KR20190108286A - Method for deciding location of ultrasonic transducer - Google Patents

Abstract

According to an embodiment of the present invention, a method to determine the position of an ultrasonic transducer includes: a step of inputting the information of an ultrasonic transducer; a step of setting a target focus; a step of setting a scanning range including the target focus in a skull image of a user photographed in advance; a step of calculating a reflection coefficient R of ultrasonic waves for each transducer position within the scanning range; and a step of determining the position of the transducer having the lowest reflection coefficient R as the position of the transducer. According to the above, a treatment method using an ultrasonic stimulation device is able to raise the ultrasonic focusing efficiency of a single transducer stimulator by determining a position where the average reflection coefficient of the ultrasound beam line is the lowest, which is a position where the reflection loss of ultrasound can be lowest.

Description

METHOD FOR DECIDING LOCATION OF ULTRASONIC TRANSDUCER}

The present invention relates to a method for determining the position of an ultrasonic transducer, and more particularly, in a treatment method using an ultrasonic stimulation apparatus, determining a position where the average reflection coefficient of the ultrasonic beam line is the lowest as the position of the ultrasonic transducer. It relates to a method for doing so.

Conventionally, in order to alleviate pain of a patient or to perform a treatment method for stimulating nerve cells of a specific body part, a method such as inserting an electrode into a patient's body has been used. There was a risk of damage.

Recently, ultrasonic stimulation therapy that can stimulate the affected area without physical invasion has been widely used. Ultrasound can be divided into high intensity ultrasound and low intensity ultrasound according to its intensity. High intensity ultrasound is used for direct treatment such as necrosis of cancer cells or tissues, while low intensity ultrasound It is known that a medical effect can be obtained without heating or necrotic tissue.

Among these, low-intensity ultrasound stimulation devices are widely used to stimulate brain neurons of patients to treat mental diseases such as depressive disorders, schizophrenia, epilepsy, hydration, and the like. However, in the conventional ultrasonic stimulation device for brain stimulation, the ultrasonic wave generated from the transducer passes through the skull and brain of the patient, the focusing speed is reduced, or the ultrasound progress path is changed due to the difference in the medium, so that the focus cannot be focused on the target focus. In order to solve this problem, it has been common to use a plurality of transducer arrays.

Referring to Korean Patent No. 10-1700883, an apparatus for stimulating nerve cells around a spinal cord or spinal cord of a patient using an ultrasound focusing array including a plurality of transducers for outputting a low intensity ultrasound beam is disclosed. In addition, as an example of using ultrasound for brain stimulation, INSIGHTEC Ltd. Transcranial ultrasound therapy device of ExAblate Neuro is composed of dozens of transducers, which is advantageous for focusing but has a disadvantage of being very expensive.

Ultrasonic stimulation apparatus using a single transducer is economical because it is cheaper than using multiple transducers, but the problem is that the ultrasonic beam line is refracted as it passes through the skull and brain tissue, or the efficiency is low because the focusing rate itself is low. have.

CN 104548392 A US 2015-0151142 A1

In order to solve such a problem, it is desirable to improve the focusing speed by using a user-defined acoustic lens or to increase the efficiency by presetting an appropriate position to minimize the refraction or reflection of the ultrasonic beam line.

Accordingly, an object of the present disclosure is to provide a method for determining a position of an ultrasound transducer having the lowest average reflection coefficient of a ultrasound beam line in a treatment method using an ultrasound stimulation device. That is, it aims at increasing the ultrasonic focusing efficiency of a single transducer stimulation apparatus by finding the position which can reduce the reflection loss of an ultrasonic wave most.

It is also an object of the present invention to provide a program for performing a method for determining the position of an ultrasonic transducer in a computer-readable recording medium.

According to one or more exemplary embodiments, a method for determining a position of an ultrasonic transducer includes: inputting information of the ultrasonic transducer; Setting a target focus; Setting a scanning range including the target focus in a skull image of a user photographed in advance; Calculating a reflection coefficient R of ultrasonic waves for each transducer position within the scanning range; And determining the position of the transducer having the lowest reflection coefficient R as the position of the transducer.

In an embodiment, the information of the ultrasonic transducer may include a diameter, a radius of curvature and an acoustic focal length of the ultrasonic transducer.

In one embodiment, it is assumed that the ultrasonic wave is composed of a plurality of equally spaced ultrasonic beam lines, and calculating the reflection coefficient R of the ultrasonic waves, the reflection coefficient Ro for the skull plate of the user of each ultrasonic beam line Calculating; Calculating an average reflection coefficient Ro_avg of the skull shell of the ultrasound; Calculating a reflection coefficient Ri for the skull inner plate of the user of each ultrasound beam line; Calculating an average reflection coefficient Ri_avg for the skull inner plate of the ultrasound; And calculating the reflection coefficient R of the ultrasonic wave based on the average reflection coefficients Ro_avg and Ri_avg.

In one embodiment, the calculating of the reflection coefficient Ro may include calculating, with respect to the skull shell of the user, an angle θ _o between the incident vector and the vertical direction vector of each ultrasound beam line, wherein the reflection The calculating of the coefficient Ri includes calculating, with respect to the skull inner plate of the user, an angle θ _i between the incident vector and the vertical direction vector of each ultrasound beam line, wherein The incident vector and the vertical direction vector of the ultrasound beam line may be determined based on a skull image of a user photographed in advance.

In an embodiment, the calculating of the reflection coefficient R of the ultrasound may include calculating a predetermined number of transducer position candidate groups in the order of decreasing Ro_avg after the calculating of the average reflection coefficient Ro_avg of the skull shell of the ultrasound. The method may further include selecting, and calculating the average reflection coefficient Ri_avg of the cranial inner plate of the ultrasound may be performed only for each of the predetermined number of transducer position candidate groups.

In one embodiment, the scanning range may be determined based on the radius of curvature and the diameter of the ultrasonic transducer, or may be arbitrarily determined by a user.

In one embodiment, a computer program stored on a computer readable recording medium may be provided for performing a method for determining the position of an ultrasonic transducer.

In one embodiment, the guide member for specifying the position of the ultrasonic transducer for irradiating focused ultrasound focused to the focal point, the mask body in the form of a mask on the face of the user, and the ultrasonic transducer can be inserted A positioning tool is formed through the inner and outer surfaces of the mask body, the positioning tool is determined based on a method for determining the position of the ultrasonic transducer according to claim 1, wherein the guide When the ultrasonic transducer is positioned in the positioning sphere while the member is placed on the face of the user, the focus may be naturally located at a predetermined stimulation site of the brain.

According to an embodiment provided herein, in the treatment method using the ultrasonic stimulation apparatus, by determining the position where the average reflection coefficient of the ultrasound beam line is the lowest, that is, the position where the reflection loss of the ultrasound can be lowest, the single transducer stimulation The ultrasonic focusing efficiency of the device can be increased.

As the ultrasound focusing efficiency of the transducer increases, high-intensity ultrasound can be used for direct treatment, such as necrosis of cancer cells or tissues, and low-intensity ultrasound stimulates the affected area without heat or necrosis of the body. The medical effect can be obtained by doing this.

FIG. 1 is a view illustrating focusing an ultrasonic beam on a target focal point in a skull of a user using an ultrasonic transducer.
2 is a view showing the difference between the ultrasonic traveling path at the position where the reflection coefficient is low and the ultrasonic traveling path at the position where the reflection coefficient is high.
3 is a flowchart illustrating a method for determining a position of an ultrasonic transducer, according to an exemplary embodiment.
4 is a diagram illustrating a simulation process of outputting an ultrasound beam line within a scanning range, according to an exemplary embodiment.
5 is a flowchart illustrating a method of calculating a reflection coefficient of an ultrasonic beam line, according to an exemplary embodiment.
FIG. 6 is a diagram illustrating an angle of incidence between an incident vector and a vertical vector of an ultrasonic beam line.
7 is a flowchart illustrating a method of calculating a reflection coefficient of an ultrasonic beam line according to another exemplary embodiment.

DETAILED DESCRIPTION The following detailed description of the invention refers to the accompanying drawings that show, by way of illustration, specific embodiments in which the invention may be practiced. These embodiments are described in sufficient detail to enable those skilled in the art to practice the invention. It should be understood that the various embodiments of the present invention are different but need not be mutually exclusive. For example, certain shapes, structures, and characteristics described herein may be embodied in other embodiments without departing from the spirit and scope of the invention with respect to one embodiment. In addition, it is to be understood that the location or arrangement of individual components within each disclosed embodiment may be changed without departing from the spirit and scope of the invention. The following detailed description, therefore, is not to be taken in a limiting sense, and the scope of the present invention, if properly described, is defined only by the appended claims, along with the full range of equivalents to which such claims are entitled. Like reference numerals in the drawings refer to the same or similar functions throughout the several aspects.

Hereinafter, preferred embodiments of the focused ultrasound stimulation device will be described in detail with reference to the drawings.

FIG. 1 is a view illustrating focusing an ultrasonic beam on a target focal point in a skull of a user using an ultrasonic transducer.

An ultrasonic transducer is a sound source that outputs ultrasonic waves. In the present invention, by adjusting the output according to the site and purpose to be treated, low intensity ultrasound of 3 W / cm 2 (Ispta) or less, as well as high intensity ultrasound output of 3 W / cm 2 (Ispta) or more is possible.

In general, ultrasonic transducers apply piezoelectric or magnetostrictive effects to convert alternating energy of 20 KHz or more into mechanical vibration of the same frequency. For example, the transducer has a structure including a body and a piezoelectric element having one side opened, and the inside of the body is filled with air, and each piezoelectric element may have a structure in which a wire for applying a voltage is connected. The piezoelectric element uses a piezoelectric effect material such as quartz and tourmaline, and the transducer can generate and output ultrasonic waves using the piezoelectric effect of the piezoelectric element. The structure of such a transducer is exemplary only, and is not limited to any particular structure or effect.

The piezoelectric element of the transducer can output ultrasound of appropriate intensity by adjusting the output according to the area and purpose to be treated (for example, high-intensity ultrasound can be used for direct treatment such as necrosis of cancer cells or tissues). And low-intensity ultrasound can obtain a medical effect by stimulating the affected area without heating the body or necrotic tissue), and the outputted ultrasound produces an overlapping beam to form an ultrasound beam.

As shown in FIG. 1, the single ultrasonic transducer 10 may form a plurality of ultrasonic beam lines L1 to L3 focused at one target focal point F. As shown in FIG. The plurality of ultrasonic beam lines L1 to L3 generated by the transducer 10 pass through an intermediate medium (for example, an acoustic medium such as water or hydrogel) and the outer table of skull and skull of the user. It sequentially passes through the inner table of skull to reach the target focal point F in the brain tissue.

The propagation path of each ultrasonic beam line may vary depending on the mechanical / acoustic characteristics such as the diameter, the radius of curvature, and the focal length of the ultrasonic transducer 10, and the shape of the user's skull. It may also vary depending on physical characteristics such as thickness, for example, the curved shape of the skull outer plate 20 and the skull inner plate 30.

The mechanical and acoustic characteristics of the ultrasonic transducer, such as the diameter, radius of curvature, and acoustic focal length, are determined by the transducer's format. The path through which the beamline reaches the body can be calculated.

However, physical features such as the shape of the user's skull (such as the surface curvature or thickness of the skull) vary from person to person, making it difficult to predict the path where the ultrasound beam line is refracted or reflected, and the skull surface is made up of large and small curves. Even in the skull of the same user, the path of the ultrasound beam line varies according to the position of the ultrasound transducer.

Referring to FIG. 2, it can be seen that the ultrasonic traveling path at the position where (A) the reflection coefficient is low and the ultrasonic traveling path at the position where (B) the reflection coefficient is high are different. As shown in (A) of FIG. 2, the refractive index is not high at the position where the reflection coefficient is low, so that the ultrasonic waves outputted from the transducer can easily reach the target focus, but the refractive index is high at the position where the reflection coefficient is high, such as (B). Since most of the ultrasound is reflected off the surface of the skull, the focusing efficiency is low and the therapeutic effect is greatly reduced.

Accordingly, an object of the present invention is to increase the ultrasound focusing efficiency of the single transducer stimulation device and improve the treatment effect by determining the position of the transducer that can lower the reflection loss of the ultrasound. For example, by calculating the reflection coefficients for the skull outer plate 20 and the skull inner plate 30 of each of the ultrasonic beam lines L1, L2, L3 of FIG. 1, the position where the average reflection coefficient is lowest (that is, reflection) is calculated. Location with the lowest loss and high focusing efficiency).

In order to achieve the above object, FIG. 3 shows a flowchart of a method for determining the position of an ultrasonic transducer according to an embodiment.

Referring to FIG. 3, first, inputting information of an ultrasonic transducer is performed (S310). Information on ultrasound transducers includes information that determines the path of ultrasound travel outside the body, such as the diameter of the transducer, Radius of Curvature and Acoustic Focal Length, and the distance between the user's body surface and the transducer. It may include.

Subsequently, a step of setting a target focus is performed (S320). The target focus is the point where a plurality of ultrasound beam lines are focused. The affected part, which requires ultrasonic stimulation for treatment, may be set as the target focus. Under the information of the input ultrasonic transducer, there may be a number of suitable positions for the ultrasonic wave to reach the target focal point. An object of the present invention is to increase the focusing efficiency of the same output by determining the transducer position having the lowest reflection coefficient among a plurality of positions.

Subsequently, a scanning range including the target focus is set in the skull image of the pre-photographed user (S330). The scanning range can be automatically determined based on the radius of curvature and the diameter of the ultrasonic transducer. In one embodiment, a user (eg, a licensee or equivalently qualified person) may optionally determine the scanning range.

As described above, there may be a number of suitable locations at which the ultrasound can reach the target focal point, of which the ultrasound propagation path is within a constant scanning range including the target focal point to determine the transducer location with the lowest reflection coefficient. It is necessary to simulate the process.

Referring to FIG. 4, there is shown a simulation of the propagation paths of the n ultrasound beam lines L1 to Ln within the set scanning range S. Referring to FIG. Since the scanning range S includes the target focus, the ultrasonic beam line can reach the target focus if the ultrasonic transducer is installed within this range.

The present invention is focused on the fact that the reflection coefficient according to the shape of the skull is different for each position, to provide a method for determining the position of the lowest reflection coefficient (that is, the position of the highest focusing efficiency) through the simulation.

The scanning range S can be arbitrarily set by the user, and the wider the range, the higher the probability of finding the position with the lowest reflection coefficient (that is, the position with the highest focusing efficiency), but the amount of computation that needs to be performed. This increases. Conversely, the narrower the range, the faster the computational speed of finding the optimal position, but the lower the probability of finding the optimal position because the position candidate group is limited.

Referring to FIG. 3 again, the step of calculating the reflection coefficient R of the ultrasonic beam line for each transducer position within the set scanning range is performed (S340). When a wave (ultrasound, etc.) is incident on the interface of different media, some are reflected and some are transmitted. Here, the amplitude ratio of the incident wave and the reflected wave is called a reflection coefficient.

The low reflection coefficient R means that the energy of the reflected wave is lower and the transmittance is higher than the incident wave because the refractive index is low, which means that more energy is transferred to the target focus. On the contrary, at the point where the reflection coefficient is high, the refractive index is high and the energy loss is large. Therefore, finding the point where the reflection coefficient is lowest by considering the shape of the cranial surface on which the ultrasound is incident means that a stronger stimulus can be applied at the same output.

A specific embodiment of obtaining the reflection coefficient R will be described later in detail with reference to FIGS. 5 to 7.

Next, a step of determining a position where the reflection coefficient R is the lowest as the position of the ultrasonic transducer is performed (S350). According to an embodiment, such optimal position information may be used to fabricate a user-customized ultrasonic stimulation device or a guide member for inserting the transducer at a predetermined position.

5 is a flowchart illustrating a method of calculating a reflection coefficient of an ultrasonic beam line, according to an exemplary embodiment. Here, it is assumed that the ultrasonic beam line is composed of n beam lines.

First, a step of calculating the reflection coefficient Ro for each of the n beam lines for the skull outer plate 20 of the user is performed (S510).

The reflection coefficient Ro can be calculated by the following formula derived based on Snell's law.

Where ρ ₁₂ is the density ratio of medium 2 (skull) to the density of medium 1 (medium between the skull and ultrasound transducer, eg water, hydrogel, etc.) (medium 2 / medium 1), C ₂₁ is the ratio of the velocity of the ultrasonic wave in the medium 1 to the velocity of the ultrasonic wave in the medium 2 (skull bone) (medium 1 / medium 2).

As shown in FIG. 6, θ _o indicates an angle of incidence formed between the incident vector and the vertical direction vector at the time of incidence of the transducer-cranial incidence of the ultrasonic beam line. The incident angle θ _o may be determined from the skull image of the user and the information of the ultrasound transducer which are previously photographed.

Thereafter, a step of calculating an average reflection coefficient Ro_avg for the skull shell is performed (S520). Since the n ultrasound beam lines have different incidence directions and the skull has a curved shape, different reflection coefficients are applied to each beam line. In operation S520, by calculating the average Ro_avg of each of the reflection coefficients Ro_1 to Ro_n of the n ultrasound beamlines, the position having the lowest reflection coefficient with respect to the skull shell may be determined.

Subsequently, a step of calculating the reflection coefficient Ri of each beam line with respect to the skull inner plate 30 of the user is performed (S530).

Similar to step S510, the reflection coefficient Ri can be calculated by the following formula derived based on Snell's law.

Where ρ ₂₃ is the density ratio of medium 3 (brain tissue) to the density of medium 2 (skull bone) (medium 3 / medium 2), and C ₃₂ is the velocity of ultrasound in medium 3 (brain tissue). The speed ratio of ultrasound in medium 2 (skull) to medium (medium 2 / medium 3).

As shown in FIG. 6, θ _i indicates an angle of incidence formed by the incident vector and the vertical vector when the skull → brain tissue is incident on the ultrasound beam line. The incident angle θ _i may be determined from the pre-photographed skull image of the user and the information of the ultrasound transducer. In an embodiment, the direction of propagation is altered by Snell's law when the ultrasound proceeds from the skull plate 20 to the skull plate 30 and / or from the skull plate 30 to the brain tissue (medium 3) ( Refraction) can be assumed.

Thereafter, calculating the average reflection coefficient Ri_avg for the skull inner plate is performed (S540). In operation S540, a position having the lowest reflection coefficient with respect to the skull inner plate may be determined by calculating the average Ri_avg of the reflection coefficients Ri_1 to Ri_n of the n ultrasound beamlines.

Next, based on the Ro_avg and Ri_avg, calculating the reflection coefficient R of the ultrasonic beam line is performed (S550). Even if the reflection coefficient Ro to the skull shell is low, the energy loss of the ultrasonic wave increases when the reflection coefficient Ri is high according to the shape of the skull inner plate. Therefore, it is effective to obtain the overall reflection coefficient R by considering Ro and Ri comprehensively. .

7 is a flowchart illustrating a method of calculating a reflection coefficient of an ultrasonic beam line according to another exemplary embodiment.

Steps S710 to S720 are performed similarly to steps S510 to S520 described above, and thus redundant descriptions thereof will be omitted.

Subsequently, a step of selecting a predetermined number (m) of transducer position candidate groups in order of decreasing Ro_avg is performed (S730). As described in step S330 of FIG. 3, the scanning range S may be arbitrarily set by the user. However, as the scanning range becomes wider, the amount of calculation increases, so that the average reflection coefficient R is calculated for each transducer position. Slows down.

In this step (S730), m transducer position candidate groups that are sampled in order of average reflection coefficient Ro_avg for the skull shell are selected in this order, and only the subsequent steps are performed to reduce the amount of computation and improve the positioning speed. have.

Subsequently, in step S740, a process of calculating the reflection coefficients Ri (Ri_1 to Ri_n) of each beam line with respect to the skull inner plate of the user is performed for each of the m transducer position candidate groups. The user can set a predetermined number m as a sample, and as the value of m increases, the probability of finding the lowest reflection coefficient (that is, the position with the highest focusing efficiency) increases, but the position where the simulation should be performed It increases the amount of computation. On the contrary, as the value of m decreases, the computational amount decreases and the speed of finding an optimal position is increased. However, since the position candidate group is limited, the probability of finding an optimal position becomes low.

Subsequently, calculating the average reflection coefficient Ri_avg for the skull inner plate (S750) and calculating the reflection coefficient R of the ultrasonic beam line based on the Ro_avg and Ri_avg (S760) are performed. Steps S750 and S760 are performed in a manner similar to those of steps S540 and S550 described with reference to FIG. 5, and thus redundant descriptions thereof will be omitted.

Such a method for determining the position of an ultrasonic transducer may be implemented in the form of program instructions that may be implemented by an application or may be performed by various computer components, and the program may be recorded on a computer-readable recording medium. have. The computer readable recording medium may include program instructions, data files, data structures, etc. alone or in combination. Program instructions recorded on a computer-readable recording medium are those specially designed and constructed for the present invention, and may be known and available to those skilled in the computer software arts.

Examples of computer-readable recording media include magnetic media such as hard disks, floppy disks and magnetic tape, optical recording media such as CD-ROMs, DVDs, and magneto-optical media such as floptical disks. media), and hardware devices specifically configured to store and execute program instructions, such as ROM, RAM, flash memory, and the like. Examples of program instructions include not only machine code generated by a compiler, but also high-level language code that can be executed by a computer using an interpreter or the like. The hardware device may be configured to operate as one or more software modules to perform the processing according to the present invention.

The method of determining the position of the ultrasonic transducer according to the embodiment may be used to manufacture a guide member for positioning the ultrasonic transducer. In performing a procedure of applying an ultrasonic stimulus to a user's brain, a user-customized mask having a positioning hole into which an ultrasonic transducer is inserted may be used. The mask that is custom-made based on the facial contour of the user may be formed to have the transducer locator at an optimal position for focusing the ultrasound at the target focus. Here, the optimum position is determined as the position where the reflection coefficient R is the lowest according to the embodiment described above.

According to the embodiments described above, in the treatment method using the ultrasonic stimulation device by finding the position where the average reflection coefficient of the ultrasonic beam line is the lowest, that is, the position where the reflection loss of the ultrasonic wave can be lowest, a single transducer stimulation device It is possible to increase the ultrasonic focusing efficiency.

Although the present invention described above has been described with reference to the embodiments shown in the drawings, this is merely exemplary, and it will be understood by those skilled in the art that various modifications and variations may be made therefrom. However, such modifications should be considered to be within the technical protection scope of the present invention. Therefore, the true technical protection scope of the present invention will be defined by the technical spirit of the appended claims.

10: ultrasonic transducer
20: skull shell
30: Skull Inner Plate
L1 ~ Ln: Ultrasonic Beam Line
S: ultrasonic scanning range
F: target focus

Claims (8)

A method for determining the position of an ultrasonic transducer,
Inputting information of the ultrasonic transducer;
Setting a target focus;
Setting a scanning range including the target focus in a skull image of a user photographed in advance;
Calculating a reflection coefficient R of ultrasonic waves for each transducer position within the scanning range; And
Determining the position of the transducer having the lowest reflection coefficient, R, as the position of the transducer.
The method of claim 1,
And the information of the ultrasonic transducer comprises a diameter, a radius of curvature and an acoustic focal length of the ultrasonic transducer.
The method of claim 2,
Assume that the ultrasonic wave is composed of ultrasonic beam lines having a plurality of equal intervals,
Calculating the reflection coefficient R of the ultrasonic wave,
Calculating a reflection coefficient Ro for the skull plate of the user of each ultrasound beam line;
Calculating an average reflection coefficient Ro_avg of the skull shell of the ultrasound;
Calculating a reflection coefficient Ri for the skull inner plate of the user of each ultrasound beam line;
Calculating an average reflection coefficient Ri_avg for the skull inner plate of the ultrasound; And
Calculating a reflection coefficient R of the ultrasonic waves based on the average reflection coefficients Ro_avg and Ri_avg.
The method of claim 3,
Computing the reflection coefficient Ro,
Calculating an angle θ _o between the incident vector and the vertical direction vector of each ultrasound beam line with respect to the skull shell of the user,
Computing the reflection coefficient Ri,
Computing an angle θ _i between the incident vector and the vertical direction vector of each ultrasound beam line with respect to the skull inner plate of the user,
The incident vector and the vertical direction vector of the ultrasound beam line with respect to the outer shell and inner shell of the user is determined based on the pre-photographed skull image of the user, the method for determining the position of the ultrasonic transducer.
The method of claim 4, wherein
Calculating the reflection coefficient R of the ultrasonic wave,
After calculating the average reflection coefficient Ro_avg for the skull shell of the ultrasound,
Selecting a predetermined number of transducer position candidate groups in a low-order order of Ro_avg;
Calculating the average reflection coefficient Ri_avg for the skull inner plate of the ultrasound,
Characterized in that it is performed only for each of the predetermined number of transducer position candidate groups.
The method of claim 2,
And the scanning range is determined based on a radius of curvature and a diameter of the ultrasonic transducer or arbitrarily determined by a user.
A computer program stored on a computer readable recording medium for carrying out the method for determining the position of an ultrasonic transducer according to any one of claims 1 to 6.
In performing a procedure of applying an ultrasonic stimulation to the user's brain, as a guide member for specifying the position of the ultrasonic transducer for irradiating focused ultrasound focused on the focus,
A mask body in the form of a mask placed on the user's face,
It includes a positioning hole formed through the inner surface and the outer surface of the mask body so that the ultrasonic transducer can be inserted,
The positioning device is determined based on a method for determining the position of an ultrasonic transducer according to any one of claims 1 to 6,
And the ultrasonic transducer is positioned in the positioning sphere while the guide member is placed on the face of the user. The guide member is naturally positioned at a predetermined stimulation site of the brain.

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