RF energy transmission device and RF energy transmission method

Abstract

The present invention provides an RF energy transmission device and an RF energy transmission method that can reduce patient pain by non-invasively transmitting RF energy to the patient's skin tissue, and can control the RF energy to accurately transmit a certain level of energy to the transmission location within the skin tissue.

Description

Technical Field

[0001] The present invention relates to an apparatus for transmitting RF energy to skin tissue and a control method thereof, and to an RF energy transmission apparatus and an RF energy transmission method for transmitting an RF pulse to tissue to treat the tissue.

Background Art

[0002] Techniques for transmitting RF energy to a patient's skin tissue to treat tissue lesions have been developed in various ways. In particular, in recent years, a technique has been developed for treating tissue without damaging the surface of the skin by transmitting RF energy while cooling the skin with an electrode in contact with the surface of the skin. Such treatment techniques using RF energy are disclosed in Korean Patent No. 10-0706115.

Prior Art Documents

Patent Documents

[0003]

Patent Document 1

Summary of the Invention

Problems to be Solved by the Invention

[0004] The present invention can reduce the pain of a patient by transmitting RF energy non-invasively to the patient's skin tissue, and can control the RF energy so as to accurately transmit a certain level of energy to the transmission position within the skin tissue. Further, even if a user arbitrarily selects the RF energy to be transmitted and the heating target within the skin tissue, the control method of the present invention can control so that the inconvenience of excessive energy being transmitted to the skin and overheating, or the device suffering thermal damage does not occur.

Means for Solving the Problems

[0005] The present invention provides an RF energy transmission device and transmission method comprising: an input unit that receives information from a user regarding a target RF transmission energy to be transmitted to the skin within a certain period of time, and information regarding the selection of a mode that defines the mode of transmission of the RF energy; a control unit that generates a pulse train for generating RF energy based on the target RF transmission energy and the mode; an RF energy generation unit that generates RF energy based on the pulse train generated by the control unit; and an RF energy transmission unit that transmits the RF energy generated from the RF energy generation unit to the skin via electrodes.

[0006] As a first aspect of the present invention, an RF energy transmission device will be described. As one embodiment of the present invention, an RF energy transmission device is configured to transmit RF energy to the skin by a pulse train comprising a plurality of sub-RF pulses consisting of an on-time when RF energy is transmitted to the skin and an off-time when RF energy is not transmitted to the skin, the RF energy transmission device comprising: an input unit that receives from a user information regarding a target RF transmission energy to be transmitted to the skin during one shot of the RF energy transmission period by a single transmission activation, and information regarding the selection of a mode that defines the mode of RF energy transmission; a control unit that generates the pulse train for generating RF energy based on the target RF transmission energy and the mode input from the input unit; and the control unit The control unit includes an RF energy generating unit that generates RF energy based on a pulse train, and an RF energy transmission unit that transmits the RF energy generated from the RF energy generating unit to the skin via electrodes. When a multimode signal is input that divides the target RF transmission energy into a first section and a second section following the first section and transmits them to the skin, the control unit can generate pulse trains for the first and second sections such that the frequencies of the multiple RF subpulses included in the pulse train of the first section are higher than the frequencies of the multiple RF subpulses included in the pulse train of the second section, and the total amount of energy transmitted to the skin in the first section is greater than the total amount of energy transmitted to the skin in the second section.

[0007] Furthermore, in one embodiment of the present invention, in an RF energy transmission device, the first frequency may be 6 MHz or more and 8 MHz or less, and the second frequency may be 1 MHz or more and 3 MHz or less.

[0008] Furthermore, in one embodiment of the present invention, in an RF energy transmission device, the power (W) of multiple sub-RF pulses in the first section may be the same as that of multiple sub-RF pulses in the second section.

[0009] Furthermore, as an embodiment of the present invention, in an RF energy transmission device, the on-time of a plurality of sub-RF pulses included in the first section may be 100 ms or more and the off-time may be 50 ms or more, and the on-time of a plurality of sub-RF pulses included in the second section may be 100 ms or more and the off-time may be 50 ms or more.

[0010] Furthermore, in one embodiment of the present invention, in an RF energy transmission device, the RF energy transmission unit further includes a cooling unit for cooling the electrode; the control unit can output a first cooling pulse for each off-time of a plurality of sub-RF pulses included in the first section, until the next on-time begins, and can output a second cooling pulse for each off-time of a plurality of sub-RF pulses included in the second section, until the next on-time begins, and can control the cooling unit.

[0011] Furthermore, in one embodiment of the present invention, in an RF energy transmission device, the RF energy transmission unit further includes one or more temperature measuring units for detecting the temperature of the electrode; and the control unit can interrupt the generation of the pulse train and control the third cooling unit so that the cooling unit cools the electrode when the temperature detected by the temperature measuring unit is above a predetermined temperature.

[0012] A second aspect of the present invention will be described as an RF energy transfer method. As one embodiment of the present invention, an RF energy transmission method is an RF energy transmission method in which RF energy is transmitted to the skin by a pulse train that includes a plurality of sub-RF pulses consisting of an on-time when RF energy is transmitted to the skin and an off-time when RF energy is not transmitted to the skin, the method comprising: an input step in which an input unit receives from a user information regarding a target RF transmission energy to be transmitted to the skin during one shot of the RF energy transmission period by one transmission activation, and information regarding the selection of a mode that defines the mode of RF energy transmission; a control step in which a control unit generates the pulse train for generating RF energy based on the target RF transmission energy and the mode input from the input unit; and an RF energy generation unit generates the pulse train generated in the control step The RF energy transmission method includes: an RF energy generation step of generating RF energy based on an input; an RF energy transmission step of transmitting the RF energy generated in the RF energy generation step to the skin via electrodes using an RF energy transmission unit; wherein in the control step, the control unit divides the target RF transmission energy into a first section and a second section following the first section and transmits them to the skin in a multimode manner, and generates pulse trains for the first and second sections such that the frequencies of the multiple RF subpulses included in the pulse train of the first section are higher than the frequencies of the multiple RF subpulses included in the pulse train of the second section, and the total amount of energy transmitted to the skin in the first section is greater than the total amount of energy transmitted to the skin in the second section.

[0013] Furthermore, in one embodiment of the present invention, in an RF energy transmission method, the first frequency may be 6 MHz or more and 8 MHz or less, and the second frequency may be 1 MHz or more and 3 MHz or less.

[0014] Furthermore, in one embodiment of the present invention, in an RF energy transfer method, in the control step, the control unit can control the power (W) of the multiple sub-RF pulses in the first section to be the same as the power of the multiple sub-RF pulses in the second section to be the same as the power of the multiple sub-RF pulses in the second section. Furthermore, as an embodiment of the present invention, in an RF energy transfer method, in the control step, the control unit may set the on-time of a plurality of sub-RF pulses included in the first section to be 100 ms or more and the off-time to be 50 ms or more, and the on-time of a plurality of sub-RF pulses included in the second section to be 100 ms or more and the off-time to be 50 ms or more.

[0015] Furthermore, as an embodiment of the present invention, an RF energy transfer method further includes a cooling step of cooling the electrode with a cooling unit; wherein in the cooling step, the control unit can control the cooling unit by outputting a first cooling pulse for each off-time of a plurality of sub-RF pulses included in the first section until the next on-time begins, and can control the cooling unit by outputting a second cooling pulse for each off-time of a plurality of sub-RF pulses included in the second section until the next on-time begins.

[0016] Furthermore, as an embodiment of the present invention, the RF energy transfer method further includes a temperature measurement step in which a temperature measuring unit detects the temperature of the electrode; wherein in the cooling step, if the temperature of the electrode detected in the temperature measurement step is above a predetermined temperature, the control unit can interrupt the generation of the pulse train, output a third cooling unit to cool the electrode, and control the cooling unit. [Effects of the Invention]

[0017] According to the present invention, by using RF energy and selectively denaturing skin tissue, a regenerative effect can be obtained that induces the generation of collagen fibers, effectively kills adipocytes, and provides the effects of skin lifting and body shaping improvement. In addition, during skin treatment, excessive damage to skin tissue can be prevented, and the treatment effect can be maximized. Furthermore, the user can directly select various information regarding the RF energy to be applied to the patient's skin, and the RF energy can be optimally transmitted to the skin by a pulse train based on the user's selection. Also, even when the absorption pattern of RF energy varies depending on physiological characteristics such as the patient's constitution, skin moisture content, subcutaneous fat distribution, etc., and the structure of the skin tissue at the treatment site, by transmitting a certain amount of energy and minimizing over-treatment and under-treatment, individualized optimal treatment for each patient can be achieved.

[0018] Furthermore, since the cooling conditions can be dynamically controlled corresponding to various treatment parameters, optimal cooling can be maintained, skin tissue can be protected from overheating, and treatment stability can be improved. Also, during the transmission of the RF pulse, the temperature of the skin or the electrode is measured in real time. If the RF energy transmitted to the skin tissue accumulates excessively due to the measured temperature, a cooling pulse is immediately output to suppress the pain and other inconveniences felt by the patient and enhance the safety during treatment.

Brief Description of the Drawings

[0019] [Figure 1] It is a perspective view showing an RF energy transmission device according to an embodiment of the invention. [Figure 2] It is a block diagram showing the main configuration of the RF energy transmission device according to FIG. 1. [Figure 3] It is a perspective view showing an embodiment of the RF energy transmission unit of FIG. ?1. [Figure 4] As an embodiment of the RF energy transmission unit of FIG. 3, it is an exploded perspective view showing the main configuration of the chip module. It should be noted that there seems to be an error in the original text where it says "図1のRFエネルギー伝達部の一実施例を示す斜視図である。" and "図3のRFエネルギー伝達部の一実施例として、チップモジュールの主な構成を示す分解斜視図である。" with a reference to "図1" in one and "図3" in the other which might be inconsistent. I've translated as is based on the provided rules. [Figure 5] As an example of an RF energy transmission unit in FIG. 3, it is a cross-sectional view showing the main configuration of a chip module. [Figure 6] It is a circuit diagram showing an RF circuit formed during patient treatment by the RF energy transmission device of FIG. 1. [Figure 7] It is a cross-sectional view schematically showing the skin tissue of the face. [Figure 8] It is a diagram showing the form of a pulse train output by a control unit according to an embodiment of the present invention. [Figure 9] It is a diagram comparing pulse trains when the energy amounts in the first mode and the second mode according to an embodiment of the present invention are the same. [Figure 10] It is a diagram showing the degree of skin tissue denaturation as a result of performing the first mode and the second mode. [Figure 11] It is a diagram showing the change in the temperature of skin tissue as a result of performing the first mode and the second mode. [Figure 12] It is a diagram showing the change in the temperature of skin tissue as a result of performing the first mode and the second mode. [Figure 13] It is a diagram showing a multi-mode pulse train according to an embodiment of the present invention. [Figure 14] It is a diagram showing the degree of skin tissue denaturation as a result of performing a multi-mode according to an embodiment of the present invention. [Figure 15] It is a diagram comparing the result of performing a multi-mode according to an embodiment of the present invention with the case of using a single frequency. [Figure 16] It is a diagram showing the effect achieved when the energy ratios of the first section and the second section of a multi-mode according to an embodiment of the present invention are made different. [Figure 17] It is a diagram showing the effect achieved when the energy ratios of the first section and the second section of a multi-mode according to an embodiment of the present invention are made different. [Figure 18] It is a diagram showing the output of a cooling pulse according to an embodiment of the present invention. [Figure 19]This figure shows the pulse train generated by the control unit when the electrode temperature according to one embodiment of the present invention is above a certain temperature. [Figure 20] This figure shows an RF energy transfer method according to one embodiment of the present invention. [Modes for carrying out the invention]

[0020] The technical configuration and effects of this disclosure are described below. However, the mechanism of action (treatment) includes estimations. The mechanism of action (treatment) does not limit the technical scope of this disclosure. In the following description, the skin tissues to which RF energy reaches may be exemplified depending on the frequency. However, it should be noted that the skin tissues to which RF energy reaches may vary from person to person, as well as from various factors such as the environment. Therefore, unless specifically limited by the claims, the skin tissues to which RF energy reaches in the description or examples of the invention are illustrative for understanding the present invention and should not be interpreted as limiting the scope of the claims.

[0021] Referring to the drawings, the input section, control section, RF energy generation section, RF energy transmission section, cooling section, temperature measurement section of the RF energy transmission device according to an embodiment of the present invention, and the RF energy transmission method according to an embodiment of the present invention will be described in detail. In the following description, the positional relationships of each component will be described based on the drawings as a general rule. Furthermore, for the sake of convenience of explanation, the structure of the invention may be simplified or, if necessary, exaggerated in the drawings.Therefore, it goes without saying that the present invention is not limited thereto, and can be implemented by adding, modifying, or omitting various other devices.

[0022] An "RF energy transmission device" is a medical RF device that transmits RF energy for therapeutic purposes. It includes all devices for treating mammals, including humans. The transmission device includes various devices that transmit RF energy for the purpose of improving lesions or the condition of skin tissue. In the following examples, the focus will be on devices for treating skin lesions. For example, it means that by using RF energy to locally heat skin tissue, it can produce effects such as improving wrinkles, changes in skin tone and texture, scars and acne scarring, sagging mucosa, overall rejuvenation, hyperhidrosis, laxity, lifting, tightening, and fat reduction. However, the present invention is not limited to this, and can be applied to various devices that transmit RF energy to various affected areas, including devices for surgically treating lesions in internal organs. "Tissue" or "skin tissue" refers to the collection of cells that make up the skin of a person's body, particularly the skin of the face.

[0023] Figure 1 is a perspective view showing an RF energy transmission device according to one embodiment of the present invention. The transmission device in Figure 1 is, as an example, a medical RF device for treating a patient's skin tissue, which uses RF energy as an energy source for treatment and is an RF transmission device that transmits RF energy to the treatment location.

[0024] As shown in Figure 1, a transmission device according to one embodiment of the present invention includes a main body 10 including an input unit, a control unit, and an RF energy generation unit, and an RF energy transmission unit connected to the main body 10, which includes a handpiece 20 as one embodiment and may further include a return unit 30. The main body 10 comprises various components for operating the transmission device of this embodiment. The exterior of the main unit 10 is equipped with an input section for inputting the therapeutic operation and therapeutic mode of the transmission device, and a display section for displaying therapeutic information to the user. Inside the main unit 10 are components such as an RF energy generation unit 50 and a cooling unit.

[0025] In one embodiment of the present invention, the handpiece 20 is configured to perform treatment at the treatment location and is provided in a form that can be held in the user's hand. One end of the handpiece 20 is provided with an electrode 141 that non-invasively contacts the surface of the patient's skin to transmit RF energy. The outer surface of the handpiece 20 is provided with various operating parts for controlling the treatment operation, and the inside of the handpiece 20 is provided with a conductive path for transmitting RF energy to the electrode 141 and a cooling channel for cooling the electrode.

[0026] The return section 30 is configured as a pad including a return electrode. The return electrode is made of a conductive material and is positioned to contact a location on the patient's body opposite to the treatment location where the handpiece electrode makes contact during treatment. Therefore, when RF energy is applied to the skin, the return electrode, together with the handpiece electrode 141, forms a path through which the RF energy is transmitted to the patient's body. As shown in Figure 1, the handpiece 20 and the return unit 30 are connected to the main body by connecting parts. The connecting parts are made up of cables or the like, and are electrically connected to the main body, forming an RF transmission path, and are configured to transmit or receive various signals.

[0027] In this embodiment, the handpiece electrode 141 is configured as a monopolar type having a single polarity and is provided with a separate return section, but the present invention is not limited to this. As another example, if the handpiece is configured as a bipolar type having electrodes with different polarities, it can be implemented without including the aforementioned return electrode pad.

[0028] Figure 2 is a block diagram showing the main configuration of the transmission device according to Figure 1. The RF energy generation unit 50 generates RF energy as energy used for treatment. The RF energy generation unit 50 receives an RF pulse train having various parameters depending on the patient's constitution, the purpose of treatment, the treatment site, etc., from the control unit and generates RF energy. The parameters may be at least one of output, pulse duration (on time), pulse interval (off time), and frequency. The RF energy generation unit 50 of this embodiment can also generate RF energy having various frequencies. For example, the RF energy generation unit 50 can generate RF energy having a first frequency and RF energy having a second frequency, and in some cases, it can even generate RF energy having both the first and second frequencies.

[0029] Furthermore, the RF energy generation unit 50 can generate RF energy having one of the selected frequencies depending on the selected treatment mode or the progress of the treatment process, and can generate RF energy for a longer or shorter period of time. It can also generate RF pulses of different frequencies across the first and second sections, and generate a different number of sub-RF pulses for each frequency. The electrode 141 is configured to transmit RF energy generated from the RF energy generation unit to the patient's skin tissue and is included in the RF energy transmission unit 20. The electrode 141 is provided at one end of a handpiece, which is one embodiment of the RF energy transmission unit 20, and is positioned to make non-invasive contact with the patient's skin tissue during use.

[0030] The electrode 141 is configured to be detachable from one end of the handpiece 20, and the user can select one of several electrodes, each having a different surface area. The surface area of ​​the electrode 141 results in a difference in the area over which RF energy is transmitted. The electrode 141, together with the return section 30 positioned opposite the handpiece 20 and in contact with the patient's skin, forms an RF circuit that passes through the patient's skin tissue and transmits RF energy to the patient's skin tissue. The monitoring unit 35 is configured to monitor the RF energy transmitted to the patient's skin tissue. The monitoring unit 35 measures at least one RF parameter along the path of the RF circuit formed by the RF energy generation unit 50, the electrode unit 141, and the return unit 30, and monitors the RF energy transmitted to the skin tissue by calculating it based on this parameter.

[0031] The cooling unit 60 is configured to cool the treatment position where treatment is performed by the handpiece, or the electrode that non-invasively contacts the treatment position. The cooling unit 60 can use various cooling methods, and as an example, the cooling unit 60 in this embodiment is configured to cool using the heat of vaporization of a liquid-phase coolant. In this embodiment, during treatment, the coolant can be sprayed onto the handpiece side of the electrode 141 that contacts the treatment position, thereby cooling the electrode and indirectly cooling the treatment position. In this case, the surface of the skin in contact with the electrode 141 is cooled, preventing thermal damage to the skin surface during treatment.

[0032] The cooling unit 60 includes a refrigerant housing for containing refrigerant, a cooling channel that forms a path for the refrigerant contained in the refrigerant housing to be transmitted, and a cooling module that sprays the refrigerant transmitted through the cooling channel onto the rear surface of the handpiece electrode. The refrigerant housing is located in the main body or at a separate location. The cooling channel connects the refrigerant housing to the cooling module, and at least a portion of the cooling channel is located inside the handpiece. The cooling channel includes at least one valve and a sensor, which the control unit uses to monitor the cooling process of the cooling unit 60 and control the cooling performance. Here, the cooling performance is the ability to lower the temperature of an object in the same amount of time, and may be the amount of refrigerant injected per unit time through the cooling module.

[0033] The sensing unit 80 is configured to sense various information necessary for the operation of the transmission device during or before and after treatment. For example, the sensing unit 80 may be at least one of an impedance sensor for measuring the impedance of skin tissue, a temperature sensor 142 (temperature measuring unit) for measuring the temperature of the electrode or skin, a contact sensor for sensing whether or not the handpiece electrode is in contact with the surface of the skin, a movement sensor for sensing the movement speed of the handpiece, and a pressure sensor for sensing the pressure of the cooling channel. As an example, in this embodiment, the temperature sensor 142 and the contact sensor (not shown) are positioned adjacent to the handpiece electrode, and a pressure sensor for monitoring the pressure at which the refrigerant is supplied is positioned in the cooling channel.

[0034] The input unit 70 is provided in the main unit and is configured to allow input of various operations of the transmission device, including the treatment mode. The user can select and set the treatment mode to be performed via the input unit 70. Specifically, the user can set the target RF energy to be transmitted to the skin tissue using RF energy pulses, and the treatment mode via the input unit 70. The target RF energy to be transmitted to the skin tissue may be a specific numerical value or a predetermined level. Alternatively, the user can set the treatment lesion, the target skin tissue to be treated, the target depth, etc.

[0035] The storage unit 90 is configured to store various types of information required for treatment and includes memory elements. The storage unit 90 is provided in the main unit 10 and can also be provided in the handpiece 20 and the chip module 100. The storage unit 90 can store parameter information for each treatment mode, patient-related information, control information based on sensed conditions, etc. It can also update and record information sensed during treatment and information entered by the user. In the case of memory provided in the handpiece 20 or the chip module 100, it can be configured to store identification information for the handpiece or chip module.

[0036] The control unit 40 is configured to control the operation of various components of the transmission device, such as the RF energy generation unit 50 and the cooling unit 60. For example, the control unit 40 controls various components in a variety of ways using the content input by the user via the input unit 70 or control information stored in the storage unit 90. The control unit receives information sensed from the sensing unit 80 and information monitored from the monitoring unit 35, and uses the received information to control various components. As an example, the control unit 40 receives temperature values ​​sensed by the temperature sensor and controls the RF pulse parameters and the cooling performance for the electrodes based on them. Alternatively, the control unit 40 controls the RF pulse parameters based on information monitored by the monitoring unit. Here, the control unit 40 is configured to include a calculation unit, and can calculate control values ​​using the received information with a pre-set algorithm, and control various components based on those values.

[0037] Figure 3 is a perspective view showing the handpiece of Figure 1. As shown in Figure 3, the handpiece 20 comprises a main body 21 and a tip module 100. The main body 21 is connected at one end to a coupling section and contains various components for performing therapeutic operations, such as an RF transmission circuit and a cooling channel. The outer surface of the main body 21 is provided with an operating section and a display section such as a display. The tip module 100 includes an electrode 141 for contacting the skin and transmitting RF energy, and is detachably coupled to one end of the main body 21. The tip module 100 includes a circuit and electrode for transmitting RF energy to the electrode, and a cooling structure for cooling the treatment area. The structure of the tip module will be described in more detail below with reference to Figures 4 and 5.

[0038] Figure 4 is an exploded perspective view showing the main components of the chip module in Figure 3, and Figure 5 is a cross-sectional view showing the main components of the chip module in Figure 3. Referring to Figures 4 and 5, the chip module consists of a chip housing 110, an electrode module 140, a cooling module 150, an internal case 120, and a rear cover 130. The tip housing 110 and the internal case 120 are coupled together to support the electrode module 140. The cooling module 150 is positioned inside the internal case 120. The rear cover 130 is coupled to the rear surface of the tip housing 110 with the electrode module 140, internal case 120, and cooling module 150 positioned inside the tip housing 10. The tip housing 110 or the rear cover 130 has a coupling structure for fastening to the end of the main body 21 of the handpiece.

[0039] As shown in Figure 4, the electrode module 140 is composed of a flexible substrate that is bendable, and an electrical element and a circuit for electrically forming thereon are formed thereon. The electrode 141 is positioned in front of the electrode module (relative to the state in which the electrode module is bent), exposed at an opening in the chip housing 110, and in contact with the surface of the skin. The electrode 141 is composed of a conductive layer formed on the flexible substrate, and the conductive layer is configured to be covered by a dielectric layer. Therefore, during treatment, the conductive layer of the electrode comes into contact with the skin via the dielectric layer, and when RF energy is applied to the electrode, the electrode transmits the RF energy to the skin tissue while capacitively coupled with the skin tissue by the dielectric layer.

[0040] On the other hand, as mentioned above, the temperature sensor 142 and contact sensor of the sensing unit are located adjacent to the electrode 141 in the electrode module 140, and measure the temperature of at least one of the electrode or the surface of the skin to sense whether the electrode and the skin are in contact. The temperature sensor 142 of the sensing unit is an example of a temperature measuring unit. The electrode module 140 also further includes a memory, which can store information about the chip module such as the type of electrode, the size of the electrode, the pattern of the electrode, and the size of the cooling space. The electrode module 140 is connected to the aforementioned electrode, each sensor, and the memory, and includes conductive leads that extend to the rear. Terminals formed at the ends of the conductive leads are exposed to the rear when the rear cover 130 is attached, and are electrically connected to the RF circuit on the main body 21 side of the handpiece when the chip module 100 is attached.

[0041] As described above, the cooling module 150 is configured to inject the refrigerant transmitted from the refrigerant storage unit 210 along the cooling channel 201 onto the rear surface of the electrode 141. The rear side of the cooling module 150 is provided with a conduit through which the cooling channel is formed, and the front side of the cooling module 150 is provided with a plurality of injection ports 151. The rear end of the conduit is exposed on the rear side of the rear cover 130 when the tip module 100 is assembled. Therefore, when the tip module 100 is coupled to the main body 21 of the handpiece, the cooling channel of the conduit is coupled to the cooling channel on the main body 21 side, forming a path through which the refrigerant supplied from the refrigerant storage unit 210 is transmitted.

[0042] As described above, the chip module 100 having such a structure is detachably coupled to the end of the main body of the handpiece. When coupling the chip module 100, the control unit 40 is provided with information about the chip module from the memory of the chip module 100, and taking this into consideration, controls the RF generating unit 50 and the cooling unit 60 to transmit RF energy to the electrodes of the chip module 100 and to cool the electrodes. The chip module 100 is a consumable and can be replaced with a new chip module 100 when treating a new patient or when the number of allowed uses is exceeded. At that time, the number of allowed uses may be counted by the user based on the number of shots in the RF energy transmission period of one transmission activation. On the other hand, the chip module 100 can be selected in various sizes depending on the area of ​​the electrodes that come into contact with the skin, for example, the electrode area may be 0.1 cm². 2 ~80cm 2 It is possible.

[0043] This ensures hygiene even when the chip module 100 comes into contact with the skin, and suppresses problems such as electrode damage and inconsistent RF energy transmission quality that can occur when using the chip module 100 without replacement. The RF energy transmission device described above is electrically connected to the patient's body in part to form an RF circuit, thereby transmitting RF energy to the patient's skin tissue and performing treatment.

[0044] Figure 6 is a schematic circuit diagram showing the RF circuit formed during patient treatment using the transmission device shown in Figure 1. The aforementioned RF energy transmission device is electrically connected to the patient's body in at least part of its structure to form an RF circuit, thereby transmitting RF energy to the patient's skin tissue and performing treatment. Specifically, the electrode portion 141 located at the end of the handpiece comes into contact with one side of the patient's skin surface during treatment due to the user's treatment movements. The return electrode of the return portion 30 comes into contact with the patient's skin surface at a position opposite to the electrode portion 141. The electrode portion 141 of the handpiece 20 is connected to the RF energy generating portion 50 located in the main body via a connecting portion. The return electrode of the return portion 30 is connected to a separate grounding portion.

[0045] As a result, when treating a patient using the RF energy transmission device, an RF circuit as shown in Figure 6 is formed. Here, the patient's body comes into contact with the electrode section 141 and the return section 30, and is capacitively coupled to them. That is, the electrode section 141 and the return section 30 act as charged plates of capacitive elements, and the patient's skin tissue interposed between the electrode section 141 and the return section 30 acts as a dielectric of the capacitive elements. Therefore, the electrode section 141 connected to the RF generation section 50 acts as an active electrode, applying RF pulses to the inside of the patient's skin tissue, and the return section 30 connected to the ground section acts as a return electrode, forming a path for the RF pulses applied to the inside of the skin tissue to return. Through the RF circuit thus formed, RF energy pulses are applied to the patient's skin tissue, transmitting RF energy, and the transmitted RF energy is used to treat the skin tissue.

[0046] On the other hand, Figure 7 is an illustrative cross-sectional view showing facial skin tissue from the surface. It should be noted that, as anyone with ordinary skill in the art to which this invention belongs will know that the cross-sectional view of skin tissue will depend on the part of the human body. Skin tissue can be divided from the surface into the epidermis, dermis (papillary dermis, reticular dermis), subcutaneous tissue (hypodermis), and fat layer. In this case, each layer of skin tissue can be further divided, for example, into the epidermal layer, dermal layer (papillary dermis and reticular dermis), lower dermal layer (hypodermis), and subcutaneous fat layer. However, since the structure of skin tissue depends on individual physiological characteristics, age, sex, etc., such divisions of layers should not be interpreted as limiting the technical scope of the present invention. Therefore, it should be obvious to a person with ordinary skill in the art to which the present invention belongs that the above divisions are not limited to the concept of skin layers applicable similarly based on various anatomical criteria, and that the technical ideas of the present invention can be similarly applied to the structure of various skin tissues.

[0047] Each layer constituting skin tissue can exhibit different conductivity and dielectric constants with respect to RF frequencies. When RF energy is transmitted through the skin, the heating depth can vary depending on the frequency of the RF energy. When the RF electrode is configured as monopolar, the RF energy is transmitted from the handpiece electrode to a return electrode (not shown) separately attached to the human body. Depending on the frequency, the degree to which energy is transmitted within the skin tissue differs. By using these electrical properties of skin tissue and adjusting the frequency of the RF energy, it is possible to more effectively heat the target skin tissue within the skin tissue.

[0048] Generally, within a certain range, the lower the frequency of RF energy, the deeper the area within the skin tissue to which the energy is effectively transmitted tends to be. The control unit can adjust the frequency of the RF energy to a first frequency and a second frequency to adjust the area within the skin tissue to be heated. For example, the first frequency can be selected as a frequency that can heat the skin tissue from the epidermis to the dermis and down to the lower dermis. For example, the second frequency can be selected as a frequency that can heat the skin tissue from the epidermis to the dermis. As mentioned above, due to the electrical characteristics of different parts of the skin tissue, applying RF energy with a specific frequency makes it possible to effectively heat not only the epidermis to the upper and lower dermis, but also the fat layer.

[0049] Meanwhile, the control unit controls the RF energy generator to generate RF energy based on the pulse train generated by the control unit during one shot. In this case, one shot refers to the RF energy transmission period resulting from a single transmission activation by the user.

[0050] The following describes, with examples, a method by which the control unit generates a pulse train for generating RF energy based on information regarding the target RF energy to be transmitted to the skin during one shot, and information regarding the selection of a mode that defines the mode of RF energy transmission. First, the user inputs information regarding the target RF energy to be transmitted to the skin in one shot, and information regarding the selection of a mode that defines the mode of RF energy transmission, via the input section of an RF energy transmission device according to one embodiment of the present invention. The input method for this information may be a touch display, a button, or a dial.

[0051] The input section may include a tab for selecting an energy level, which is information about the target RF energy to be transmitted to the skin during one shot. The user may input the target RF energy to be transmitted to the skin during one shot as a specific numerical value, or they may directly input a predetermined energy level. Furthermore, the input section has a tab that allows the user to select a mode that defines the method of RF energy transmission during a single shot. The user can select one of several modes depending on the target location in the patient's skin tissue to be treated. In one embodiment, the user can select the first, second, or third mode depending on the user's purpose, such as how deep the target location to which RF energy is to be primarily transmitted is located from the skin surface. In this case, the first and second modes may be modes that use a single frequency for treatment, while the third mode may be a mode that uses multiple frequencies for treatment.

[0052] In another embodiment, even if a user selects a desired mode, unintended areas may be treated depending on the individual's skin, such as the thickness and moisture content of the skin tissues and their condition during treatment. To prevent this, the user can be asked to reconfirm their selection of the mode, or the user can be recommended a mode that can deliver RF energy with optimal efficiency based on the heating location and the energy to be delivered to that location. Alternatively, the control unit can automatically modify the mode to deliver RF energy to the heating location with optimal efficiency.

[0053] On the other hand, the input unit can be configured to automatically recognize and input the size of the module chip and the area size of the electrodes selected by the user, or it can be configured to allow the user to input them directly. The control unit receives electrode area information from the input unit and can optimize parameters such as the number of sub-RF pulses in the pulse train and cooling conditions based on the received electrode area information. In one embodiment, the control unit can control the number of sub-RF pulses included in the pulse train to increase as the size of the module chip selected by the user increases.

[0054] The control unit generates a pulse train that generates RF energy based on the information received from the input unit. The pulse train generated by the control unit is input to the RF energy generation unit, which is configured to generate RF energy using the pulse train. In other words, referring to the pulse train as an embodiment shown in Figure 8, the pulse train generated by the control unit is transmitted to the skin in the on-time t on , and off-time when RF energy is not transmitted to the skin. off It is composed of the following. In the pulse train, on-time and off-time are arranged alternately, and the sub-RF pulses are composed of on-time and off-time in that order, or off-time and on-time in that order. sub However, a pulse train can contain multiple units.

[0055] The following explains in detail the criteria used to generate the pulse train when the user selects either Mode 1 or Mode 2. The first mode is assumed to be a mode that uses a single frequency to transmit RF energy from the epidermis to the upper dermis, and the second mode is assumed to be a mode that uses a single frequency to transmit RF energy from the epidermis to the upper and lower dermis. However, the invention is not limited to this, and it goes without saying that the technical concept and scope of rights of the present invention also include cases where the RF energy transmitted through the second mode actually reaches the subcutaneous tissue, which is an even deeper region of the skin.

[0056] The control unit obtains, through the input unit, information regarding the target RF energy to be transmitted to the skin during a single shot selected by the user, and information regarding the selection of a mode that defines the form of RF energy transmission. The information regarding the target RF transmission energy, in one embodiment, refers to the total amount of RF energy that is ultimately intended to be transmitted to the skin during a single shot. Furthermore, the information regarding the target RF transmission energy is selectively limited to a predetermined range, taking into consideration user safety and therapeutic efficiency. For example, the total amount of RF energy transmitted, or the maximum output energy per sub-RF pulse, may each have upper and lower limits pre-stored in the system, allowing the user to select a desired value within that range.

[0057] Furthermore, information regarding the selection of a mode that defines the mode of RF energy delivery includes information that the user has selected either a first mode or a second mode, which is a mode that can deliver RF energy to deeper parts of the skin than when the first mode is selected. The frequencies of the sub-RF pulses included in the first-mode pulse train and the frequencies of the sub-RF pulses included in the second-mode pulse train are set to be the same.

[0058] The RF energy frequencies used in the first and second modes are set differently depending on the depth of the treatment area, the patient's skin characteristics (e.g., skin moisture content, fat layer distribution), and the purpose of treatment. However, based on statistical analysis and clinical data, it is preferably effective to select a frequency within the range of approximately 6 MHz to 8 MHz, more preferably within the range of approximately 6.5 MHz to 6.9 MHz, and even more preferably within the range of approximately 6.7 MHz to 6.8 MHz. Within this range, as shown in Figure 10, 6.78 MHz in particular shows excellent effect in terms of the degree of skin tissue degeneration and is advantageous in terms of therapeutic effect and safety, and is therefore adopted as a specific example.

[0059] The frequency range of 6 MHz to 8 MHz described above is generally a frequency band in which RF energy can effectively penetrate from the surface of the skin, beyond the epidermis, to the dermis. However, the actual penetration depth of RF energy depends on the individual skin characteristics of the patient, such as skin moisture content, subcutaneous fat thickness, body temperature, and physiological conditions at the time of treatment. In one embodiment of the present invention, the system is configured to select an appropriate frequency or to automatically adjust it, taking into account the characteristics of the user. On the other hand, if we compare the case where the amount of RF energy transmitted to the skin in the first mode and the amount of RF energy transmitted to the skin in the second mode are selected to be the same, the first mode and the second mode are set to have different numbers of sub-RF pulses, on-times and off-times, with the number of sub-RF pulses in the first mode being greater than the number of sub-RF pulses in the second mode, and the on-times and off-times in the first mode being shorter than those in the second mode.

[0060] Figure 9(A) shows an example of a first-mode pulse train when using a single frequency, and Figure 9(B) shows an example of a second-mode pulse train when using a single frequency. In the embodiment shown in Figure 9, in the first mode, excluding the initial tuning pulse, the pulse train consists of 12 identical sub-RF pulses with a power W of approximately 200 watts (W), an on-time of approximately 80 ms, and an off-time of approximately 50 ms. In the second mode, excluding the initial tuning pulse, the pulse train consists of 6 identical sub-RF pulses with a power W of approximately 150 watts (W), an on-time of approximately 150 ms, and an off-time of approximately 100 ms.

[0061] Referring to Figure 9, when the target RF transfer energy selected by the user is the same for both the first and second modes, if the first mode is selected, the number of sub-RF pulses included in the pulse train generated by the control unit (hereinafter referred to as the first mode sub-RF pulses) is greater than the number of sub-RF pulses included in the pulse train generated by the control unit when the second mode is selected (hereinafter referred to as the second mode sub-RF pulses). The on-time and off-time of the first mode sub-RF pulses can be configured to be shorter than the on-time and off-time of the second mode sub-RF pulses. When the second mode is selected, the control unit is configured to control the number of sub-RF pulses included in the pulse train to be within the range of 3 to 10, preferably 4 to 7. When the first mode is selected, the control unit can control the number of sub-RF pulses in the first mode to be within the range of 2 to 10 times the number of sub-RF pulses in the second mode. For example, if the second mode includes 5 sub-RF pulses, the first mode is controlled to include 10 to 50 sub-RF pulses.

[0062] When the target RF transmission energy is the same, the first mode generates a pulse train that outputs shorter pulses and higher power than the second mode. When RF pulse energy is transmitted to the skin based on such a pulse train, thermal diffusion is minimized and the RF energy accumulates, so heat can be effectively transmitted from the epidermis to the upper dermis. In the second mode, a small number of sub-RF pulses can be used to control the delivery of low-power RF pulse energy with a sufficiently long on-time, concentratedly to the lower dermis of the skin. This is achieved by balancing sustained heat accumulation with a cooling period (thermal relaxation), and the heat is transferred to the dermis and the superficial adipose layer. Under certain conditions, it is possible to target and heat the fibrous septa without affecting adipocytes.

[0063] In another embodiment, the number of sub-RF pulses included in the pulse trains of the first and second modes can also be controlled by the area of ​​the electrodes in the RF energy transmission section. For example, the larger the area of ​​the electrodes selected by the user, the more the number of sub-RF pulses in the first and second modes can be controlled to increase. This is because, although a larger electrode area means a wider area to which RF energy is applied to the skin, the density of RF energy for the same amount of applied RF energy is lower in that area. By controlling the number of sub-RF pulses to increase, the RF energy can be concentrated and transmitted to the epidermal side.

[0064] On the other hand, the sub-RF pulses of the first mode and the sub-RF pulses of the second mode are configured to have different output powers (power, W). That is, the control unit can set the power of the sub-RF pulse used in the first mode and the power of the sub-RF pulse used in the second mode to be different. However, the power of the sub-RF pulses in the first mode is determined by the number of sub-RF pulses set in the first mode, and the power of the sub-RF pulses in the second mode is also determined by the number of sub-RF pulses set in the second mode. In this way, the number and power of the sub-RF pulses in each mode are controlled in conjunction with each other in order to maintain a constant total target RF transmission energy.

[0065] Furthermore, the output power (W) of each sub-RF pulse included in the first mode can be controlled to remain the same, and the output power can also be controlled to remain the same during the multiple sub-RF pulses included in the second mode. With this configuration, output uniformity between sub-RF pulses within each mode is ensured, allowing for even energy distribution to the skin tissue under the same treatment conditions. As a result, excessive or insufficient energy distribution to specific areas can be prevented, reducing adverse effects such as pain, overheating, and burns during or after treatment, and improving the accuracy and safety of the treatment.

[0066] Furthermore, uniform control of output power enhances system reliability, allowing users to obtain more predictable and consistent treatment results. Additionally, if the target RF energy to be applied to the skin is the same in both the first and second modes, the control unit can set the power of each of the sub-RF pulses in the second mode to a lower value than the power of each of the sub-RF pulses in the first mode. This is because, in order to effectively heat deeper layers of skin tissue, the sub-RF pulses must have a longer on-time, which can cause discomfort to the patient. Reducing the power of the sub-RF pulses reduces patient discomfort.

[0067] On the other hand, in each sub-RF pulse of the first mode RF pulse train, the on-time is set to be between 30ms and 100ms, and the off-time is set to be between 10ms and 50ms. In each sub-RF pulse of the second mode RF pulse train, the on-time is set to be between 100ms and 300ms, and the off-time is set to be between 50ms and 200ms. The on-time and off-time settings within this range are intended to embody an energy delivery pattern suited to the therapeutic purpose of each mode, and the inventors have confirmed that RF energy is effectively delivered to the epidermal and dermal layers of the skin. It is presumed that in the first mode, uniform thermal stimulation is provided to the epidermal and upper dermal layers of the skin through short, rapid, repetitive stimulation, while in the second mode, deeper energy delivery reaching the epidermal and upper and lower dermal layers of the skin is achieved through relatively longer stimulation.

[0068] In other words, in order to secure the target cumulative amount of RF energy even in a short time, the sub-RF pulse of the first mode is configured to be applied for a short time at high power, while the second mode is configured to be applied for a longer time at relatively low power. As a result, when the first and second modes are set to the same energy, the depth to which the RF energy is transmitted and the skin tissue to which it is transmitted will differ. This allows the power (W) of each sub-RF pulse in the first mode to be maintained at the same level, and the power output of each sub-RF pulse in the second mode to be controlled to be the same. This enables uniform energy transfer of the sub-RF pulses within each mode, resulting in a stable therapeutic effect.

[0069] As shown in Figure 10, when the target RF transmission energy applied to the skin is the same for both the first and second modes, and the skin tissue is heated using a frequency of 6.78 MHz, the degree of skin tissue denaturation can be compared. When the first mode is used (left side), it can be confirmed that denaturation progresses more in the relatively shallow parts, while when the second mode is used (right side), it can be confirmed that denaturation progresses more in the relatively deeper parts.

[0070] As shown in Figures 11 and 12, when the target RF transmission energy applied to the skin is the same at 75 J for both the first and second modes, the degree of heating can be observed at positions 3.0 mm and 5.0 mm from the skin surface to the inside of the skin. Specifically, when RF energy was applied by a pulse train having on / off times for sub-RF pulses corresponding to the first mode, the temperature change was 7.1°C (34.1°C-27°C) at a position 3.0 mm inside the skin, and 3.9°C (29.9°C-26°C) at a position 5.0 mm inside the skin.

[0071] On the other hand, when RF energy was applied by a pulse train having on / off times for sub-RF pulses corresponding to the second mode, the temperature change was 12.2°C (39.2°C-27°C) at a position 3.0 mm inside the skin, and 8°C (29.9°C-26°C) at a position 5.0 mm inside the skin.

[0072] These experimental results confirmed that the second mode, with its relatively longer on-time and off-time of the sub-RF pulse, effectively delivers energy to the skin tissue 3.0 mm to 5.0 mm deeper (generally corresponding to the lower dermis) and heats it more effectively than the first mode. Therefore, according to the present invention, the user can select an appropriate energy level and transmission mode depending on the patient's skin condition or the purpose of treatment, and the control unit will then stably and efficiently transmit RF energy by adjusting the configuration of the pulse train.

[0073] The third mode will be explained in detail below with examples. The control unit receives information from the user, through the input unit, regarding the target RF energy to be transmitted to the skin during a selected shot, and the selection of a mode that defines the form of RF energy transmission. At this time, the user selects a third mode (multimode) in which the target RF transmission energy is divided into a first section and a second section following the first section and transmitted to the skin.

[0074] The first and second sections each include one or more pulse trains, and the control unit can generate pulse trains corresponding to each section under different conditions and control them to deliver RF energy to the skin. Multiple sub-RF pulses included in the pulse train of the first section can be configured to have a higher frequency than multiple sub-RF pulses included in the pulse train of the second section. That is, in the first section, RF energy with a higher frequency than the sub-RF pulses in the second section can be applied, and in the second section, sub-RF pulses with a lower frequency than the sub-RF pulses in the first section can be generated.

[0075] The frequency of the sub-RF pulses included in the pulse train in the first section (hereinafter referred to as the "first frequency") is preferably set within the range of 6 MHz to 8 MHz, and the frequency of the sub-RF pulses in the second section (hereinafter referred to as the "second frequency") is preferably set within the range of 1 MHz to 3 MHz.

[0076] As shown in Figure 13, in a pulse train, the power of the sub-RF pulses in the first section, which consists of sub-RF pulses with a frequency of 6.78 MHz, is identical at approximately 200 watts (W), and the power of the sub-RF pulses in the second section, which consists of sub-RF pulses with a frequency of 2.00 MHz, can be configured to be identical at approximately 150 watts (W).

[0077] In the first section, RF energy with a frequency of 6.78 MHz is transmitted to the skin tissue, targeting the heating area from the epidermis to the dermis. Then, in the second section, RF energy with a frequency of 2.00 MHz, lower than the sub-RF pulse in the first section, is transmitted to the skin tissue, targeting the heating area from the epidermis to the fatty layer. Therefore, the RF energy density transmitted to the skin tissue in the second section is lower than the energy density transmitted in the first section. As a result, the temperature of the epidermis and upper dermis of the skin does not rise above the target temperature, but is maintained at the target temperature.

[0078] This can be confirmed by experiments, as shown in Figures 14 and 15. Figure 14(A) shows the state of collagen without RF energy transmission (baseline), Figure 14(B) shows the state of collagen with RF energy transmitted using a single frequency RF pulse of 6.78 MHz, and Figure 14(C) shows the state of collagen with RF energy of 6.78 MHz and RF energy of 2.00 MHz transmitted sequentially. Comparing the degree of collagen denaturation, it was confirmed that when RF energy was transmitted at 6.78 MHz + 2.00 MHz, the collagen diameter was greater, the length was shorter, the staining intensity was stronger, and the collagen was denser compared to the state without RF energy transmission (baseline) and when RF energy was transmitted using a single frequency RF pulse of 6.78 MHz.

[0079] Furthermore, these results can be confirmed from the graph in Figure 15. When RF energy was transmitted at 6.78 MHz + 2.00 MHz, the diameter of the collagen appeared to be significantly thicker compared to the state where no RF energy was transmitted (baseline) and when RF energy was transmitted using a single frequency RF pulse of 6.78 MHz.

[0080] Furthermore, the control unit can control the pulse train in each section such that the total amount of RF energy transmitted to the skin in the first section is greater than the total amount of RF energy transmitted to the skin in the second section. In this case, when the sum of the total amount of RF energy transmitted to the skin in the first section and the total amount of RF energy transmitted to the skin in the second section is taken as 100%, the ratio of the total amount of RF energy transmitted to the skin in the first section is greater than 50%, preferably greater than 55% and less than 70%, and particularly preferably 60%.

[0081] Comparative data of RF energy being transmitted to collagen are shown in Figures 16 and 17. The ratio of the total energy in the first section, where a sub-RF pulse with a frequency of 6.78 MHz is generated, to the total energy in the second section, where a sub-RF pulse with a frequency of 2.00 MHz is generated, was varied, while the sum of the total energy in the first section and the total energy in the second section was kept constant at 150 J. As can be seen from Figures 16 and 17, the collagen appeared to have a larger diameter under conditions 4, 5, and 6, where the total energy in the first section was greater than the total energy in the second section. In particular, the collagen appeared to have the largest diameter under condition 4, where the total energy in the first section was 90 J and the total energy in the second section was 60 J.

[0082] With this configuration, the first section uses high-frequency waves to provide more concentrated and integrated energy stimulation to skin tissues closer to the surface, such as the epidermis and dermis, which is expected to enhance skin elasticity and induce collagen production. On the other hand, the second section transmits less energy at a lower frequency than the first section, allowing for a more balanced overall treatment of skin tissues closer to the deeper layers, such as the lower dermis and adipose layer, compared to the first section.

[0083] Since the energy transmitted changes depending on the location and depth of the skin layer being heated in each section, the frequency can be set differently. Specifically, in the first section, the epidermis and dermis are mainly targeted for heating, and by using a first frequency that is relatively high-frequency, precise thermal stimulation can be provided localized to the surface of the skin. On the other hand, in the second section, since the target of heating is not only the epidermal layer but also deeper layers including the upper and lower dermis, a second frequency is used, which is in the low-frequency range with a greater penetration depth, to enable effective heat transfer to the lower dermis and fat layer.

[0084] Furthermore, the control unit can control the output power (W) between multiple sub-RF pulses included in the first pulse train to be the same as each other, and can also control the output power between multiple sub-RF pulses included in the second pulse train to be the same as each other. This configuration minimizes variations in energy transfer between sub-RF pulses within each section, resulting in a uniform distribution of RF energy delivered to the skin across sections, thus achieving a consistent heating effect throughout the entire treatment area.

[0085] Furthermore, the on-time of the multiple sub-RF pulses included in the first section is 100 ms or more, and the off-time is 50 ms or more. Similarly, the on-time of the multiple sub-RF pulses included in the second section is 100 ms or more, and the off-time is 50 ms or more. The on-time of the sub-RF pulses in the first and second sections is set to 100 ms or more to ensure that RF energy is transmitted deeply to the dermis and fat layer beneath the skin.

[0086] The following describes the configuration of the cooling unit. The cooling unit is configured to cool the treatment area where the RF energy transfer unit performs treatment, or to cool the electrodes included in the RF energy transfer unit. For example, in this embodiment, the cooling unit is configured to use the heat of vaporization of a liquid-phase coolant to cool the treatment area or electrodes. Of course, it may also be configured to use the temperature of the gaseous coolant itself to cool the treatment area or electrodes.

[0087] Specifically, the cooling unit includes a refrigerant reservoir containing a refrigerant, a cooling channel that forms a path for the refrigerant contained in the refrigerant reservoir to be transmitted, and a cooling module that sprays the refrigerant transmitted through the cooling channel toward the electrodes of the RF energy transmission unit or to the treatment position on the rear surface of the electrodes. The refrigerant reservoir is located in the main body or at a separate location. The cooling channel is connected from the refrigerant reservoir to the cooling module, and at least a portion of the cooling channel may be located inside a handpiece, which is an embodiment of the RF energy transmission unit. The cooling channel is configured to include at least one valve and a sensor, which the control unit uses to monitor the cooling process of the cooling unit and control the cooling performance. Here, cooling performance is the ability to lower the temperature of an object over the same amount of time, and is the amount of refrigerant sprayed per unit time by the cooling module.

[0088] Components such as an ICD (intelligent cooling device) filter, pressure sensor, bubble sensor, joint coupling, and ICD valve may be placed on the cooling channel. Specifically, the refrigerant containment section consists of a pressure vessel that contains liquid-phase refrigerant. The refrigerant containment section has a discharge section at one end, and the discharge section is positioned downwards to facilitate the outflow of the refrigerant. The discharge section is connected to one end of the cooling channel, and the liquid-phase refrigerant is supplied to the cooling channel through the discharge section at a predetermined pressure.

[0089] Based on the direction of refrigerant flow, a portion of the cooling channel forward is located inside the main body, while a portion of the cooling channel rearward is connected from the outside of the main body to the cooling module of the handpiece. The front and rear ends of the cooling channel are selectively detachably connected by a joint coupling. The joint coupling is, for example, located on the outside of the main body and configured to allow the cooling channel to be separated from the outside of the main body when necessary.

[0090] The cooling channel located within the main unit is equipped with an ICD filter, a pressure sensor, and a bubble sensor. The ICD filter is installed at the discharge end of the refrigerant storage unit and is configured to filter out foreign matter from the liquid phase refrigerant discharged from the refrigerant storage unit.

[0091] A pressure sensor is installed on the cooling channel and measures the pressure in the cooling channel. The pressure in the cooling channel is determined by the pressure at which the refrigerant is discharged from the refrigerant reservoir, and the pressure in the refrigerant reservoir can be determined based on the value measured by the pressure sensor. Here, the pressure in the cooling channel measured by the pressure sensor is the same as the pressure in the refrigerant reservoir, or the pressure in the refrigerant reservoir can be determined by giving weight to the measured pressure in the cooling channel. Since the pressure in the cooling channel affects the cooling performance at the treatment site, the pressure sensor monitors the pressure value during the cooling process and transmits the measured value to the control unit.

[0092] The bubble sensor detects whether or not bubbles are present in the liquid phase refrigerant passing through the refrigerant flow path. Bubbles may form in the cooling flow path if the pressure or temperature is not appropriate. Therefore, if the bubble sensor 250 detects bubbles, it transmits this information to the control unit, which then adjusts its control accordingly.

[0093] Furthermore, the cooling channel located in the main unit is further equipped with an emergency discharge channel. The emergency discharge channel branches off from the cooling channel and is a path for discharging refrigerant to the outside. An emergency discharge valve is provided on the emergency discharge channel. In a normal cooling process, the emergency discharge valve closes the emergency discharge channel, and selectively opens in an abnormal cooling process. When the emergency discharge valve is opened, the refrigerant supplied from the refrigerant reservoir is discharged to the outside through the emergency discharge channel rather than proceeding towards the handpiece. On the other hand, of the cooling channels, a portion of the rear section located outside the main body is connected at one end to the joint coupling 260, and the other end forms a cooling channel inside the handpiece and is connected to the aforementioned cooling module 150. Such cooling channels on the outside of the main body may be provided within the connecting section shown in Figure 1, or a separate conduit may be formed.

[0094] Specifically, the method by which the control unit generates cooling pulses to control the cooling performance of the cooling unit will be explained separately for the case where the first and second modes (modes that treat using a single frequency) are selected and the third mode (modes that treat using multiple frequencies) is selected.

[0095] First, let's explain what happens when you select modes 1 and 2. As shown in Figure 18(A), when the first mode is selected, the control unit can output a first cooling pulse for each off-time of each sub-RF pulse of the RF pulse train in the first mode, and control the cooling unit so that the cooling unit cools the electrodes until the next on-time begins. As shown in Figure 18(B), when the second mode is selected, the control unit can output a second cooling pulse for each off-time of each sub-RF pulse of the RF pulse train in the second mode, and control the cooling unit so that the cooling unit cools the electrodes until the next on-time begins.

[0096] This configuration allows for a stable reduction in electrode temperature at each point immediately before RF energy is applied to the patient's skin, by periodically cooling the electrodes between each sub-RF pulse. As a result, the phenomenon of electrodes overheating and causing skin damage can be effectively suppressed, and the uniform maintenance of electrode temperature ensures that RF energy is delivered to the skin with consistent quality, improving the consistency and effectiveness of the treatment. Furthermore, by maintaining a low temperature for the RF energy delivery section that comes into direct contact with the skin, the heat sensation and pain experienced by the patient can be alleviated, which contributes to improving user satisfaction and skin safety throughout the entire procedure.

[0097] Furthermore, if the same amount of RF energy is transmitted to the skin tissue in both the first mode and the second mode, the power of the sub-RF pulse in the first mode is greater, which leads to the problem of increased patient discomfort. To solve this problem, the control unit can set the power of the cooling pulses, which are placed during the off-time of the sub-RF pulse in the first mode, to be greater than that in the second mode.

[0098] On the other hand, while the cooling control of the present invention has been described as a preferred embodiment in which a cooling pulse is output for each off-time of each sub-RF pulse until the start of the next on-time, the present invention is not limited thereto. The control unit can control the cooling unit to output cooling pulses not only during the off-time of the sub-RF pulse, but also up to a certain point after the next on-time, as needed. This enables more aggressive cooling under conditions where heat accumulation is expected, and allows for flexible temperature control in a variety of treatment environments.

[0099] Next, we will explain the case where treatment is performed using the third mode. Even when the user selects a mode for treatment using multiple frequencies, the control unit can, in the same manner as when the user selects a mode for treatment using a single frequency, output a first cooling pulse for each off-time of a plurality of sub-RF pulses included in the first interval, and control the cooling unit so that the cooling unit cools the electrode until the next on-time begins. Similarly, for each off-time of a plurality of sub-RF pulses included in the second interval, output a second cooling pulse so that the cooling unit cools the electrode until the next on-time begins, and control the cooling unit.

[0100] Thus, even in modes where RF energy is sequentially applied in different intervals based on multiple frequencies, by configuring the system to utilize the off-time between sub-RF pulses for each interval to ensure effective cooling, electrode overheating can be prevented and the electrode temperature can be maintained at a constant level. As a result, the quality of energy transmitted to the skin can be stably maintained, while minimizing irritation to the patient's skin, thereby improving the stability of the procedure and user satisfaction.

[0101] Furthermore, as shown in Figure 18(C), although the power of the cooling pulses in the first and second sections is the same, the control unit can also control the power of the cooling pulses based on the power of the respective sub-RF pulses in the first and second sections. In one embodiment, if the total amount of RF energy in the first section is set to be greater than the total amount of RF energy in the second section, the total amount of energy of the cooling pulses included in the first section can be set to be greater than the total amount of RF energy in the second section. On the other hand, the RF energy transfer device further comprises one or more temperature measuring units for sensing the electrode temperature in real time. The temperature measuring units are located on or inside the electrode and are configured to continuously measure and monitor the electrode temperature during RF energy generation and transfer.

[0102] As shown in Figure 19, if the electrode temperature detected by the temperature measurement unit rises above a preset critical temperature, the control unit can immediately interrupt the generation of currently operating RF energy and the generation and output of the pulse train to ensure electrode safety and reduce patient discomfort. At the same time, the control unit can generate and output a third cooling pulse to control the cooling unit so that the cooling unit cools the electrode rapidly.

[0103] This allows for real-time detection of excessive electrode heating during RF energy transmission, enabling immediate response and preventing adverse effects such as electrode damage or burns to the patient's skin tissue. Furthermore, the automatic temperature control mechanism improves the device's stability and reliability, creating a safe treatment environment without user intervention.

[0104] In the following, a second aspect of the present invention will be described, specifically an RF energy transfer method. However, any matters that overlap with the configuration or operation already described in the first aspect of the present invention will be omitted from the explanation.

[0105] As shown in Figure 20, the RF energy transfer method of the present invention includes: an input step S100 in which an input unit receives input from a user regarding a target RF energy to be transferred to the skin during one shot of the RF energy transfer period by a single transfer activation, and information regarding the selection of a mode that defines the form of RF energy transfer; a control step S200 in which a control unit generates the pulse train for generating RF energy based on the target RF energy to be transferred from the input unit and the mode; an RF energy generation step S300 in which an RF energy generation unit generates RF energy based on the pulse train generated in the control step; and an RF energy transfer step S400 in which an RF transfer unit transfers the RF energy generated in the RF energy generation step to the skin via electrodes.

[0106] Here, in the control step S200, the method by which the control unit generates pulse trains for each of the first and second modes using a single frequency and the mode using multiple frequencies is as described in the first embodiment. Furthermore, the RF energy transfer method further includes a cooling step in which the electrodes are cooled by a cooling unit, and the manner in which the cooling unit performs the cooling step is as described in the first embodiment.

[0107] Furthermore, the RF energy transfer method further includes a temperature measurement step in which a temperature measuring unit measures the temperature of the electrode, and if the temperature measured in real time by the temperature measuring unit is above a predetermined temperature, for example, 43°C, the control unit can terminate the generation and output of the balstrain, and at the same time the control unit can generate and output a third cooling pulse to rapidly cool the electrode and control the cooling unit.

[0108] The embodiments described above primarily focus on devices that transmit RF energy to treat skin tissue non-invasively. However, the present invention is not limited to this and can be applied to RF energy transmission devices using various energy sources such as light energy and ultrasonic energy. Furthermore, while the above description applies mainly to the treatment of facial skin tissue using RF energy, it goes without saying that it can also be used for skin tissue in other areas similar to facial skin tissue.

[0109] Although one embodiment of the present invention has been described in detail above, the present invention is not limited to the above embodiment. It is made clear that a person with ordinary skill in the art to which the present invention belongs can implement the present invention in various ways by modifying or changing it without departing from the scope of the technical features of the present invention as defined in the appended claims.

Claims

1. In an RF energy transmission device configured to transmit RF energy to the skin by a pulse train that includes multiple sub-RF pulses, each consisting of an on-time when RF energy is transmitted to the skin and an off-time when RF energy is not transmitted to the skin, An input unit that receives information from the user regarding the target RF energy to be transmitted to the skin during one shot of the RF energy transmission period caused by a single transmission activation, and information regarding the selection of a mode that defines the mode of RF energy transmission; A control unit that generates the pulse train for generating RF energy based on the target RF transfer energy and the mode input from the input unit; An RF energy generation unit that generates RF energy based on the pulse train generated by the control unit; An RF energy transmission unit that transmits the RF energy generated from the RF energy generation unit to the skin via electrodes; Includes, The control unit, When a multimode signal is input that divides the target RF transmission energy into a first section and a second section following the first section and transmits them to the skin, The pulse trains for the first and second sections are generated such that the frequencies of the multiple RF subpulses included in the pulse train for the first section are higher than the frequencies of the multiple RF subpulses included in the pulse train for the second section, and the total amount of energy transmitted to the skin in the first section is greater than the total amount of energy transmitted to the skin in the second section. RF energy transmission device.

2. The first frequency is between 6 MHz and 8 MHz. The second frequency is between 1 MHz and 3 MHz. The RF energy transmission device according to claim 1.

3. The power (W) of the multiple sub-RF pulses in the first section is the same as that of each other. The power of the multiple sub-RF pulses in the second section is the same as that of each other. The RF energy transmission device according to claim 1 or 2.

4. In the multiple sub-RF pulses included in the first section, the on-time is 100 ms or more, and the off-time is 50 ms or more. In the multiple sub-RF pulses included in the second section, the on-time is 100 ms or more, and the off-time is 50 ms or more. The RF energy transmission device according to claim 1 or 2.

5. The RF energy transfer unit further includes a cooling unit for cooling the electrodes; The control unit, For each off-time of the multiple sub-RF pulses included in the first section, a first cooling pulse is output to control the cooling unit so that it cools the electrode until the next on-time begins. For each off-time of the multiple sub-RF pulses included in the second interval, a second cooling pulse is output to control the cooling unit so that it cools the electrode until the next on-time begins. The RF energy transmission device according to claim 1 or 2.

6. The RF energy transfer unit further includes one or more temperature measuring units for detecting the temperature of the electrode; The control unit, If the temperature detected by the temperature measuring unit exceeds a predetermined temperature, the generation of the pulse train is interrupted. The cooling unit outputs a third cooling pulse to cool the electrode and controls the cooling unit. The RF energy transmission device according to claim 5.

7. In an RF energy transmission method that transmits RF energy to the skin using a pulse train that includes multiple sub-RF pulses, each consisting of an on-time when RF energy is transmitted to the skin and an off-time when RF energy is not transmitted to the skin, Input step: The input unit receives information from the user regarding the target RF energy to be transmitted to the skin during one shot of the RF energy transmission period caused by a single transmission activation, and information regarding the selection of a mode that defines the mode of RF energy transmission; A control step in which the control unit generates the pulse train for generating RF energy based on the target RF transfer energy input from the input unit and the mode; An RF energy generation step in which an RF energy generation unit generates RF energy based on the pulse train generated in the control step; An RF energy transfer step in which the RF energy generated in the RF energy generation step is transferred to the skin via electrodes by an RF energy transfer unit; Includes, In the control step, the control unit, When a multimode is selected that divides the target RF transmission energy into a first section and a second section following the first section and transmits them to the skin, The pulse trains for the first and second sections are generated such that the frequencies of the multiple RF subpulses included in the pulse train for the first section are higher than the frequencies of the multiple RF subpulses included in the pulse train for the second section, and the total amount of energy transmitted to the skin in the first section is greater than the total amount of energy transmitted to the skin in the second section. RF energy transfer method.

8. The first frequency is between 6 MHz and 8 MHz. The second frequency is between 1 MHz and 3 MHz. The RF energy transfer method according to claim 7.

9. In the control step, the control unit, The power (W) of the multiple sub-RF pulses in the first section is the same as that of each other. The power of the multiple sub-RF pulses in the second section is controlled to be the same as that of each other. The RF energy transfer method according to claim 7 or 8.

10. In the control step, the control unit, In the multiple sub-RF pulses included in the first section, the on-time is set to be 100 ms or more, and the off-time is set to be 50 ms or more. In the multiple sub-RF pulses included in the second section, the on-time is set to be 100 ms or more, and the off-time is set to be 50 ms or more. The RF energy transfer method according to claim 7 or 8.

11. A cooling step of cooling the electrode with a cooling unit; further comprising, In the cooling step, the control unit, For each off-time of the multiple sub-RF pulses included in the first section, a first cooling pulse is output to control the cooling unit so that it cools the electrode until the next on-time begins. For each off-time of the multiple sub-RF pulses included in the second interval, a second cooling pulse is output to control the cooling unit so that it cools the electrode until the next on-time begins. The RF energy transfer method according to claim 7 or 8.

12. A temperature measurement step further includes detecting the temperature of the electrode using a temperature measuring unit; In the cooling step, the control unit, If the temperature of the electrode detected in the temperature measurement step exceeds a predetermined temperature, the generation of the pulse train is interrupted. The cooling unit outputs a third cooling pulse to cool the electrode and controls the cooling unit. The RF energy transfer method according to claim 11.

Images