Ultrasound treatment apparatus for forming plurality of thermal coagulation regions continuously in vertical direction, and operating method thereof

Abstract

A probe of an ultrasound apparatus, according to an embodiment of the present invention, comprises a plurality of transducer elements arranged in a lateral direction. The ultrasound apparatus comprises a control circuit that controls the plurality of transducer elements. The control circuit outputs a first control signal group that focuses first ultrasonic signals, generated from a first group of transducer elements from among the plurality of transducer elements, at a first focal point, and outputs a second control signal group that focuses second ultrasonic signals, generated from a second group of transducer elements, at a second focal point. The first focal point and the second focal point are located at different points along a direction perpendicular to the lateral direction, and the size of a first aperture of the first group of transducer elements and the size of a second aperture of the second group of transducer elements may be different.

Description

Ultrasonic treatment device and operating method for forming multiple continuous thermal coagulation zones in a vertical direction

[0001] The present invention relates to an ultrasonic treatment device. Specifically, the present invention relates to a high intensity focused ultrasound (HIFU) device that forms a plurality of continuous thermal coagulation zones in a vertical direction.

[0002] The skin ligament (Retinacula cutis) is a unique tissue, widely present in the face, hands, feet, and breast tissue, but rarely reported elsewhere in the body. The traditional histological view of the subcutaneous tissue is that it consists of a loose matrix of connective tissue with no fibrous differentiation (Clinical Anatomy, May 2004, Volume 17, Issue 4, pages 287-93).

[0003] Although loss of skin elasticity is reported to be a cause of sagging skin, loss of skin elasticity alone is not enough to explain sagging facial skin.

[0004] There are studies showing that the density of skin ligaments in the subcutaneous tissue is negatively correlated with skin sagging and positively correlated with elasticity (Skin Research & Technology, 2018 Feb, Volume 24 Issue 1, Pages 93-98).

[0005] Additionally, devices utilizing radiofrequency for application to the retinacula cutis have been disclosed. For example, a product called BodyTite (registered trademark) exists. Research using this device has reported a greater than 35% increase in skin and soft tissue contraction by applying vertical sequential thermal stimulation up to a cutoff temperature of 69-70°C, the temperature that optimizes fibroseptal network (FSN) contraction and remodeling (The Art of Body Contouring, August 2019).

[0006] The present invention aims to provide a high-intensity focused ultrasound device and an operating method thereof that induces regeneration and / or recovery of skin ligaments to improve skin sagging and contribute to restoring skin elasticity.

[0007] The present invention aims to provide a high-intensity focused ultrasound device and an operating method thereof that can effectively apply thermal stimulation to vertical fibers existing in skin tissue.

[0008] The purpose of the present invention is to form a plurality of thermal coagulations that are continuous in the vertical direction by continuously focusing high-intensity focused ultrasound waves in a direction perpendicular to the skin, and as a result, the plurality of thermal coagulations are connected to each other to form a thermal coagulation having a relatively constant width in a direction parallel to the skin.

[0009] An ultrasonic device according to an embodiment of the present invention includes a probe that generates ultrasonic waves based on a control signal and includes a plurality of transducer elements arranged laterally, a control circuit that outputs the control signal for controlling driving of at least some of the plurality of transducer elements, and a pulser that provides a driving signal to at least some of the plurality of transducer elements based on the control signal, wherein the control circuit outputs a first control signal group that controls a first group of transducer elements among the plurality of transducer elements and focuses first ultrasonic signals generated from the first group of transducer elements on a first focusing point, and outputs a second control signal group that controls a second group of transducer elements among the plurality of transducer elements and focuses second ultrasonic signals generated from the second group of transducer elements on a second focusing point, and wherein the first focusing point and the second focusing point are located at different points along a direction perpendicular to the lateral direction, and the size of the first aperture of the first group of transducer elements and the size of the second aperture of the second group of transducer elements are The aperture sizes can vary.

[0010] A method of operating a high-intensity focused ultrasound device according to an embodiment of the present invention includes a step in which a control circuit outputs a first control signal group for focusing ultrasonic signals generated from a first group of transducer elements among a plurality of transducer elements arranged laterally at a first focusing point, a step in which a pulser provides a driving signal to the transducer elements of the first group based on the first control signal group, a step in which the control circuit outputs a second control signal group for focusing ultrasonic signals generated from a second group of transducer elements among the plurality of transducer elements at a second focusing point, and a step in which the pulser provides a driving signal to the transducer elements of the second group based on the second control signal group, wherein the first focusing point is closer to the probe in a vertical axis direction than the second focusing point, and a size of a first aperture of the transducer elements of the first group may be smaller than a size of a second aperture of the transducer elements of the second group.

[0011] The high-intensity focused ultrasound device and its operating method according to the present invention can induce regeneration and / or recovery of skin ligaments.

[0012] The high-intensity focused ultrasound device and its operating method according to the present invention can effectively apply thermal stimulation to vertical fibers existing in skin tissue.

[0013] The high-intensity focused ultrasound device and its operating method according to the present invention can form a plurality of continuous and uniform thermal coagulations in a direction perpendicular to the skin of a subject. As a result, the plurality of thermal coagulations are connected to each other, forming a thermal coagulation with a relatively constant width in a direction parallel to the skin.

[0014] Figure 1 is a drawing explaining the principle of a conventional vertical fiber stimulation device using high frequency.

[0015] FIG. 2 is a drawing showing a schematic configuration of a high-intensity focused ultrasound device according to one embodiment of the present invention.

[0016] Figure 3 is a drawing illustrating a related technology for forming vertical thermal coagulation using high-intensity focused ultrasound.

[0017] FIGS. 4A and 4B are drawings illustrating a method for forming vertical thermal coagulations of a high-intensity focused ultrasound device according to one embodiment of the present invention.

[0018] FIG. 5 is a drawing illustrating a method for forming vertical thermal coagulations at multiple transverse points of a high-intensity focused ultrasound device according to one embodiment of the present invention.

[0019] FIG. 6 is a drawing illustrating a method for forming three vertical thermal coagulations of a high-intensity focused ultrasound device according to one embodiment of the present invention.

[0020] FIG. 7 is a diagram illustrating control signals and drive signals for forming vertical thermal coagulations of a high-intensity focused ultrasound device according to one embodiment of the present invention.

[0021] FIG. 8 is a drawing illustrating the focus and energy of high-intensity focused ultrasound according to one embodiment of FIG. 7.

[0022] FIGS. 9A to 9C are drawings illustrating the results of a simulation experiment for vertical thermal coagulation formation of a high-intensity focused ultrasound device according to an embodiment of the present invention.

[0023] FIGS. 10A to 10C are drawings explaining experimental results of thermal coagulation formation by a high-intensity focused ultrasound device according to an embodiment of the present invention and thermal coagulation formation by an embodiment of the related technology of FIG. 3.

[0024] FIGS. 11 to 14 are drawings illustrating a method of forming vertical thermal coagulations at multiple transverse points of a high-intensity focused ultrasound device according to one embodiment of the present invention.

[0025] FIGS. 15a and 15b are drawings illustrating a method for forming vertical thermal coagulations of a high-intensity focused ultrasound device according to one embodiment of the present invention.

[0026] FIG. 16 is a drawing illustrating a high-intensity focused ultrasound device according to one embodiment of the present invention.

[0027] FIG. 17 is a drawing explaining an operating method of a high-intensity focused ultrasound device according to one embodiment of the present invention.

[0028]

[0029] Hereinafter, embodiments of the present invention will be described clearly and in detail to the extent that a person having ordinary skill in the art can easily practice the present invention.

[0030] In this specification, ordinal expressions such as first and second do not necessarily imply the order of distance or time, but are merely expressions for distinguishing them from each other.

[0031]

[0032] Figure 1 is a drawing explaining the principle of a conventional high-frequency stimulation device stimulating vertical fibers.

[0033] The internal electrode of the high-frequency stimulator emits a positively charged RF current, and the emitted RF current flows from the positively charged internal electrode to the negatively charged external electrode.

[0034] Necrotic, ablative tissue thermal effects may occur in soft tissues within 1 to 2 cm from the internal electrode, and quasi-necrotic, non-ablative skin thermal stimulation may occur in the dermis.

[0035] The RF energy within 1-2 cm of the inner electrode provides coagulation and ablation to local tissue, fat, blood vessels and fibrous septal network (FSN), and as the RF spreads further toward the outer electrode, the RF spreads further and flows to a much wider and larger surface area electrode, which can produce non-ablative heating as a thermal effect on the skin structure.

[0036] However, a conventional high-frequency stimulation device such as that shown in Fig. 1 cannot provide a constant thermal stimulus in an elongated manner in the same direction as the formation direction of the skin ligament. In other words, the thermal stimulus of a conventional high-frequency stimulation device is very strong in a range close to the internal electrode, and the thermal stimulus becomes weaker as it approaches the external electrode.

[0037] Furthermore, the conventional high-frequency stimulation device of Fig. 1 generates heat only in one area, making it difficult to effectively stimulate vertical fibers within the dermis. Furthermore, the conventional high-frequency stimulation device of Fig. 1 has difficulty horizontally piercing the dermis, which is a tough tissue. Rather, the conventional high-frequency stimulation device of Fig. 1 suffers from the problem of severing vertical fibers due to the needle-shaped internal electrode inserted into the internal tissue for high-frequency stimulation.

[0038] These problems of the conventional high-frequency stimulation device of Fig. 1 were not previously known, and are problems raised by the inventors in this specification.

[0039]

[0040] FIG. 2 is a diagram schematically illustrating a configuration of a high-intensity focused ultrasound device (10) according to an embodiment of the present invention. The configuration of the high-intensity focused ultrasound device (10) of FIG. 2 is exemplary, and other configurations not illustrated in FIG. 2 may be included according to embodiments. For example, the high-intensity focused ultrasound device (10) may additionally include configurations for imaging. The configuration of FIG. 2 will be described with a focus on a configuration for treatment.

[0041] Referring to FIG. 2, a high-intensity focused ultrasound device (10) may include a control device (100) and a probe (200).

[0042] The control device (100) may include a control circuit (110), a pulser (120), and a high voltage power supply (130).

[0043] The control circuit (110) can output a control signal (CS) that controls the operation of at least some of the plurality of transducer elements (TEs).

[0044] In one embodiment, the control circuit (110) can output a control signal (CS) including a delay time of a drive signal (DS) transmitted to the transducer elements (TEs) so that ultrasound is focused on a plurality of ultrasound focusing points. For example, based on the control signal (CS) of the control circuit (110), at least some of the transducer elements (TEs) can receive the drive signal (DS) from the pulser (120) at different times. Focusing point is used in the same sense as focus point.

[0045] In one embodiment, the control circuit (110) may output a control signal (CS) for each transducer element (TE) or for each group including a plurality of transducer elements. For example, if the transducer module (210) includes a total of 64 transducer elements (TEs), the control circuit (110) may output a control signal (CS) corresponding to each of the 64 transducer elements (TEs). Alternatively, the control circuit (110) may output a control signal (CS) corresponding to a group, such as a first group including some of the 64 transducer elements (TEs), a second group including some of the 64 transducer elements (TEs), etc. The control signal (CS) corresponding to a group may include a control signal (CS) corresponding to each of the transducer elements (TEs) included in the group. In the present specification, a control signal (CS) that controls a plurality of transducer elements may be referred to as a control signal group.

[0046] In one embodiment, the control circuit (110) can output a control signal (CS) that indicates the magnitude of the energy and / or voltage of the drive signal (DS) transmitted to the transducer elements (TEs).

[0047] The pulser (120) can output a driving signal (DS) that drives the transducer elements (TEs) based on a control signal (CS) output by the control circuit (110). The driving signal (DS) can be provided to the probe (200). The driving signal (DS) can be an impulse provided to the electrical transducer elements (TEs) so that the transducer elements (TEs) are excited to generate ultrasonic waves.

[0048] A high voltage power supply (130) can provide power to a pulser (120). The pulser (120) can output a driving signal (DS) based on the power provided from the high voltage power supply (130). For example, the peak amplitude of a pulse of the driving signal (DS) can be 50 V or more. The peak amplitude of the pulse is a potential difference value between a high point and a low point of the pulse of the driving signal (DS) (peak to peak), and can be referred to as an output voltage (Voltage peak to peak; Vpp) of the pulser (120).

[0049] The energy and voltage of the drive signal (DS) can be controlled. For example, the pulser (120) can control the pulse duration, energy, and / or peak amplitude of the pulse of the drive signal (DS). The energy of the drive signal (DS) can include the total on-time. The total on-time can be the sum of the pulse durations of the drive signal (DS) provided to the transducer elements (TEs). Depending on the change in the pulse duration, energy, and / or peak amplitude of the pulse of the drive signal (DS), the energy and voltage of the drive signal (DS) change, and as a result, the degree of excitation of the transducer elements (TEs) can change, and the energy of the ultrasound generated by the transducer elements (TEs) can change.

[0050] The parameters of the drive signal (DS) can be determined such that the total energy of the drive signal (DS) can form a coagulation at a focusing point inside the target (ST). For example, the total on-time of the drive signal (DS) can be determined to be 0.3 msec (milliseconds) or more. The drive signal (DS) can be in the form of a continuous waveform or a pulsed waveform. The target can be a human body, and specifically, can include human skin and tissue structures near the skin.

[0051] The transducer module (210) of the probe (200) may include a plurality of transducer elements (TEs).

[0052] Depending on the embodiment, the transducer module (210) may be configured as an integral part of the probe (200) or may be configured in a form that is detachable from the probe (200). For example, the transducer module (210) may be implemented in a detachable form like the cartridge (201b) of FIG. 16.

[0053] Each of the transducer elements (TEs) may be composed of a piezoelectric material. For example, the transducer elements may be composed of lead zirconate titanate (PZT). Each of the transducer elements (TEs) may be excited based on a driving signal (DS). That is, each of the transducer elements (TEs) may vibrate based on the driving signal (DS) and generate an ultrasonic signal. In the present specification, the terms "vibrating," "exciting," or "activating" by an electrical signal provided to the transducer element may be used interchangeably.

[0054]

[0055] A high-intensity focused ultrasound device (10) according to an embodiment of the present invention can focus ultrasound signals generated from each of the transducer elements (TEs) onto a plurality of different focusing points in the axial direction. In one embodiment, the axial direction may be a vertical direction facing the inside of the object and perpendicular to the skin.

[0056] The high-intensity focused ultrasound device (10) can activate multiple groups of transducer elements having different apertures to generate ultrasound waves that are focused on multiple different focusing points. The ultrasound waves focused on the first focusing point (FC1) and the second focusing point (FC2) may be ultrasound waves generated from transducer elements included in different groups. Although FIG. 2 illustrates that the first group of transducer elements consists of four elements and the second group of transducer elements consists of six elements, this is a simplified representation for the sake of explanation. Accordingly, the transducer elements of each group may consist of a different number of elements than that in FIG. 2. In addition, although FIG. 2 illustrates a total of six transducer elements (TEs), this is a simplified representation for the sake of explanation, and the transducer module (210) may include a different number of elements than that in FIG. 2.

[0057] For example, the high-intensity focused ultrasound device (10) can generate a control signal (CS) and a drive signal (DS) so that ultrasound waves are focused on different first focus points (FC1) and second focus points (FC2) in the axial direction. The control circuit (110) can output a first control signal group, and the pulser (120) can generate a first drive signal group based on the first control signal group. Each of the transducer elements of the first group among the transducer elements (TEs) can generate first ultrasonic signals based on the first drive signal group. The control circuit (110) can output a second control signal group, and the pulser (120) can generate a second drive signal group based on the second control signal group. Each of the transducer elements of the second group among the transducer elements (TEs) can generate second ultrasonic signals based on the second drive signal group. The first focus point (FC1) may be closer to the probe (200) in the vertical axis direction than the second focus point (FC2). In one embodiment, the vertical axis direction may refer to a direction perpendicular to the direction in which the transducer elements (TEs) are arranged. The vertical axis direction may face the interior of the object. For example, the vertical axis direction may be a direction perpendicular to the skin.

[0058] A high-intensity focused ultrasound device (10) can form a plurality of coagulations at a plurality of points inside a target object by focusing ultrasound signals generated from each of the transducer elements (TEs) onto a plurality of different focusing points. The high-intensity focused ultrasound device (10) can generate a control signal (CS) and a drive signal (DS) based on the energy of the ultrasound signal focused on the focusing point in order to form a coagulation at a desired focusing point inside the target object.

[0059] For example, a first coagulation (CG1) may be formed around a first focusing point (FC1) by first ultrasonic signals generated based on a first driving signal group of the pulser (120). A second coagulation (CG2) may be formed around a second focusing point (FC2) by second ultrasonic signals generated based on a second driving signal group of the pulser (120). The first focusing point (FC1) and the second focusing point (FC2) may be located on a virtual extension line (VE) along the axial direction.

[0060] In one embodiment, multiple clots formed by the high-intensity focused ultrasound device (10) focusing ultrasound signals at multiple different focus points can be connected to each other. For example, a first clot (CG1) and a second clot (CG2) can be connected to each other. Although FIG. 2 illustrates two clots being formed within the object, the present invention is not limited thereto. The high-intensity focused ultrasound device (10) can form three or more clots within the object.

[0061] In one embodiment, the apertures (A1, A2) of the transducer elements of the first group and the transducer elements of the second group may be different from each other. For example, the second aperture (A2) of the transducer elements of the second group may be larger than the first aperture (A1) of the transducer elements of the first group. The aperture of a group of transducer elements driven to focus an ultrasonic signal at a relatively deeper focus point in the axial direction may be larger than the aperture of a group of transducer elements driven to focus an ultrasonic signal at a relatively shallower focus point.

[0062] In one embodiment, the number of elements constituting the first group of transducer elements and the second group of transducer elements may be different from each other. For example, the number of transducer elements in the second group may be greater than the number of transducer elements in the first group.

[0063] In one embodiment, the first center of the first group of transducer elements and the second center of the second group of transducer elements based on the lateral direction can be identically positioned in the lateral direction.

[0064] The transducer elements (TEs) may be arranged along the lateral direction. Depending on the embodiment, the number of transducer elements (TEs), the overall length, the kerf, the element width, the element shape, and / or the element thickness may vary.

[0065] Depending on the embodiment, the shape of each of the transducer elements (TEs) may be a planar element or a curved element. FIG. 2 illustrates, as an exemplary embodiment, the transducer elements (TE1) composed of concave curved elements in the opposite direction of the direction in which the ultrasound propagates, but in other embodiments, the transducer elements (TEs) may be composed of planar elements. Alternatively, in other embodiments, the transducer elements (TEs) may be composed of concave curved elements in the direction in which the ultrasound propagates.

[0066] In one embodiment, the total length of the transducer elements (TE1) is 72 mm, the element height along the elevation direction is 22 mm, the element thickness is 0.3 mm, the element width is 0.46 mm, the element gap (kerf) is 0.1 mm, and the element curvature can have a circular curvature. When the first group of transducer elements having the first aperture is composed of six elements among the transducer elements according to the above numerical values, the total surface area of ​​the first group of transducer elements is 0.46 x 22 x 6 = 60.72 It can be. The first aperture of the first group of transducer elements can be (0.46 x 6) + (0.1 x 5) = 3.26 mm. When the second group of transducer elements having the second aperture is formed by 8 elements among the transducer elements according to the above figures, the total surface area of ​​the second group of transducer elements is 0.46 x 22 x 8 = 80.96 can be. The first aperture of the transducer elements of the first group can be (0.46 x 8) + (0.1 x 7) = 4.38 mm. That is, the total surface area of ​​the elements constituting a group of transducer elements can be calculated as "single element width x single element height x number of elements constituting the group". The aperture size of the elements constituting a group of transducer elements can be calculated as "(single element width x number of elements constituting the group) + (kerf x (number of elements constituting the group - 1)".

[0067] In one embodiment, to form a coagulation at a focal point located at a predetermined depth in the axial direction of the object, the aperture size of the transducer elements constituting the group of transducer elements may be 3.26 mm or greater. In another embodiment, the aperture size of the transducer elements constituting the group of transducer elements may be 4.38 mm or greater.

[0068] In one embodiment, the number of transducer elements constituting a group of transducer elements may be 6 or more to form a coagulation at a focusing point located at a predetermined depth in the axial direction of the object. For example, the number of transducer elements of a first group driven to form a coagulation at a first focusing point (FC1) may be 6 or more, and the number of transducer elements of a second group driven to form a coagulation at a second focusing point (FC2) may be 8 or more.

[0069] In one embodiment, to form a coagulation at a focal point located at a predetermined depth in the axial direction of the object, the total area of ​​the transducer elements constituting the group of transducer elements is 60 It may be ideal. For example, the total surface area of ​​the first group of transducer elements driven to form a coagulation at the first focus point (FC1) is 60 The total surface area of ​​the second group of transducer elements driven to form a coagulation at the second focus point (FC2) is 80 It could be strange.

[0070] In one embodiment, the probe (200) of the high-intensity focused ultrasound device (10) according to an embodiment of the present invention may include six or more transducer elements (TEs). A coagulation may be formed inside the object by the six or more transducer elements (TEs). According to an implementation example, the probe (200) may include eight or more transducer elements (TEs) capable of coagulation.

[0071] In one embodiment, the probe (200) of the high intensity focused ultrasound device (10) according to an embodiment of the present invention has a total surface area of ​​60 The probe (200) may include transducer elements (TEs) having a total surface area of ​​80 It may include ideal transducer elements (TEs).

[0072] In one embodiment, the thickness of the transducer element may be 0.1 mm or greater, taking into account ease of processing and / or maintenance. In one embodiment, the thickness of the transducer element may be 0.1 to 1.0 mm.

[0073] In one embodiment, the kerf between the transducer elements may be 0.3 mm or less, taking into account ease of processing and / or maintenance. Unlike conventional single-element transducers, the transducer elements according to an embodiment of the present invention are arranged in an array, and as a result, the ultrasound signal generated by the kerf may have grating lobes. In one embodiment, the high-intensity focused ultrasound device (10) according to an embodiment of the present invention may include transducer elements (TEs) with a kerf of 0.3 mm or less, in order to minimize compound lobes.

[0074] In one embodiment, the frequency of the ultrasonic signal generated from the transducer elements (TE1) may be 1 to 10 MHz. Depending on the embodiment, the frequency of the ultrasonic signal may be 0.5 to 20 MHz.

[0075] The above figures are exemplary and may vary based on the size of the clot and / or the energy level of the ultrasound signal. For example, the number of transducer elements of the first group driven to form a clot at the first focus point (FC1) may be 8 or more, and the number of transducer elements of the second group driven to form a clot at the second focus point (FC2) may be 10 or more. The total surface area of ​​the transducer elements of the first group may be 80 It could be strange.

[0076] A high-intensity focused ultrasound device (10) according to an embodiment of the present invention can focus ultrasound signals at a plurality of focus points (or focal areas) by driving a plurality of different groups of transducer elements to form a plurality of coagulations at a plurality of depths along the vertical axis direction inside a target object. The aperture sizes of the plurality of different groups of transducer elements may be different from each other. The focal width of the ultrasound signals focused at each of the plurality of focus points may be constant. The focal width of the ultrasound signals focused at each of the plurality of focus points may be substantially the same. The focal width may refer to the width in the direction horizontal to the skin. For example, the horizontal width of the focal area is constant at each of two or more focus points. Therefore, the high-intensity focused ultrasound device (10) can generate a thermal stimulus of a constant size in the form of continuous coagulations in the vertical axis direction. The high-intensity focused ultrasound device (10) can generate a thermal stimulus of a substantially constant size in the form of continuous coagulations in the vertical axis direction. As a result, multiple clots formed sequentially and connected at two or more depths can ultimately form a final clot extending vertically. The width of the final clot is relatively constant in the direction perpendicular to the skin, and the final clot can be formed into a cylindrical shape.

[0077] In one embodiment, the high-intensity focused ultrasound device (10) can control the width of the ultrasonic sound field of the focusing point. As a result, the high-intensity focused ultrasound device (10) can form the size of the coagulation differently. That is, the high-intensity focused ultrasound device (10) can set the width of the focus area differently according to the user's control and / or preset setting information. For example, the first user control and / or the first setting information may be a first width for the width of the focus area focused at each of the plurality of focusing points, and the second user control and / or the second setting information may be a second width. For example, the high-intensity focused ultrasound device (10) can generate a control signal and a drive signal so that the width of the focus area at each of the plurality of focusing points has the first width. Alternatively, for example, the high-intensity focused ultrasound device (10) can generate a control signal and a drive signal so that the width of the focus area at each of the plurality of focusing points has the second width. Therefore, based on the focal area width set by the user, the high-intensity focused ultrasound device (10) can generate appropriate control signals and driving signals.

[0078] In one embodiment, the high-intensity focused ultrasound device (10) can control the amount of energy delivered to the focusing point by the ultrasonic signal. As a result, the high-intensity focused ultrasound device (10) can form the coagulation at different sizes. That is, the high-intensity focused ultrasound device (10) can set the amount of energy delivered to the focusing point by the ultrasonic signal at different sizes according to the user's control and / or preset setting information. For example, the first user control and / or the first setting information may be a first size for the amount of energy focused at each of the plurality of focusing points, and the second user control and / or the second setting information may be a second size. For example, the high-intensity focused ultrasound device (10) can generate a control signal and a drive signal so that the amount of energy delivered by the ultrasonic signal at each of the plurality of focusing points has the first size. Alternatively, for example, the high-intensity focused ultrasound device (10) can generate a control signal and a drive signal so that the amount of energy delivered by the ultrasonic signal at each of the plurality of focusing points has the second size. Therefore, based on the size of the energy set by the user, the high-intensity focused ultrasound device (10) can generate appropriate control signals and driving signals.

[0079] The high-intensity focused ultrasound device (10) can control the spacing between a plurality of focusing points formed in the axial direction. That is, the high-intensity focused ultrasound device (10) can set the spacing between a plurality of focusing points formed in the axial direction differently according to a user's control and / or preset setting information. For example, a first user control and / or first setting information may set the spacing between a plurality of focusing points along the axial direction to be a first spacing, and a second user control and / or second setting information may set the spacing between a plurality of focusing points to be a second spacing. The high-intensity focused ultrasound device (10) can generate a control signal and a driving signal based on the spacing between a plurality of focusing points along the axial direction.

[0080] The high-intensity focused ultrasound device (10) can control the spacing between a plurality of focusing points formed in the vertical axis direction. That is, the high-intensity focused ultrasound device (10) can set the spacing between a plurality of focusing points formed in the vertical axis direction differently according to the user's control and / or preset setting information. The high-intensity focused ultrasound device (10) can generate a control signal and a driving signal based on the spacing between the plurality of focusing points along the vertical axis direction.

[0081] In one embodiment, the control device (100) may generate an ultrasound image based on the received ultrasound reflected from inside the body by the generated ultrasound signal (ultrasound signal for treatment or a separate ultrasound signal for imaging). In this case, the probe (200) or the control device (100) may include a front-end circuit for processing the ultrasound signal reflected from inside the object (referred to as the received ultrasound signal) into an electrical signal. The front-end circuit may include a low-noise amplifier (NA) and a time gain compensation (TGC) for attenuation compensation. The control device (100) may include an imaging circuit () for processing the electrical signal converted from the received ultrasound signal. The imaging circuit may include an analog-to-digital converter (ADC), a first-input-first-output (FIFO) memory, etc. The digitally processed received ultrasound signal may be received and focused (Rx focusing) by the control circuit (110) or a separate processing circuit. A high-intensity focused ultrasound device (10) can perform scan conversion based on a received ultrasound signal on which receiving focusing has been performed and display the scan-converted received ultrasound signal on a display device.

[0082] In one embodiment, the control circuit (110) can determine whether to operate in an ultrasound imaging mode that images received ultrasound signals or in a treatment mode that radiates high-intensity focused ultrasound signals to the subject. In one embodiment, the control circuit (110) can determine whether to operate in a mode that performs both treatment and imaging simultaneously. For example, some of the transducer elements (TEs) can operate in imaging mode, and others can operate in treatment mode. Alternatively, some of the transducer elements (TEs) can alternate between the imaging mode and the treatment mode over time. When the imaging mode and the treatment mode alternate, the number of transducer elements (TEs) used in the imaging mode and the number of transducer elements (TEs) used in the treatment mode can be the same or different. Furthermore, the transducer elements (TEs) used in the imaging mode and the transducer elements (TEs) used in the treatment mode can be the same elements, or can be different elements.

[0083]

[0084] Figure 3 is a drawing illustrating a related technology for forming vertical thermal coagulation using high-intensity focused ultrasound. The related technology described with reference to Figure 3 cannot be considered prior art, but rather is merely an exemplary technology designed to prepare for the present invention.

[0085] Referring to FIG. 3, an ultrasonic device according to the related art can focus ultrasonic signals onto a plurality of focusing points (FC1, FC2) to form coagulations (RCG1, RCG2) at a plurality of depths along the axial direction inside a target object. The plurality of focusing points (FC1, FC2) can be located on a virtual identical extension line (VE) along the axial direction.

[0086] An ultrasonic device according to the related art can focus ultrasonic signals onto a plurality of focusing points by driving transducer elements of the same group laterally. An ultrasonic device according to the related art can focus ultrasonic signals onto a plurality of focusing points based on the same aperture size.

[0087] For example, an ultrasonic device according to the related art can generate a first control signal based on a first time delay (TG1) and drive transducer elements (E1 to E6) based on the first control signal. The transducer elements (E1 to E6) can generate a first ultrasonic signal, and the first ultrasonic signal can be focused on a first focusing point (FC1) and form a first coagulation (RCG1). An ultrasonic device according to the related art can generate a second control signal based on a second time delay (TG2) and drive the same transducer elements (E1 to E6) based on the second control signal. The transducer elements (E1 to E6) can generate a second ultrasonic signal, and the second ultrasonic signal can be focused on a second focusing point (FC2) and form a second coagulation (RCG2). Therefore, the transducer elements (E1 to E6) that generate the first ultrasonic signal and the second ultrasonic signal are identical, and as a result, the aperture size is also identical.

[0088] An ultrasonic device according to the related art can drive transducer elements of the same group to focus ultrasonic signals onto multiple focusing points. That is, an ultrasonic device according to the related art can change the delay times provided to the transducer elements in order to focus ultrasonic signals onto multiple focusing points. In this case, multiple coagulations (RCG1, RCG2) formed at multiple focusing points are not formed with a uniform size, but rather with different sizes. As described with reference to the experimental results of Fig. 10 below, the multiple coagulations (RCG1, RCG2) formed by the ultrasonic device according to the related art may be formed with different sizes, like water droplets. That is, even when coagulations formed at multiple depths by the ultrasonic device according to the related art are formed so as to be connected to each other, the widths of the final coagulations cannot be formed identically at different depths perpendicular to the skin. That is, the width of the final coagulation cannot be formed uniformly. An ultrasonic device according to the related art cannot generate a thermal stimulus of a constant size along a direction extending in the axial direction.

[0089]

[0090] FIGS. 4A and 4B are diagrams illustrating a method for forming vertically continuous thermal coagulations in a high-intensity focused ultrasound device according to an embodiment of the present invention. For example, after the first coagulation (CG1) of FIG. 4A is formed, the second coagulation (CG2) of FIG. 4B may be formed so as to be continuously connected to the first coagulation (CG1) of FIG. 4A. The embodiment referring to FIGS. 4A and 4B exemplarily illustrates that the second coagulation (CG2) is formed after the first coagulation (CG1). However, the present invention does not exclude that the first coagulation (CG1) is formed after the second coagulation (CG2). That is, the depth of the coagulation and the time at which the coagulation is formed may be unrelated.

[0091] The thermal coagulation formation described with reference to FIGS. 4A and 4B can be performed by the high-intensity focused ultrasound device (10) of FIG. 2. A method for forming vertical thermal coagulations using the high-intensity focused ultrasound device (10) will be described in detail with reference to FIGS. 2, 4A and 4B. The high-intensity focused ultrasound device (10) is described on the premise that it transmits ultrasonic signals into the interior of a target object. Therefore, thermal coagulations can be generated inside the target object.

[0092] The number of transducer elements illustrated in FIGS. 4a and 4b is simplified for explanation purposes. That is, the number of transducer elements according to an embodiment of the present invention is not limited to the number of transducer elements illustrated in FIGS. 4a and 4b and may be different therefrom.

[0093] Referring to FIG. 4A, the pulser (120) of the high-intensity focused ultrasound device (10) according to an embodiment of the present invention can transmit a first drive signal group (DS2 to DS5) to the transducer elements (E2 to E5) of the first group (Group 1). The first drive signal group (DSG1) may be based on the first control signal group output by the control circuit (110). The first control signal may include a time delay of the first drive signal group (DSG1). For example, referring to FIG. 4A, the time delays of the drive signals (DS2, DS5) transmitted to each of the transducer elements (E2, E5) may be the same, and the time delays of the drive signals (DS3, DS4) transmitted to each of the transducer elements (E3, E4) may be the same. The time delay of the driving signals (DS3, DS4) transmitted to each of the transducer elements (E3, E4) may be longer than the time delay of the driving signals (DS2, DS5) transmitted to each of the transducer elements (E2, E5). The time delays of the first driving signal group (DSG1) may be set so that the first ultrasonic signals generated from each of the first group of transducer elements (E2 to E5) are focused on the first focusing point (FC1). Among the driven transducer elements, the farther the transducer element is located from the center of the first aperture (A1), the shorter the time delay of the driving signal it receives. The first focusing point (FC1) may be located at the first depth (D1) in the axial direction. The time delay may mean the degree of delay until the time when the driving signal is transmitted to the transducer element. That is, a transducer element that receives a drive signal after a relatively short time delay can generate an ultrasonic signal at an earlier time than a transducer element that receives a drive signal after a relatively long time delay.

[0094] By focusing the first ultrasonic signals, a first coagulation (CG1) can be formed at a first focusing point (FC1) on a virtual first extension line (VE1) extending in the axial direction from the center of the first aperture (A1) of the transducer elements (E2 to E5) of the first group (Group 1).

[0095] Referring to FIG. 4a, the high-intensity focused ultrasound device (10) according to an embodiment of the present invention does not drive the transducer elements (E1, E6) to generate the first ultrasonic signal. That is, the transducer elements (E1, E6) are not included in the transducer elements (E2 to E5) of the first group (Group 1).

[0096] Referring to FIG. 4B, the pulser (120) of the high-intensity focused ultrasound device (10) according to an embodiment of the present invention can transmit a second drive signal group (DSG2) to the transducer elements (E1 to E6) of the second group (Group 2). The second drive signal group (DSG2) can be based on the second control signal group output by the control circuit (110). The second control signal can include a time delay of the second drive signal group (DSG2). Similar to FIG. 4A, the further the transducer element is located from the center of the aperture, the shorter the time delay of the drive signal it receives. The time delays of the second drive signal group (DSG2) can be set so that the second ultrasonic signals generated from each of the transducer elements (E1 to E6) of the second group (Group 2) are focused on the second focusing point (FC2). The second focus point (FC2) may be located at a second depth (D2) in the axial direction. The second focus point (FC2) may be located further from the probe in the axial direction than the first focus point (FC1). That is, the second focus point (FC2) may be located deeper within the object than the first focus point (FC1). The second depth (D2) may be greater than the first depth (D1).

[0097] In one embodiment, each of the time delays of the second drive signal group (DSG2) may be different from each of the time delays of the first drive signal group (DSG1). For example, the delay time of the second drive signal (DS2) of the first drive signal group (DSG1) transmitted to the transducer element (E2) among the transducer elements (E2 to E5) of the first group (Group 1) may be different from the delay time of the second drive signal (DS2) of the second drive signal group (DSG2) transmitted to the transducer element (E2) among the transducer elements (E1 to E6) of the second group (Group 2).

[0098] By focusing the second ultrasonic signals, a second coagulation (CG2) can be formed at a second focusing point (FC2) on a virtual first extension line (VE1) extending axially from the center of the second aperture (A2) of the transducer elements (E1 to E6) of the second group (Group 2). The first extension line (VE1) of Fig. 4b is identical to the first extension line (VE1) of Fig. 4a. The second ultrasonic signals can be generated at a time after the first ultrasonic signals have been completely emitted into the target object.

[0099] Referring to FIG. 4b, a high-intensity focused ultrasound device (10) according to an embodiment of the present invention drives transducer elements (E2 to E5) and transducer elements (E1, E6) to generate a second ultrasonic signal. That is, the transducer elements (E1, E6) are included in the transducer elements (E1 to E6) of the second group (Group 2). The transducer elements (E2 to E5) included in the transducer elements (E1 to E6) of the second group (Group 2) are identical to the transducer elements (E2 to E5) included in the transducer elements (E2 to E5) of the first group (Group 1). The transducer elements (E1, E6) additionally included in the second group (Group 2) can be added symmetrically to the lateral outer side of the transducer elements (E2 to E5) of the first group (Group 1). The transducer elements (E1, E6) additionally included in the second group (Group 2) may be added in the same number to the outermost side of the transducer elements (E2 to E5) of the first group (Group 1). Accordingly, the center of the first aperture (A1) of the transducer elements (E2 to E5) of the first group (Group 1) and the center of the second aperture (A2) of the transducer elements (E1 to E6) of the second group (Group 2) may be the same.

[0100] Referring to FIGS. 4A and 4B , the size of the first aperture (A1) is different from the size of the second aperture (A2). However, the first F-number (F-number) based on the first aperture (A1) and the first depth (D1) of the first focus point (FC1) is the same as the second F-number based on the second aperture (A2) and the second depth (D2) of the second focus point (FC2). The F-number can be calculated as the depth of the focus point relative to the aperture size.

[0101] That is, the high-intensity focused ultrasound device (10) according to an embodiment of the present invention can drive a plurality of transducer groups having the same F-number but different apertures and aperture sizes, and focus ultrasound signals on a plurality of focusing points, respectively. As a result, the high-intensity focused ultrasound device (10) can focus ultrasound signals so that a plurality of focusing points located at different depths have a uniform focal area width, and as a result, connected clots can form a uniform width. The position of the focusing point can be determined so that the clots are connected to each other. Control signals and driving signals can be generated so that the clots are connected to each other and the connected clots form a uniform width.

[0102] In this specification, different apertures may refer to apertures composed of different transducer elements. In one embodiment, the different apertures may have the same aperture size. For example, referring to FIG. 4B, the groups of transducer elements (E1 to E5) and the groups of transducer elements (E2 to E6) may form different apertures having the same aperture size.

[0103]

[0104] FIG. 5 is a drawing illustrating a method for forming vertical thermal coagulations at a plurality of lateral points of a high-intensity focused ultrasound device according to an embodiment of the present invention. The thermal coagulation formation described with reference to FIG. 5 can be performed by the high-intensity focused ultrasound device (10) of FIG. 2. Parts overlapping or similar to those described with reference to FIGS. 2, 4A, and 4B will be omitted for detailed description. A method for forming vertical thermal coagulations at a plurality of lateral points of the high-intensity focused ultrasound device (10) will be described in detail with reference to FIGS. 2, 4A, 4B, and 5. The transducer elements (E1 to E6) of FIG. 5 may correspond to the transducer elements (E1 to E6) of FIGS. 4A and 4B.

[0105] Referring to FIG. 5, a high-intensity focused ultrasound device (10) according to an embodiment of the present invention can form a first coagulation (CG1) and a second coagulation (CG2) inside a target object according to the description with reference to FIG. 4, and then the pulser (120) can transmit a third drive signal group (DSG3) to the transducer elements (E3 to E6) of the first group (Group 1). The transducer elements (E3 to E6) of the first group (Group 1) generate a third ultrasonic signal based on the third drive signal group (DSG3), and the third ultrasonic signal can be focused on a third focusing point (FC3). A third coagulation (CG3) can be formed by the third ultrasonic signal focused on the third focusing point (FC3).

[0106] After the third ultrasonic signals are completely emitted into the target object, the pulser (120) can transmit a fourth drive signal group (DSG4) to the transducer elements (E2 to E7) of the second group (Group 2). The transducer elements (E2 to E7) of the second group (Group 2) generate a fourth ultrasonic signal based on the fourth drive signal group (DSG4), and the fourth ultrasonic signal can be focused on the fourth focus point (FC4). A fourth coagulation (CG4) can be formed by the fourth ultrasonic signal focused on the fourth focus point (FC4).

[0107] The axial depth of the third focus point (FC3) may be the same as the axial depth of the first focus point (FC1). The axial depth of the fourth focus point (FC4) may be the same as the axial depth of the second focus point (FC2). Therefore, the axial depth of the fourth focus point (FC4) may be deeper than the axial depth of the third focus point (FC3). The third focus point (FC3) and the fourth focus point (FC4) may be located on an imaginary second extension line (VE2) extending in the axial direction from the center of the aperture (A1) of the transducer elements (E3 to E6) of the first group (Group 1) and the center of the aperture (A2) of the transducer elements (E2 to E7) of the second group (Group 2). The second extension line (VE2) may be substantially parallel to the first extension line (VE1) of FIGS. 4a and 4b.

[0108] The size of the second aperture (A2) of the transducer elements (E2 to E7) of the second group (Group 2) that form the fourth ultrasonic signal is larger than the size of the first aperture (A1) of the transducer elements (E3 to E6) of the first group (Group 2) that form the third ultrasonic signal. The size of the first aperture (A1) of Fig. 5 is the same as the size of the first aperture (A1) of Fig. 4a, and the size of the second aperture (A2) of Fig. 5 is the same as the size of the second aperture (A2) of Fig. 4b.

[0109] The third F-number based on the first aperture (A1) and the third focus point (FC3) of Fig. 5 is identical to the fourth F-number based on the second aperture (A2) and the fourth focus point (FC4). Furthermore, the third F-number and the fourth F-number are identical to the first F-number and the second F-number described with reference to Figs. 4a and 4b.

[0110] The transducer elements (E2 to E7) of the second group (Group 2) forming the fourth ultrasonic signal are transducer elements that are spaced laterally apart from the transducer elements (E1 to E6) of the second group (Group 2) forming the second ultrasonic signal of Fig. 4b. The transducer elements (E2 to E5) of the first group (Group 1) of Fig. 4a are positioned laterally at different positions from the transducer elements (E3 to E6) of the first group (Group 1) of Fig. 5. That is, the centers of the apertures of the transducer elements (E2 to E5) of the first group (Group 1) of Fig. 4a and the centers of the apertures of the transducer elements (E3 to E6) of the first group (Group 1) of Fig. 5 are positioned laterally at different positions. Similarly, the transducer elements (E1 to E6) of the second group (Group 2) of Fig. 4a are positioned laterally at different positions from the transducer elements (E2 to E7) of the second group (Group 2) of Fig. 5. That is, the aperture centers of the transducer elements (E1 to E6) of the second group (Group 2) of Fig. 4a and the aperture centers of the transducer elements (E2 to E7) of the second group (Group 2) of Fig. 5 are positioned laterally at different positions.

[0111] Although in FIGS. 4A, 4B, and 5, it is explained assuming that the centers of the apertures of the transducer elements (E2 to E5) of the first group (Group 1) of FIG. 4A and the centers of the apertures of the transducer elements (E3 to E6) of the first group (Group 1) of FIG. 5 differ by one transducer element in the lateral direction, the spacing between the aperture centers may be set differently. That is, the high-intensity focused ultrasound device (10) may set the spacing between the aperture centers differently according to user control and / or preset setting information. For example, the first user control and / or the first setting information may set the spacing between the aperture centers along the lateral direction to be the first spacing, and the second user control and / or the second setting information may set the spacing between the aperture centers along the lateral direction to be the second spacing.

[0112] Therefore, the high-intensity focused ultrasound device (10) can form vertical thermal coagulations at a plurality of lateral points by changing the position of the center of the aperture in the lateral direction and driving the transducer elements corresponding to the changed aperture among the plurality of transducer elements. As a result, the high-intensity focused ultrasound device (10) can uniformly form coagulations at a plurality of depths in a wide range of the target object. That is, the high-intensity focused ultrasound device (10) can generate a thermal stimulus of a substantially constant size in a form extending in the axial direction in a wide range of the target object.

[0113] In the case of conventional high-intensity focused ultrasound devices for skin treatment, multiple thermal coagulations were formed at multiple lateral points by mechanically moving the transducer module itself laterally. In contrast, the high-intensity focused ultrasound device (10) according to an embodiment of the present invention can form multiple thermal coagulations at multiple lateral points through electronic drive. Therefore, thermal coagulations can be formed at multiple lateral points over a wide range of a target object in a relatively short period of time. Furthermore, by uniformly forming coagulations at multiple depths, the efficiency of skin treatment can be increased.

[0114]

[0115] FIG. 6 is a drawing illustrating a method for forming three vertical thermal coagulations successively at multiple depths using a high-intensity focused ultrasound device according to an embodiment of the present invention. The multiple thermal coagulations connected to each other can ultimately form a final coagulation having a single vertically extended cylindrical shape. The thermal coagulation formation described with reference to FIG. 6 can be performed by the high-intensity focused ultrasound device (10) of FIG. 2. Parts overlapping or similar to those described with reference to FIGS. 2, 4a, 4b, and 5 will be omitted for detailed description. The method for forming three vertical thermal coagulations using the high-intensity focused ultrasound device (10) will be described in detail with reference to FIGS. 2 and 6.

[0116] Referring to FIG. 6, a high-intensity focused ultrasound device (10) according to an embodiment of the present invention can transmit a first drive signal group to the transducer elements (E3 to E6) of a first group (Group 1) using the pulser (120) of FIG. 2. The transducer elements (E3 to E6) of the first group (Group 1) generate a first ultrasonic signal based on the first drive signal group, and the first ultrasonic signal can be focused on a first focusing point (FC1). A first coagulation (CG1) can be formed by the first ultrasonic signal focused on the first focusing point (FC1).

[0117] Similarly, the pulser (120) may transmit a second group of drive signals to the transducer elements (E2 to E7) of the second group (Group 2), the transducer elements (E2 to E7) of the second group (Group 2) may generate a second ultrasonic signal, the second ultrasonic signal may be focused on the second focusing point (FC2), and a second coagulation (CG2) may be formed. In addition, the pulser (120) may transmit a third group of drive signals to the transducer elements (E1 to E8) of the third group (Group 3), the transducer elements (E1 to E8) of the third group (Group 3) may generate a third ultrasonic signal, the third ultrasonic signal may be focused on the third focusing point (FC3), and a third coagulation (CG3) may be formed.

[0118] The first focus point (FC1), the second focus point (FC2), and the third focus point (FC3) may be located on an imaginary extension line (VE) extending along the axial direction.

[0119] The sizes of the apertures of the transducer elements (E3 to E6) of the first group (Group 1), the transducer elements (E2 to E7) of the second group (Group 2), and the transducer elements (E1 to E8) of the third group (Group 3) may be different. The centers of the apertures of the respective groups may be located at the same point laterally.

[0120] FIG. 6 illustrates that the transducer elements (E2 to E7) of the second group (Group 2) each have one transducer element added to the outermost lateral side of the transducer elements (E3 to E6) of the first group (Group 1), but a greater number of transducers may be included depending on the embodiment. The same applies to the transducer elements (E1 to E8) of the third group (Group 3).

[0121] Additionally, FIG. 6 illustrates that the transducer elements (E2 to E7) of the second group (Group 2) are added at the outermost continuous positions in the lateral direction of the transducer elements (E3 to E6) of the first group (Group 1), but transducer elements may be added at non-contiguous positions depending on the embodiment. The same applies to the transducer elements (E1 to E8) of the third group (Group 3).

[0122] Although FIG. 6 illustrates that the high-intensity focused ultrasound device (10) forms three clots (CG1, CG2, CG3) at three focusing points (FC1, FC2, FC3) in the axial direction, depending on the embodiment, the high-intensity focused ultrasound device (10) can form four or more clots in the axial direction. That is, the high-intensity focused ultrasound device (10) can set the number of focusing points formed in the axial direction differently according to the user's control and / or preset setting information.

[0123] For example, the first user control and / or first setting information may be a first number of focus points formed in the vertical axis direction. The first user control and / or first setting information may be preset. The first user control and / or first setting information is preset by the user to the high-intensity focused ultrasound device (10), and the high-intensity focused ultrasound device (10) may receive one command (e.g., input of a shot button) from the user. In response to one command from the user, the high-intensity focused ultrasound device (10) may form clots at the first number of focus points in the vertical axis direction based on the first user control and / or the first setting information.

[0124] The second user control and / or second setting information may be a second number of focus points formed in the vertical axis direction. The second user control and / or second setting information may be preset. The second user control and / or second setting information is preset by the user to the high-intensity focused ultrasound device (10), and the high-intensity focused ultrasound device (10) may receive a single command (e.g., input of a shot button) from the user. In response to the single command from the user, the high-intensity focused ultrasound device (10) may form clots at the second number of focus points in the vertical axis direction based on the second user control and / or second setting information.

[0125] In one embodiment, different user controls and / or setting information may be preset to the high-intensity focused ultrasound device (10) as multiple sets. The control circuit of the high-intensity focused ultrasound device (10) may output control signals appropriate for the preset user controls and / or setting information.

[0126] In one embodiment, the preset user control and / or setting information may be that the user presets the depth of each of a plurality of focusing points at which the ultrasound signals are focused. Upon receiving a command from the user (e.g., input of a shot button), the control circuit of the high-intensity focused ultrasound device (10) may control the size of the aperture so that the ultrasound signals are focused at the depth of each of the plurality of preset focusing points of the user, and output delay signals of the transducer elements within the aperture. For example, as in the embodiments described with reference to FIGS. 4A and 4B, the control circuit of the high-intensity focused ultrasound device (10) may sequentially output a first control signal group and a second control signal group in response to a command received from the user (e.g., input of a shot button). A time interval may exist between the output of the first control signal group and the output of the second control signal group.

[0127] In one embodiment, the preset user control and / or setting information may be a user presetting of the energy delivered to the subject by the ultrasound signal. The user may preset the energy delivered to all of the plurality of focusing points, or may preset the energy delivered to at least one of the plurality of focusing points. Upon receiving a command from the user (e.g., input of a shot button), the control circuit of the high-intensity focused ultrasound device (10) may determine the depth of each of the plurality of focusing points based on the preset energy. Alternatively, the control circuit of the high-intensity focused ultrasound device (10) may determine the distance between the plurality of focusing points based on the preset energy. For example, the high-intensity focused ultrasound device (10) may determine that the distance between the plurality of focusing points increases as the energy delivered to the subject is set to be greater. The distance may be a distance along the vertical axis direction. The distance may be a depth difference in the inner direction of the skin of the subject. A high-intensity focused ultrasound device (10) can control the size of an aperture so that ultrasound signals are focused on each of a plurality of determined focusing points, and output delay signals of transducer elements within the aperture.

[0128] In the embodiments described with reference to FIG. 6, one user command is exemplified by inputting a shot button. However, commands can be received from the user in various other ways. For example, the method of receiving a command from the user, such as pressing a pedal, voice input, or the user's touch on an electrical touch button, is not particularly limited.

[0129]

[0130] This is a drawing explaining control signals and drive signals for forming vertical thermal coagulations of a high-intensity focused ultrasound device according to an embodiment of the present invention. The thermal coagulation formation explained with reference to FIG. 7 can be performed by the high-intensity focused ultrasound device (10) of FIG. 2. Parts that overlap or are similar to those explained with reference to FIGS. 2 to 6 will be omitted for detailed description. The control signals and drive signals for forming vertical thermal coagulations of the high-intensity focused ultrasound device (10) will be explained in detail with reference to FIGS. 2 and 7.

[0131] FIG. 7 is described assuming a group composed of transducer elements (E1 to E8), but the number of transducer elements constituting the group may vary depending on the embodiment. FIG. 7 illustrates that the transducer module (210) includes 16 transducer elements, but the number of transducer elements included in the transducer module (210) may vary depending on the embodiment. FIG. 7 exemplarily describes forming one coagulation (CG) at one focus point (FC), but as described with reference to FIGS. 4A to 6, the high-intensity focused ultrasound device (10) can form multiple coagulations at multiple focus points based on the control signal and the drive signal referring to FIG. 7. In addition, the high-intensity focused ultrasound device (10) can form multiple coagulations at multiple lateral points based on the control signal and the drive signal referring to FIG. 7.

[0132] Referring to FIG. 7, the control circuit (110) can generate a control signal group (CS1 to CS8) corresponding to the transducer elements (E1 to E8) included in the group to be driven based on the axial depth of the set focus point (FC). The control signal group can include a plurality of time delays (TD) corresponding to each of the transducer elements (E1 to E8). For example, the control signal group (CS1 to CS8) can include a plurality of time delays (T1 to T8) corresponding to each of the transducer elements (E1 to E8).

[0133] Time delays (TD) corresponding to the axial depth of a focus point (FC) may be stored in advance in the memory device (140). For example, a list of time delays (TD) corresponding to the axial depth of a plurality of focus points (FC) may be stored in the memory device (140) in the form of a table. Alternatively, according to an embodiment, the time delays (TD) may be implemented in a hard-coded form in an FPGA (field programmable gate array).

[0134] In one embodiment, the memory device (140) may be an internal or external RAM (random access memory) of the FPGA. In one embodiment, the memory device (140) may be an internal or external ROM (read only memory) of the FPGA. The type of implementation of the memory device (140) is not particularly limited.

[0135] The pulser (120) can provide a group of drive signals (DS1 to DS8) to each of the transducer elements (E1 to E8) based on a group of control signals (CS1 to CS8). Depending on the embodiment, each drive signal of the group of drive signals (DS1 to DS8) can be directly or indirectly transmitted to each of the transducer elements (E1 to E8). For example, the group of drive signals (DS1 to DS8) can be provided to the transducer elements (E1 to E8) via another element located between the paths of electrical signals between the pulser (120) and the transducer elements (E1 to E8). For example, the group of drive signals (DS1 to DS8) can be provided to the transducer elements (E1 to E8) via a relay or a switch.

[0136] The pulser (120) may include a plurality of channel circuits (C1 to C8). FIG. 7 illustrates that the pulser (120) includes eight channel circuits (C1 to C8). Depending on the embodiment, the number of channel circuits included in the pulser (120) may vary.

[0137] Referring to FIG. 7, the pulser (120) can drive eight channel circuits (C1 to C8) to generate a group of drive signals (DS1 to DS8) corresponding to eight transducer elements (E1 to E8). Thereafter, the pulser (120) can drive eight channel circuits (C1 to C8) to generate a group of drive signals (DS1 to DS8) corresponding to other eight transducer elements (E2 to E9). Alternatively, the pulser (120) can drive eight channel circuits (C1 to C8) to generate a group of drive signals (DS1 to DS8) corresponding to other eight transducer elements (E3 to E10).

[0138] In one embodiment, the pulser (120) may provide each of the drive signals included in the drive signal groups (DS1 to DS8) to each of the corresponding transducer elements (E1 to E8) based on the time delays (T1 to T8) of the control signal groups (CS1 to CS8). For example, the pulser (120) may provide each of the drive signals of the drive signal groups (DS1 to DS8) to each of the corresponding transducer elements (E1 to E8) after a time delayed by each of the time delays (T1 to T8).

[0139] Unlike that illustrated in FIG. 7, the control circuit (110) stores the time delays (T1 to T8) of the control signal group (CS1 to CS8) in separate time delay elements (), and each of the time delay elements can transmit a triggering signal to each of the channel circuits (C1 to C8) of the pulser (120) after a designated time delay. When the channel circuits (C1 to C8) of the pulser (120) receive the triggering signal, they can provide each of the driving signals to each of the corresponding transducer elements (E1 to E8).

[0140] A high-intensity focused ultrasound device (10) can provide a driving signal to the transducer elements based on a time delay in various ways. The method of providing the driving signal to the transducer elements is not limited to the methods described above.

[0141]

[0142] FIG. 8 is a drawing illustrating a driving signal for forming vertical thermal coagulations of a high-intensity focused ultrasound device according to an embodiment of the present invention.

[0143] The driving signals described with reference to FIG. 8 can be generated by the high-intensity focused ultrasound device (10) of FIG. 2. Parts that overlap or are similar to those described with reference to FIGS. 2 to 7 will not be described in detail. The driving signals for forming vertical thermal coagulations of the high-intensity focused ultrasound device (10) will be described in detail with reference to FIGS. 2 and 8.

[0144] FIG. 8 is described assuming a pulser (120) including eight channel circuits (C1 to C8), but the number of channel circuits included in the pulser (120) may vary depending on the embodiment.

[0145] Figure 8 is explained on the premise that the pulser (120) outputs each of the drive signals of the drive signal group after a delay equal to each of the time delays (T1 to T8) of the control signal group (CS1 to CS8).

[0146] Time delays (TD) may be pre-stored in the memory device (140). For example, a list of time delays (TD) corresponding to axial depths of multiple focus points (FC) may be stored in the memory device (140) in table form. Alternatively, depending on the embodiment, the time delays (TD) may be implemented in a hard-coded form in the FPGA.

[0147] In one embodiment, unlike that illustrated in FIG. 8, the control circuit (110) stores the time delays (T1 to T8) of the control signal group (CS1 to CS8) in separate time delay elements, and each of the time delay elements can transmit a respective triggering signal to each of the channel circuits (C1 to C8) of the pulser (120) after a designated time delay. When the channel circuits (C1 to C8) of the pulser (120) receive the triggering signal, each of the drive signals can be provided to each of the corresponding transducer elements (E1 to E8).

[0148]

[0149] Referring to FIG. 8, the control circuit (110) can generate a control signal group (CS1 to CS8) corresponding to the transducer elements (E1 to E8) included in the group to be driven based on the axial depth of the set focus point (FC).

[0150] The channel circuits (C1 to C8) of the pulser (120) can each generate a driving signal group based on each of the control signals included in the control signal group (CS1 to CS8). Depending on the embodiment, the driving signals included in the driving signal group may be monopolar signals or bipolar signals.

[0151] In one embodiment, the pulser (120) can generate a first type of drive signal group (DSG1). Each of the drive signals (DS1 to DS8) included in the first type of drive signal group (DSG1) can be output from the pulser (120) after a time delayed by each of the corresponding time delays (T1 to T8). Accordingly, each of the drive signals (DS1 to DS8) can be output based on a virtual time delay line (VTD). The virtual time delay line (VTD) conceptually illustrates the corresponding time delays (T1 to T8).

[0152] Each of the drive signals (DS1 to DS8) of the first type of drive signal group (DSG1) may be in the form of a pulsed waveform. The length (LT) of the rectangular shape indicated corresponding to each of the drive signals (DS1 to DS8) of the first type of drive signal group (DSG1) may indicate the energy of the ultrasonic signal generated by each of the drive signals (DS1 to DS8). The total on-times of at least some of the drive signals (DS1 to DS8) of the first type of drive signal group (DSG1) may be different. As a result, the energies of at least some of the ultrasonic signals generated by the drive signals (DS1 to DS8) may be different from each other. For example, as the transducer elements corresponding to the drive signals (DS1 to DS8) of the drive signal group (DSG1) move away from an imaginary extension line extending in the axial direction from the center of the aperture, the pulse duration of the drive signal may increase, thereby increasing the energy of the ultrasonic signal generated by the drive signal. Among the drive signals (DS1 to DS8), the pulse duration of the eighth drive signal (DS8) may be longer than the pulse duration of the seventh drive signal (DS7). Accordingly, the energy of the ultrasonic signal generated by the eighth transducer element based on the eighth drive signal (DS8) may be greater than the energy of the ultrasonic signal generated by the seventh transducer element based on the seventh drive signal (DS7).

[0153]

[0154] In one embodiment, the pulser (120) can generate a second type of drive signal group (DSG2). Similar to the first type of drive signal group (DSG1), each of the drive signals (DS1 to DS8) included in the second type of drive signal group (DSG2) can be output from the pulser (120) after a time delayed by the corresponding time delays (T1 to T8).

[0155] The length of the box indicated corresponding to the drive signals (DS1 to DS8) of the second type of drive signal group (DSG2) may represent the energy of each of the drive signals (DS1 to DS8). The total on-time of at least some of the drive signals (DS1 to DS8) of the second type of drive signal group (DSG2) may be the same. For example, the pulse duration of each of the drive signals (DS1 to DS8) may be the same.

[0156]

[0157] In one embodiment, the pulser (120) can control the on-time of each of the drive signals to form an appropriate thermal coagulation at a designated focus point.

[0158] For example, based on the first type of drive signal group (DSG1), the pulser (120) can differently control the pulse duration of the drive signal provided to at least some of the transducer elements corresponding to the drive signals (DS1 to DS8) of the first type of drive signal group (DSG1) based on the total energy applied to the focus point. Alternatively, based on the second type of drive signal group (DSG2), the pulser (120) can equally control the pulse duration of the drive signal provided to each of the transducer elements corresponding to the drive signals (DS1 to DS8) of the second type of drive signal group (DSG2) based on the total energy applied to the focus point. In this case, in order to focus the ultrasonic signal on the focus point of the same depth in the axial direction, the total energy by focusing of the ultrasonic signals formed at the focus point may be the first energy. The total on-time of the driving signals (DS1 to DS8) of the second type of driving signal group (DSG2) can be determined so that the total energy by focusing of the ultrasonic signals formed at the focusing point becomes the first energy.

[0159] In one embodiment, when the focus points are different, the pulser (120) can control the pulse duration of the drive signal provided to each of the transducer elements so that the total energy applied to the focus points is different. In another embodiment, even when the focus points are different, the pulser (120) can control the pulse duration of the drive signal provided to each of the transducer elements so that the total energy applied to the focus points is the same.

[0160] For example, if the depth difference between multiple clots formed in a vertical direction is not large, the pulser (120) can control the pulse duration of the drive signal provided to each of the transducer elements so that the total energy applied to the focusing point is the same. Alternatively, if the depth difference between multiple clots formed in a vertical direction is large, the pulse duration of the drive signal provided to each of the transducer elements can be controlled so that the total energy applied to the focusing point is different.

[0161]

[0162] Figures 9a to 9c are diagrams illustrating simulation experiment results for vertical thermal coagulation formation using a high-intensity focused ultrasound device according to an embodiment of the present invention. For example, Figures 9a to 9c may be simulation experiment results based on the high-intensity focused ultrasound device (10) of Figure 2.

[0163] Fig. 9a illustrates an axial profile of an ultrasonic signal generated by a transducer element of the transducer module (210) of Fig. 2. Referring to Fig. 9a, the intensity of the ultrasonic signal is greatest at a focal point 14.1 mm in the axial direction. The intensity of the ultrasonic signal is very low at points other than the focal point, indicating that the ultrasonic signal is precisely focused at the focal point.

[0164] Fig. 9b illustrates a lateral profile of an ultrasonic signal generated by a transducer element of the transducer module (210) of Fig. 2. Referring to Fig. 9a, the intensity of the ultrasonic signal is greatest at a focal point at a constant axial depth from the center of the aperture, which is the central point in the lateral direction. The intensity of the ultrasonic signal is relatively low at points other than the focal point, indicating that the ultrasonic signal is precisely focused at the focal point.

[0165] FIG. 9C illustrates a lateral profile of ultrasonic signals generated by multiple groups of the transducer module (210) of FIG. 2, which are focused on multiple focusing points. Referring to FIG. 9C, it can be seen that the energy of the ultrasonic signals focused on multiple focusing points is continuously connected to each other, and as a result, the width of the focal area formed at multiple depths along the vertical axis is uniformly formed. That is, the high-intensity focused ultrasound device (10) can generate a thermal stimulus of a substantially constant size in a form extending in the vertical axis direction, and form coagulations having a uniform width and connected to each other.

[0166]

[0167] FIGS. 10A to 10C are diagrams illustrating experimental results of thermal coagulation formation by a high-intensity focused ultrasound device according to an embodiment of the present invention and thermal coagulation formation by the embodiment of FIG. 3. FIG. 10A shows coagulations formed by thermal stimulation by an ultrasound signal radiated to a skin phantom formed of BSA (Bovine Serum Albumin). FIGS. 10B and 10C show coagulations formed by thermal stimulation by an ultrasound signal radiated to a skin phantom formed of PMMA (poly methyl methacrylate). Some of the experimental results of FIGS. 10A to 10C may be experimental results based on the high-intensity focused ultrasound device (10) of FIG. 2, and others may be experimental results based on the ultrasound device according to the related art of FIG. 3.

[0168] Referring to Fig. 10a, the clots on the left show a shape in which multiple clots are connected to each other, formed by focusing ultrasonic signals at multiple focusing points along the vertical axis of the high-intensity focused ultrasound device (10) of Fig. 2. The clots formed by the high-intensity focused ultrasound device (10) on the left are connected to each other, and as a result, are formed in a cylinder shape with a uniform horizontal width. In contrast, the clots on the right formed by the ultrasonic device according to the related art are connected to each other, but do not have a uniform width at the multiple focusing points and are formed in a droplet shape.

[0169] Figure 10b shows experimental results based on the ultrasonic device according to the related technology of Figure 3. Figure 10b shows clots formed by focusing ultrasonic signals at two focusing points along the axial direction by the ultrasonic device according to the related technology. Figure 10b shows that the clots formed by the ultrasonic device according to the related technology were connected to each other, but did not have a uniform width across multiple focusing points and were formed in the shape of droplets.

[0170] Fig. 10c shows experimental results based on the high-intensity focused ultrasound device (10) of Fig. 2. The left side of Fig. 10c shows a clot formed by the high-intensity focused ultrasound device (10) by focusing the ultrasound signal at one focusing point, and the right side shows clots formed by the high-intensity focused ultrasound device (10) by focusing the ultrasound signals at two focusing points along the axial direction. The right side of Fig. 10c shows that the two clots formed by the high-intensity focused ultrasound device (10) are connected to each other, and are formed as a cylinder shape having a uniform width as a result. The high-intensity focused ultrasound device (10) can form a plurality of clots in the vertical direction, such as the left side of Fig. 10c, by driving a plurality of transducer groups multiple times so that the focusing points of the ultrasound signals are changed. A high-intensity focused ultrasound device (10) can change the focusing point by using multiple groups of transducers having the same F-number but different apertures and aperture sizes, thereby forming multiple coagulations in a cylindrical shape that are connected to each other in the vertical direction and have a uniform horizontal width, as shown on the right side of FIG. 10c.

[0171]

[0172] FIGS. 11 to 14 are drawings illustrating a method for forming vertical thermal coagulations at a plurality of lateral points of a high-intensity focused ultrasound device according to an embodiment of the present invention. The thermal coagulation formation described with reference to FIGS. 11 to 14 can be performed by the high-intensity focused ultrasound device (10) of FIG. 2. A method for forming vertical thermal coagulations at a plurality of lateral points of the high-intensity focused ultrasound device (10) will be described in detail with reference to FIGS. 2, 4a, and 4b. Parts that overlap or are similar to those described with reference to FIGS. 2 to 8 will be omitted for detailed description.

[0173] The high-intensity focused ultrasound device (10) according to the embodiment of FIGS. 11 to 14 can form vertical thermal coagulations at a plurality of lateral points based on virtual transducer elements (VR1 to VR4).

[0174] The high-intensity focused ultrasound device (10) according to the embodiments of FIGS. 11 to 14 is described assuming a transducer module (210) including 16 transducer elements, but the transducer module (210) may include a different number of transducer elements depending on the embodiment.

[0175] Referring to FIG. 11, a high-intensity focused ultrasound device (10) can generate a driving signal to focus ultrasound signals at a plurality of focusing points (FC1 to FC3) based on the outermost transducer elements (E1 to E4) of a transducer module (210) and corresponding virtual transducer elements (VR1 to VR4). The virtual transducer elements (VR1 to VR4) do not physically exist and can be used to determine the size of an aperture and the time delay of the driving signals.

[0176] The high-intensity focused ultrasound device (10) can assume a plurality of groups having a first aperture (A1), a second aperture (A2), and a third aperture (A3) based on transducer elements (E1 to E4) and virtual transducer elements (VR1 to VR4). For example, the transducer elements of the first group can include virtual transducer elements (VR3, VR4) and transducer elements (E1, E2). The high-intensity focused ultrasound device (10) can determine time delays on the assumption that all of the transducer elements (VR3, VR4, E1, E2) of the first group generate ultrasonic signals, and can generate drive signals of the transducer elements (E1, E2) of the first group based on the determined time delays. Likewise, the high-intensity focused ultrasound device (10) can generate drive signals of the second group of transducer elements (E1, E2, E3) and drive signals of the third group of transducer elements (E1, E2, E3, E4). For example, the drive signals of the third group of transducer elements (E1, E2, E3, E4) can be based on a time delay (TD1).

[0177] The embodiment of Fig. 11, unlike the embodiment described with reference to Fig. 6, has a different number of ultrasonic signals focused on each of the focusing points (FC1, FC2, FC3). Therefore, the high-intensity focused ultrasonic device (10) according to the embodiment of Fig. 11 can increase the total on-time of the driving signal compared to the embodiment described with reference to Fig. 6.

[0178] Focusing points (FC1, FC2, FC3) at which ultrasonic signals generated by the first group of transducer elements (E1, E2), the second group of transducer elements (E1, E2, E3), and the third group of transducer elements (E1, E2, E3, E4) are focused are located on a virtual extension line (VE) along the axial direction. The centers of the first aperture (A1), the second aperture (A2), and the third aperture (A3) are also located on the virtual extension line (VE). The centers of the first aperture (A1), the second aperture (A2), and the third aperture (A3) may be located between the virtual transducer element (VR4) and the transducer element (E1), as illustrated in FIG. 11. Therefore, the high-intensity focused ultrasound device (10) can form multiple clots in the depth direction corresponding to the outermost part of the lateral length of the transducer module (210).

[0179] Fig. 12 illustrates an embodiment after a coagulation group (CGG1) formed by other coagulations (CG1, CG2, CG3) in the embodiment of Fig. 11. Similar to Fig. 11, the high-intensity focused ultrasound device (10) can generate a driving signal for focusing ultrasound signals on a plurality of focusing points (FC1 to FC3) based on the outermost transducer elements (E1 to E5) of the transducer module (210) and the corresponding virtual transducer elements (VR1 to VR3).

[0180] A high-intensity focused ultrasound device (10) can assume a plurality of groups having a first aperture (A1), a second aperture (A2), and a third aperture (A3) based on transducer elements (E1 to E5) and virtual transducer elements (VR1 to VR3).

[0181] The centers of the first aperture (A1), the second aperture (A2), and the third aperture (A3) are located between the transducer elements (E1, E2). That is, the centers of the apertures (A1 to A3) of FIG. 12 are located at a position that is moved laterally by a certain distance from the centers of the apertures (A1 to A3) of the embodiment of FIG. 11.

[0182] The high-intensity focused ultrasound device (10) can determine time delays on the assumption that all of the transducer elements (VR3, E1, E2, E3) of the first group generate ultrasonic signals, similar to the embodiment of FIG. 11, and can generate drive signals of the transducer elements (E1, E2, E3) of the first group based on the determined time delays. Similarly, the high-intensity focused ultrasound device (10) can generate drive signals of the transducer elements (E1, E2, E3, E4) of the second group and drive signals of the transducer elements (E1, E2, E3, E4, E5) of the third group. For example, the drive signals of the transducer elements (E1, E2, E3, E4, E5) of the third group can be based on the time delay (TD2).

[0183] A high-intensity focused ultrasound device (10) can focus ultrasound signals based on a plurality of transducer groups on each of a plurality of focusing points (FC1, FC2, FC3) located on a virtual extension line (VE) along the axial direction from the center of apertures (A1 to A3), and form clots (CG1, CG2, CG3).

[0184] FIG. 13 illustrates an embodiment after a coagulation group (CGG1) formed by other coagulations (CG1, CG2, CG3) in the embodiment of FIG. 11 and a coagulation group (CGG2) formed by other coagulations (CG1, CG2, CG3) in the embodiment of FIG. 12.

[0185] The high-intensity focused ultrasound device (10) can generate a driving signal to focus ultrasound signals on a plurality of focusing points (FC1 to FC3) based on the outermost transducer elements (E1 to E6) of the transducer module (210) and the corresponding virtual transducer elements (VR1 to VR2), similar to FIGS. 11 and 12.

[0186] A first group based on a first aperture (A1) may be composed of transducer elements (E1 to E4), a second group based on a second aperture (A2) may be composed of transducer elements (E1 to E5) and a virtual transducer element (VR2), and a third group based on a third aperture (A3) may be composed of transducer elements (E1 to E6) and virtual transducer elements (VR1, VR2). The drive signals of the transducer elements (E1, E2, E3, E4, E5, E6) of the third group may be based on a time delay (TD3).

[0187] The high-intensity focused ultrasound device (10) can focus ultrasound signals based on a plurality of transducer groups on each of a plurality of focusing points (FC1, FC2, FC3) located on a virtual extension line (VE) along the axial direction from the center of the apertures (A1 to A3), similar to those described in FIGS. 11 and 12, and form clots (CG1, CG2, CG3).

[0188] Fig. 14 illustrates an embodiment after the coagulation groups (CGG1, CGG2, CGG3) according to the embodiments of Figs. 11 to 13.

[0189] Unlike the embodiments of FIGS. 11 to 13, the high-intensity focused ultrasound device (10) can configure a plurality of transducer groups without using virtual transducer elements. For example, a first group based on a first aperture (A1) can be configured with transducer elements (E3 to E6), a second group based on a second aperture (A2) can be configured with transducer elements (E2 to E7), and a third group based on a third aperture (A3) can be configured with transducer elements (E1 to E8).

[0190] A high-intensity focused ultrasound device (10) can focus ultrasound signals based on a plurality of transducer groups on each of a plurality of focusing points (FC1, FC2, FC3) similar to the embodiment described with reference to FIG. 6, and form clots (CG1, CG2, CG3).

[0191] The high-intensity focused ultrasound device (10) can then form clots at multiple lateral points while moving the center of the aperture laterally, similar to the embodiment described with reference to FIG. 5.

[0192] A high-intensity focused ultrasound device (10) based on the embodiments of FIGS. 11 to 14 can form clots at multiple lateral points in a wide range corresponding to the entire lateral length of the transducer module (210).

[0193]

[0194] FIGS. 15A and 15B are drawings illustrating a method for forming vertical thermal coagulations using a high-intensity focused ultrasound device according to an embodiment of the present invention. FIGS. 15A and 15B illustrate that vertical thermal coagulations according to an embodiment of the present invention can be formed using the high-intensity focused ultrasound device (10) of FIG. 2. Parts that overlap or are similar to the descriptions made with reference to FIGS. 3 to 14 will be omitted for detailed description.

[0195] Referring to FIGS. 15a and 15b, a high-intensity focused ultrasound device (10) can generate an ultrasound signal based on a plurality of transducer groups.

[0196] Referring to Fig. 15a, a first group (Group 1) based on a first aperture (A1) may be composed of transducer elements (E7, E10), and referring to Fig. 15b, a second group (Group 2) based on a second aperture (A2) may be composed of transducer elements (E6 to E11). Ultrasonic signals generated from the transducer elements (E7, E10) of the first group (Group 1) of Fig. 15a may be focused on a first focusing point (FC1) to form a first coagulation (CG1). Ultrasonic signals generated from the transducer elements (E6 to E11) of the second group (Group 2) of Fig. 15b may be focused on a second focusing point (FC2) to form a second coagulation (CG2).

[0197] That is, the high-intensity focused ultrasound device (10) according to the embodiments of FIGS. 15A and 15B may configure some groups of transducer elements not to be contiguous with each other. Some groups of transducer elements may be configured by some of the transducer elements within the aperture corresponding to the group, and other groups of transducer elements may be configured by all of the transducer elements within the corresponding aperture. For example, the transducer elements (E7, E10) of the first group (Group 1) are not contiguous with each other. The transducer elements (E7, E10) of the first group (Group 1) are some of the transducer elements (E7 to E10) within the first aperture (A1). In this case, unlike previous embodiments, the high-intensity focused ultrasound device (10) has a small number of elements that generate ultrasonic signals focused on the first focusing point (FC1) to form the first coagulation (CG1), so the total on-time of the driving signal can be determined taking this into account.

[0198]

[0199] Fig. 16 is a drawing illustrating a high-intensity focused ultrasound device (10-1) according to an embodiment of the present invention. The control device (100) of the high-intensity focused ultrasound device (10-1) according to the embodiment of Fig. 16 may correspond to the control device (100) of the high-intensity focused ultrasound device (10) of Fig. 2.

[0200] The probe (201) of the high-intensity focused ultrasound device (10-1) according to the embodiment of FIG. 16 may include a handpiece (201a) and a cartridge (201b). The handpiece (201a) may be in a form that can be gripped by a user's hand. The cartridge (201b) may have a structure that is detachable from the handpiece (201a).

[0201] In one embodiment, a guide portion for electrical connection terminals and physical connection may be implemented on the handpiece (201a) so that the cartridge (201b) can be coupled to the handpiece (201a). For example, the guide portion may be implemented in the shape of a bar or protrusion protruding from the front end of the handpiece (201a) in the direction in which the cartridge (201b) is coupled.

[0202] In one embodiment, the cartridge (201b) may include a body portion (BD) that forms an external housing, a window (W) that allows ultrasonic waves radiated from the plurality of transducer elements (TE) to pass through the body portion (BD), and a cavity positioned inside the body portion (BD) and between the plurality of transducer elements (TE) and the window (W). The cavity may be filled with a liquid. For example, the cavity may be filled with distilled water.

[0203] Figure 16 illustrates the side (SS) and bottom (BS) of the cartridge (201b).

[0204] In one embodiment, the probe (201) may include a body portion (BD) that includes a plurality of transducer elements (TE) and forms an external housing, a window (W) that allows ultrasonic waves generated from the plurality of transducer elements (TE) to pass through the outside of the body portion (BD), and a cavity between the plurality of transducer elements (TE) located inside the body portion (BD) and the window (W).

[0205] In one embodiment, at least a portion of the body portion (BD) may be configured to be transparent. In this case, the transparent portion of the body portion (BD) may be positioned close to the window (W).

[0206] In one embodiment, the body portion (BD) may include a first portion (PT1) and a second portion (PT2). Depending on the embodiment, the first portion (PT1) and the second portion (PT2) may be formed by combining multiple parts formed of the same material, or may be formed by combining multiple parts formed of different materials.

[0207] In one embodiment, at least one of the first portion (PT1) and the second portion (PT2) may be formed of a transparent material. At least a portion of the interior of the body portion (BD) may be externally observable. For example, if the second portion (PT2) is formed of a transparent material, the user can easily identify the boundary between the bottom surface of the cartridge (201b) in contact with the skin and the skin. Furthermore, if the first portion (PT2) is formed of a transparent material, the user can visually identify any internal defects in the cartridge (201b).

[0208] In one embodiment, the cartridge (201b) may include a plurality of light emitting portions (LD). The light emitting portions (LD) may be formed in a shape extending along the vertical direction (VT) of the body portion (BD). The light emitting portions (LD) may be formed in at least a portion of a length along the vertical direction (VT) of the body portion (BD). For example, the light emitting portions (LD) may be formed in a shape along the vertical direction (VT) in both the first portion (PT1) and the second portion (PT2), or the light emitting portions (LD) may be formed in a shape along the vertical direction (VT) in either the first portion (PT1) or the second portion (PT2). Alternatively, the light emitting portions (LD) may be formed only in a portion of a length along the vertical direction (VT) of the second portion (PT2).

[0209] Each of the light emitting units (LD) may include at least one LED (Light Emitting Diode). Each of the plurality of light emitting units (LD) may be formed at each of the plurality of outer locations of the cartridge (201b). For example, when viewed based on the bottom surface (BS), each of the plurality of light emitting units (LD) may be positioned at the outer periphery of the plurality of transducer elements (TE) and the window (W) based on the central axis of the cartridge (201b). That is, the light emitting units (LD) may be positioned at a corner portion of the cartridge (201b) so as to be recognizable from the outside whether they emit light. Therefore, the user can easily check the boundary between the bottom surface of the cartridge (201b) that touches the skin and the skin. In addition, the range of the skin to which ultrasonic signals are radiated can be easily checked.

[0210] In one embodiment, at least one light source supplying light to the light emitting unit (LD) may be located in the handpiece (201a). The light source may be an LED. In this case, the light emitting unit (LD) may be implemented as an optical waveguide. The cartridge (201b) may include a plurality of optical waveguides. Each of the plurality of optical waveguides may be coupled to each of the LEDs located in the handpiece (201a) to guide the light generated (radiated) from the LEDs. Each of the optical waveguides may be formed at an outer location of the cartridge (201b). For example, when viewed from the bottom surface (BS), each of the plurality of optical waveguides may be located at an outer location of the plurality of transducer elements (TE) and the window (W) based on the central axis of the cartridge (201b). That is, each of the optical waveguides may be located at an edge portion of the cartridge (201b) so that whether the LEDs of the handpiece (201a) are emitting light can be recognized from the outside through the optical waveguide.

[0211] In one embodiment, the probe (201) may include a handpiece (201a) that can be gripped by a user and a cartridge (201b) that can be detachably attached to the handpiece (201a). The cartridge (201b) may include a body (BD), a window (W), and a cavity. The high-intensity focused ultrasound device (10-1) may include an LED that illuminates a transparent portion of the body (BD) in either the handpiece (201a) or the cartridge (201b). The cartridge (201b) may further include an optical waveguide coupled to the LED to guide light emitted from the LED.

[0212]

[0213] FIG. 17 is a drawing illustrating an operating method of a high-intensity focused ultrasound device according to an embodiment of the present invention. The operating method of FIG. 17 can be performed in the high-intensity focused ultrasound device (10) of FIG. 2. The operating method of the high-intensity focused ultrasound device (10) will be described with reference to FIGS. 2 and 17. Detailed descriptions of parts that overlap or are similar to those described above will be omitted.

[0214] At step S110, the high-intensity focused ultrasound device (10) can output a first control signal group for focusing ultrasound signals generated from a first group of transducer elements among a plurality of transducer elements (TEs) arranged laterally of the probe (200) onto a first focusing point (FC1). For example, the first control signal group can include time delays of drive signals provided to each of the first group of transducer elements corresponding to the first aperture (A1).

[0215] At step S120, the pulser (120) may provide a drive signal to the first group of transducer elements based on the first control signal group. The drive signal may be a plurality of signals provided to each of the first group of transducer elements. For example, it may be similar to one of the drive signal groups (DSG1, DSG2) of FIG. 8.

[0216] At step S130, the control circuit (110) may output a second control signal group that focuses ultrasonic signals generated from a second group of transducer elements among a plurality of transducer elements (TEs) on a second focusing point (FC2). For example, the second control signal group may include time delays of drive signals provided to each of the second group of transducer elements corresponding to the second aperture (A2).

[0217] At step S140, the pulser (120) may provide a drive signal to the second group of transducer elements based on the second control signal group. The drive signal may be a plurality of signals provided to each of the second group of transducer elements. For example, it may be similar to one of the drive signal groups (DSG1, DSG2) of FIG. 8.

[0218] For example, in the operating method of the high-intensity focused ultrasound device (10), the first focusing point (FC1) may be closer to the probe (200) in the vertical axis direction than the second focusing point (FC2), and the sizes of the first apertures (A1) of the transducer elements of the first group and the second apertures (A2) of the transducer elements of the second group may be different from each other. For example, the size of the second aperture (A2) may be larger than the size of the first aperture (A1).

[0219] In one embodiment, the number of transducer elements in the second group may be greater than the number of transducer elements in the first group.

[0220] The first focusing point (FC1) and the second focusing point (FC2) are formed in a direction perpendicular to the direction in which the transducer elements (TEs) included in the probe (200) are arranged, and the size of the first aperture of the transducer elements of the first group and the size of the second aperture of the transducer elements of the second group may be different from each other.

[0221]

[0222] Meanwhile, the above-described embodiments are specific examples for implementing the present invention. In addition to the above-described embodiments, the present invention will also include embodiments that can be simply designed or easily modified. Furthermore, the present invention will also include technologies that can be easily modified and implemented using the embodiments. Therefore, the scope of the present invention should not be limited to the above-described embodiments, but should be defined not only by the claims described below but also by equivalents of the claims of the present invention.

[0223]

[0224] 10: High-intensity focused ultrasound device

[0225] 100: Control unit

[0226] 110: Control circuit

[0227] 120: Pulsar

[0228] 130: High voltage power supply

[0229] 200: Probe

[0230] 210: Transducer Module

[0231] 201a: Handpiece

[0232] 201b: Cartridge

[0233] A: Aperture

[0234] BD: Body

[0235] BS: Bottom

[0236] C: Channel circuit

[0237] CGG: Coagulation Group

[0238] CS: Control signal

[0239] DS: Drive signal

[0240] E: Transducer element

[0241] DSG: Drive Signal Group

[0242] CG: Coagulation

[0243] FC: Focus point

[0244] LD: Light-emitting part

[0245] PT: Part

[0246] RCG: Coagulation of Related Technologies

[0247] SS: Side

[0248] ST: Object

[0249] TD, TG: Time Delay

[0250] TE: Transducer element

[0251] VE: Virtual Extension

[0252] VR: Virtual Transducer Elements

[0253] VT: vertical direction

[0254] W: Windows

Claims

1. A probe that generates ultrasonic waves based on a control signal and includes a plurality of transducer elements arranged in a lateral direction; A control circuit for outputting the control signal that controls the operation of at least some of the plurality of transducer elements; and A pulser comprising: a pulser providing a driving signal to at least some of the plurality of transducer elements based on the control signal; The above control circuit, Controlling a first group of transducer elements among the plurality of transducer elements and outputting a first control signal group that focuses first ultrasonic signals generated from the first group of transducer elements on a first focusing point; Controlling a second group of transducer elements among the plurality of transducer elements and outputting a second control signal group that focuses second ultrasonic signals generated from the second group of transducer elements on a second focusing point; The above first focus point and the above second focus point are located at different points along a direction perpendicular to the lateral direction, A high-intensity focused ultrasound device, wherein the sizes of the first apertures of the transducer elements of the first group and the sizes of the second apertures of the transducer elements of the second group are different from each other.

2. In paragraph 1, A high intensity focused ultrasound device, wherein the first focusing point is closer to the probe in the vertical axis direction than the second focusing point.

3. In paragraph 1, At least some of the transducer elements of the first group are driven at different times based on different control signals of the first control signal group, A high intensity focused ultrasound device, wherein at least some of the transducer elements of the second group are driven at different times based on different control signals of the second control signal group.

4. In paragraph 1, A high-intensity focused ultrasound device, wherein the size of the first aperture of the transducer elements of the first group is smaller than the size of the second aperture of the transducer elements of the second group.

5. In paragraph 1, A high-intensity focused ultrasound device, wherein the number of transducer elements driven by the first control signal group is less than the number of transducer elements driven by the second control signal group.

6. In paragraph 5, A high-intensity focused ultrasound device, wherein the transducer elements driven by the second control signal group are transducer elements in which the same number of transducer elements are added to the outermost portion along the lateral direction among the transducer elements driven by the first control signal group.

7. In paragraph 1, The first control signal group and the second control signal group are preset, The above control circuit, A high intensity focused ultrasound device, which outputs the first control signal group and the second control signal group in response to one user command.

8. In paragraph 2, A high intensity focused ultrasound device, wherein the first F-number based on the first aperture is the same as the second F-number based on the second aperture.

9. In paragraph 2, A high-intensity focused ultrasound device, wherein the first focusing point and the second focusing point are located at different points of a virtual first extension line along the vertical axis direction.

10. In paragraph 2, A high intensity focused ultrasound device, wherein at each of the first focusing point and the second focusing point, the focal area widths of the first ultrasonic signals and the second ultrasonic signals are substantially the same.

11. In paragraph 2, The above control circuit, A third control signal group is output to control a third group of transducer elements among the plurality of transducer elements and focus ultrasonic signals generated from the third group of transducer elements on a third focusing point. A fourth control signal group is output to control the fourth group of transducer elements among the plurality of transducer elements and focus ultrasonic signals generated from the fourth group of transducer elements on the fourth focusing point. The third focus point is closer to the probe in the vertical axis direction than the fourth focus point, The sizes of the third apertures of the transducer elements of the third group and the sizes of the fourth apertures of the transducer elements of the fourth group are different from each other, The size of the first aperture and the size of the third aperture are the same, and the size of the second aperture and the size of the fourth aperture are the same. The transducer elements of the first group are positioned at different locations laterally from the transducer elements of the third group and the plurality of transducer elements, A high-intensity focused ultrasound device, wherein the transducer elements of the second group are positioned at different locations laterally from the transducer elements of the fourth group and the plurality of transducer elements.

12. In paragraph 11, The third F-number based on the third aperture is identical to the fourth F-number based on the fourth aperture, A high-intensity focused ultrasound device, wherein the third focusing point and the fourth focusing point are located at different points of a virtual second extension line along the vertical axis direction.

13. In paragraph 2, The above control circuit, A high-intensity focused ultrasound device that outputs groups of control signals that form a third focusing point positioned laterally spaced from the first focusing point, and a fourth focusing point positioned laterally spaced from the second focusing point.

14. In paragraph 13, The F-numbers associated with each of the first and third focus points are identical, A high intensity focused ultrasound device, wherein the F-numbers associated with each of the second focusing point and the fourth focusing point are identical.

15. In paragraph 2, The above pulsar, Transmitting a first driving signal group to the transducer elements of the first group based on the first control signal group, and transmitting a second driving signal group to the transducer elements of the second group corresponding to the second control signal group, A high-intensity focused ultrasound device, wherein the first drive signal group and the second drive signal group are signals that drive the transducer elements of the first group and the transducer elements of the second group, respectively, such that first coagulation at the first focusing point by ultrasonic waves generated from the transducer elements of the first group is connected to second coagulation at the second focusing point by ultrasonic waves generated from the transducer elements of the second group.

16. In paragraph 15, A high-intensity focused ultrasound device, wherein the pulse duration of the first driving signal group is shorter than or equal to the pulse duration of the second driving signal group.

17. In paragraph 15, The first driving signal group includes a plurality of first driving signals for controlling each of the transducer elements of the first group, As the transducer elements of the first group move away from the imaginary first extension line connecting the first focusing point and the second focusing point along the vertical axis direction, the time delay of the plurality of first driving signals becomes shorter, The second driving signal group includes a plurality of second driving signals for controlling each of the transducer elements of the second group, A high-intensity focused ultrasound device, wherein the time delay of the plurality of second drive signals becomes shorter as the transducer elements of the second group move away from the first extension line.

18. In paragraph 1, The above probe, A body part including the above plurality of transducer elements and forming an external housing; A window for passing ultrasonic waves generated from the plurality of transducer elements to the outside of the body; and located inside the above body portion and including a cavity between the plurality of transducer elements and the window, A high intensity focused ultrasound device, wherein at least a portion of the body portion is configured transparently.

19. In paragraph 18, The above probe, A handpiece that the user can grip; and A cartridge is included that is detachably configured to be attached to the handpiece, The cartridge comprises the body, the window, the cavity, and at least one LED, A high intensity focused ultrasound device, wherein at least one LED illuminates a transparently configured portion of the body portion.

20. In paragraph 18, The above probe, A high intensity focused ultrasound device comprising at least one LED and an optical waveguide coupled to the LED to guide light emitted from the LED.

21. In paragraph 1, The transducer elements of the first group are composed of some of the transducer elements within the first aperture, A high-intensity focused ultrasound device, wherein the transducer elements of the second group are composed of all transducer elements among the transducer elements within the second aperture.

22. In paragraph 1, The above control circuit generates the first control signal group and the second control signal group based on preset setting information, The above setting information is, or includes information about the depth of at least one of the first focus point and the second focus point, Contains information about energy transferred to at least one of the first focus point and the second focus point, The above setting information is a high intensity focused ultrasound device preset by the user.

23. A step of the control circuit outputting a first control signal group for focusing ultrasonic signals generated from a first group of transducer elements among a plurality of transducer elements arranged laterally on a first focusing point; A step of the pulser providing a driving signal to the transducer elements of the first group based on the first control signal group; The step of the control circuit outputting a second control signal group that focuses ultrasonic signals generated from a second group of transducer elements among the plurality of transducer elements on a second focusing point; and The step of the pulser providing a driving signal to the transducer elements of the second group based on the second control signal group, The first focus point is closer to the probe in the vertical axis direction than the second focus point, A method of operating a high-intensity focused ultrasound device, wherein the size of the first aperture of the transducer elements of the first group is smaller than the size of the second aperture of the transducer elements of the second group.

24. A probe that receives an electrical signal based on a control signal and generates ultrasonic waves, and includes a plurality of transducer elements arranged laterally; A control circuit for generating a control signal that controls the operation of at least some of the plurality of transducer elements; and A pulser comprising: a pulser providing a driving signal to at least some of the plurality of transducer elements based on the control signal; The above control circuit generates a plurality of control signal groups, Based on each of the plurality of control signal groups, each of the different transducer element groups among the plurality of transducer elements is driven, The apertures of each of the above different groups of transducer elements are different, A high-intensity focused ultrasound device, wherein each of the plurality of control signal groups focuses ultrasonic signals generated from the plurality of transducer elements onto a plurality of different focusing points in the vertical direction.

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