation device. The control unit 250 performs the second magnetic stimulation according to the proportion of the received maximum output electric field value (V/m) of the second magnetic stimulation device and the maximum output electric field value (V/m) of the first magnetic stimulation device 1000. The output intensity of the first magnetic stimulation device 1000 is calculated by converting the output intensity of the device. Explain specific figures as examples. The second magnetic stimulation device may be Remed's ALTMS, a hospital magnetic stimulation device. For example, if the 45% intensity of the hospital magnetic stimulation device is the MT of the user using the magnetic stimulation device of the present invention, the corresponding electric field value can be calculated. If the electric field value of ALTMS, the second magnetic stimulation device, is 190 V/m at 100% intensity, the electric field value is 85.5 V/m at 45% intensity.

At this time, if the electric field value is 160V/m at 100% intensity of the first magnetic stimulation device, which is the at-home magnetic stimulation device of the present invention, the output intensity of the first magnetic stimulation device capable of outputting the same electric field value of 85.5V/m is It can be calculated. The output intensity of the first magnetic stimulation device with an electric field value of 85.5V/m is calculated to be 53%. The control unit 250 may determine the first protocol according to the output intensity converted as described above.

Furthermore, when receiving a second stimulation protocol such as MT, MEP, stimulation period, stimulation mode, etc. determined based on the second magnetic stimulation device, which is a hospital magnetic stimulation device, the control unit 250 converts the second stimulation protocol into the first stimulation protocol of the present invention. Magnetic stimulation can be controlled by converting to the first stimulation protocol of the magnetic stimulation device.

Although embodiments of the present invention have been described above with reference to the attached drawings, those skilled in the art will understand that the present invention can be implemented in other specific forms without changing its technical idea or essential features. You will be able to understand it. Therefore, the embodiments described above should be understood in all respects as illustrative and not restrictive.

This study is supported by the Technology Development Project of the Ministry of SMEs and Startups in 2023 [S3347843]

This work was supported by the Technology development Program(S3347843) funded by the Ministry of SMEs and Startups(MSS, Korea)

1000 … Helmet type magnetic stimulation device
100 … Helmet type applicator part
110 … Case part
111 … lower case part
112 … Upper case part
113 … interior space
114 … Blower cover
120 … coil fixing part
121 … first support
122 … second support
123 … third support
130 … self-generating coil
140 … cooling part
141 … blower
142 … cooling hole
143 … fluid guide part
150 … Coil cover member
151 … fluid guide protrusion
200 … Stimulus generation unit
210 … power supply
220 … High voltage generator
230 … energy storage
240 … switching part
250 … control unit
260 … storage unit
270 … Ministry of Communications
280 … input section
290 … display part
300 … connection

Claims (3)

A first magnetic stimulation device that provides non-invasive treatment by applying a magnetic field to intracranial nerve cells or scalp cells,
It is worn on the user's head and includes an applicator unit containing a magnetic generating coil therein, and a stimulation generating unit connected to the applicator unit to generate magnetic stimulation,
The stimulus generator,
A high voltage generator that converts the input power supplied from the power supply into high voltage, an energy storage portion that stores the high voltage generated from the high voltage generator, and an electrical connection relationship between the energy storage portion and the magnetic generating coil to control the energy. A switching unit that generates a plurality of magnetic pulses by providing or not providing energy, and a control unit that controls the high voltage generator and the switching unit according to a first stimulation protocol,
The control unit,
A magnetic stimulation device, wherein the first stimulation protocol is determined based on a second stimulation protocol of a second magnetic stimulation device that is distinct from the first magnetic stimulation device. According to claim 1,
The first stimulation protocol includes maximum output electric field value and output intensity data of the first magnetic stimulation device,
The second stimulation protocol includes maximum output electric field value and output intensity data of the second magnetic stimulation device,
The control unit,
Calculating the output intensity of the first magnetic stimulation device based on the maximum output electric field value of the first magnetic stimulation device, the maximum output electric field value of the second magnetic stimulation device, and the output intensity data of the second magnetic stimulation device. , magnetic stimulation device. According to clause 2,
The control unit,
Calculate the output intensity of the first magnetic stimulation device by converting the output intensity of the second magnetic stimulation device in proportion to the maximum output electric field value of the second magnetic stimulation device and the maximum output electric field value of the first magnetic stimulation device. A magnetic stimulation device.

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