RF energy transmission apparatus and RF energy transmission method

Abstract

The present invention relates to an RF energy transmission apparatus and an RF energy transmission method, wherein information about target RF transmission energy to be transmitted to the skin and information about the selection of a mode defining the form of RF energy transmission are received as input to generate pulse trains, and if a multi-mode is input, pulse trains of a first section and a second section, having a smaller frequency and a smaller total amount of energy than the first section, are generated to transmit RF energy in a non-invasive form to a patient's skin tissue, such that the patient's pain can be reduced, and simultaneously, RF energy can be controlled to ensure that a certain level of energy is accurately transmitted to a transmission location within the skin tissue.

Description

RF energy transmission device and RF energy transmission method

[0001] The present invention relates to a device for delivering RF energy to skin tissue and a method for controlling the same, and to an RF energy delivery device and RF energy delivery method for treating tissue by delivering RF pulses to the tissue.

[0002] Techniques for treating tissue lesions by delivering RF energy to a patient's skin have been developed in various ways. In particular, recent technologies have been developed that treat tissue without damaging the skin surface by cooling the skin with electrodes in contact with it and delivering RF energy. These RF energy-based treatment techniques are disclosed in Korean Patent No. 10-0706115, among others.

[0003] The present invention can reduce the pain of a patient by delivering RF energy to the patient's skin tissue in a non-invasive manner, and at the same time, can control the RF energy so that a certain level of energy can be accurately delivered to the delivery location within the skin tissue.

[0004] In addition, even if the user arbitrarily selects the RF energy to be delivered and the heating target within the skin tissue, the control method of the present invention can control the device so that excessive energy is not delivered to the skin, causing overheating or thermal damage to the device.

[0005] The present invention provides an RF energy transmission device and transmission method including an input unit that receives information on target RF transmission energy to be transmitted to the skin for a certain period of time from a user and information on selection of a mode that defines a transmission form of the RF energy, a control unit that generates a pulse train for generating RF energy according to 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 through an electrode.

[0006] As a first aspect of the present invention, an RF energy transmission device is described.

[0007] As one embodiment of the present invention, an RF energy delivery device is configured to deliver RF energy to skin according to a pulse train including a plurality of sub-RF pulses configured with an on-time during which RF energy is delivered to skin and an off-time during which RF energy is not delivered to skin, the RF energy delivery device comprising: an input unit for receiving information on target RF delivery energy to be delivered to skin during one shot, which is an RF energy delivery period according to one delivery operation from a user, and information on selection of a mode that defines a delivery form of the RF energy; a control unit for generating the pulse train for generating RF energy according to the target RF delivery energy and the mode input from the input unit; an RF energy generation unit for generating RF energy based on the pulse train generated by the control unit; An RF energy transmission unit that transmits RF energy generated from the RF energy generation unit to the skin through an electrode; wherein the control unit, when a multi-mode is input to transmit the target RF transmission energy to the skin by dividing it into a first section and a second section following the first section, generates pulse trains of the first section and the second section such that the frequency of a plurality of RF sub-pulses included in the pulse train of the first section is higher than the frequency of a plurality of RF sub-pulses 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.

[0008] In addition, in an RF energy transmission device as an embodiment of the present invention, 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.

[0009] In addition, as an embodiment of the present invention, in the RF energy transmission device, the power (W) of the plurality of sub-RF pulses in the first section may be the same as each other, and the power of the plurality of sub-RF pulses in the second section may be the same as each other.

[0010] In addition, as an embodiment of the present invention, in the RF energy transmission device, in the plurality of sub-RF pulses included in the first section, the on-time may be 100 ms or more and the off-time may be 50 ms or more, and in the plurality of sub-RF pulses included in the second section, the on-time may be 100 ms or more and the off-time may be 50 ms or more.

[0011] In addition, as an embodiment of the present invention, in the RF energy transmission device, the RF energy transmission unit may further include a cooling unit that cools the electrode, and the control unit may control the cooling unit by outputting a first cooling pulse so that the cooling unit cools the electrode until the next on-time starts for each off-time of a plurality of sub-RF pulses included in the first section, and may control the cooling unit by outputting a second cooling pulse so that the cooling unit cools the electrode until the next on-time starts for each off-time of a plurality of sub-RF pulses included in the second section.

[0012] In addition, in an RF energy transmission device as an embodiment of the present invention, the RF energy transmission unit may further include one or more temperature measuring units that detect the temperature of the electrode; and the control unit may control a third cooling unit to stop generating the pulse train and allow the cooling unit to cool the electrode when the temperature detected from the temperature measuring unit is higher than a predetermined temperature.

[0013] As a second aspect of the present invention, a method for transmitting RF energy is described.

[0014] As one embodiment of the present invention, a method for delivering RF energy to skin according to a pulse train including a plurality of sub-RF pulses consisting of an on-time during which RF energy is delivered to skin and an off-time during which RF energy is not delivered to skin, comprises: an input step for receiving, from a user through an input unit, information on target RF delivery energy to be delivered to skin during one shot, which is an RF energy delivery period according to one delivery operation, and information on selection of a mode that defines a delivery form of the RF energy; a control step for generating, through a control unit, the pulse train for generating RF energy according to the target RF delivery energy and the mode input from the input unit; an RF energy generation step for generating RF energy based on the pulse train generated in the control step by an RF energy generation unit; an RF energy delivery step for delivering, through an RF energy delivery unit, the RF energy generated in the RF energy delivery step to skin through an electrode; In the control step, the control unit provides an RF energy transfer method in which, when a multi-mode is selected to transfer the target RF transfer energy to the skin by dividing it into a first section and a second section following the first section, the frequency of a plurality of RF sub-pulses included in the pulse train of the first section is higher than the frequency of a plurality of RF sub-pulses included in the pulse train of the second section, and the total amount of energy transferred to the skin in the first section is greater than the total amount of energy transferred to the skin in the second section.

[0015] In addition, in an RF energy transmission method as an embodiment of the present invention, 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.

[0016] In addition, in the RF energy transfer method as an embodiment of the present invention, in the control step, the control unit can control the power (W) of the plurality of sub-RF pulses in the first section to be equal to each other, and the power of the plurality of sub-RF pulses in the second section to be equal to each other.

[0017] In addition, in an RF energy transfer method as an embodiment of the present invention, in the control step, the control unit may set the on-time to be 100 ms or more and the off-time to be 50 ms or more for a plurality of sub-RF pulses included in the first section, and may set the on-time to be 100 ms or more and the off-time to be 50 ms or more for a plurality of sub-RF pulses included in the second section.

[0018] In addition, as an embodiment of the present invention, in the RF energy transmission method, a cooling step of cooling the electrode by a cooling unit may be additionally included; and in the cooling step, the control unit may control the cooling unit by outputting a first cooling pulse so that the cooling unit cools the electrode until the next on-time starts for each off-time of a plurality of sub-RF pulses included in the first section, and may control the cooling unit by outputting a second cooling pulse so that the cooling unit cools the electrode until the next on-time starts for each off-time of a plurality of sub-RF pulses included in the second section.

[0019] In addition, as an embodiment of the present invention, in the RF energy transmission method, a temperature measuring step of detecting the temperature of the electrode by a temperature measuring unit may be additionally included; and in the cooling step, the control unit may control the cooling unit by outputting a third cooling unit so that, when the temperature of the electrode detected in the temperature measuring step becomes higher than a predetermined temperature, the generation of the pulse train is stopped and the cooling unit cools the electrode.

[0020]

[0021] According to the present invention, by selectively denaturing skin tissue using RF energy, a regenerative effect that induces the production of collagen fibers can be obtained, and fat cells can be effectively killed to provide skin lifting and body shaping effects.

[0022] Additionally, it has the effect of preventing excessive damage to skin tissue during skin treatment and maximizing the treatment effect.

[0023] Additionally, 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 delivered to the skin by a pulse train according to the user's selection.

[0024] In addition, even when the absorption pattern of RF energy differs depending on the patient's physiological characteristics such as constitution, skin moisture content, and subcutaneous fat distribution, or the skin tissue structure of the treatment area, it is possible to achieve optimal treatment tailored to each patient by minimizing overtreatment and undertreatment by delivering energy of a constant size.

[0025] Additionally, cooling conditions can be dynamically controlled in response to various treatment parameters, thereby maintaining optimal cooling to protect skin tissue from overheating and improve treatment stability.

[0026] In addition, the temperature of the skin or electrode is measured in real time while the RF pulse is being delivered, and if the RF energy delivered to the skin tissue accumulates excessively based on the measured temperature, a cooling pulse is immediately output to suppress pain and other discomfort felt by the patient and enhance safety during treatment.

[0027]

[0028] FIG. 1 is a perspective view illustrating an RF energy transmission device according to one embodiment of the present invention.

[0029] FIG. 2 is a block diagram showing the main configuration of the RF energy transmission device according to FIG. 1.

[0030] FIG. 3 is a perspective view illustrating an embodiment of the RF energy transmission unit of FIG. 1.

[0031] FIG. 4 is an exploded perspective view showing the main configuration of a tip module as an embodiment of the RF energy transmission unit of FIG. 3.

[0032] FIG. 5 is a cross-sectional view showing the main configuration of a tip module as an embodiment of the RF energy transmission unit of FIG. 3.

[0033] Fig. 6 is a circuit diagram illustrating an RF circuit formed during patient treatment using the RF energy transmission device of Fig. 1.

[0034] Figure 7 is a cross-sectional view schematically illustrating the skin tissue of the face.

[0035] FIG. 8 is a diagram illustrating the form of a pulse train output by a control unit according to an embodiment of the present invention.

[0036] FIG. 9 is a diagram comparing pulse trains when the energy amounts of the first mode and the second mode are the same according to one embodiment of the present invention.

[0037] Figure 10 is a diagram showing the degree of skin tissue degeneration as a result of performing the first and second modes.

[0038] Figures 11 and 12 are diagrams showing temperature changes in skin tissue as a result of performing the first and second modes.

[0039] FIG. 13 is a diagram illustrating a multi-mode pulse train according to one embodiment of the present invention.

[0040] FIG. 14 is a diagram showing the degree of degeneration of skin tissue as a result of performing multi-mode according to one embodiment of the present invention.

[0041] FIG. 15 is a diagram comparing the results of performing multi-mode according to one embodiment of the present invention with the case of using a single frequency.

[0042] Figures 16 and 17 are diagrams illustrating the effect that occurs when the energy ratios of the first and second sections of the multi-mode are different according to one embodiment of the present invention.

[0043] Figure 18 is a diagram showing the output of a cooling pulse according to one embodiment of the present invention.

[0044] FIG. 19 is a diagram showing a pulse train generated by a control unit when the temperature of an electrode is above a certain temperature according to one embodiment of the present invention.

[0045] FIG. 20 is a drawing showing an RF energy transmission method according to one embodiment of the present invention.

[0046] The technical composition and operational effects of the present disclosure are described below. However, the operational (therapeutic) mechanism includes estimation. The operational (therapeutic) mechanism does not limit the technical scope of the present disclosure.

[0047] The following description provides examples of skin tissues reached by RF energy depending on the frequency. However, it should be noted that the skin tissues reached by RF energy depending on the frequency may vary not only between individuals but also depending on various factors, including the environment. Therefore, unless specifically limited by the claims, the skin tissues reached by RF energy in the description or examples of the invention are examples for understanding the present invention and are not to be construed as limiting the claims.

[0048] Referring to the drawings, the input unit, the control unit, the RF energy generation unit, the RF energy transmission unit, the cooling unit, the temperature measurement unit 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 description below, the positional relationship of each component is described in principle based on the drawings. In addition, the drawings may simplify the structure of the invention for convenience of explanation or, if necessary, exaggerate it. Therefore, the present invention is not limited thereto, and it goes without saying that it can be implemented by adding, changing, or omitting various devices in addition to this.

[0049] The term "RF energy delivery device" refers to a medical RF device that delivers RF energy for the purpose of treatment. It also includes all devices for treating mammals, including humans. The delivery device may include various devices that deliver RF energy for the purpose of improving the condition of a lesion or skin tissue. The following examples will focus on devices for treating skin lesions. For example, it may mean that RF energy is used to locally heat skin tissue to improve wrinkles, tone and textural changes, scars and acne scarring, sagging mucosa, overall rejuvenation, hyperhidrosis, laxity, lifting, tightening, fat reduction, etc. However, it should be noted that the present invention is not limited thereto, and may be applied to various devices that deliver RF energy to various affected areas, including devices for surgically treating lesions of internal organs.

[0050] The term 'tissue' or 'skin tissue' refers to a collection of cells that make up the skin of the human body, especially the face.

[0051] Fig. 1 is a perspective view illustrating a transmission device using RF energy according to one embodiment of the present invention. The transmission device of Fig. 1 is, as an example, a medical RF device for treating a patient's skin tissue, and is an RF transmission device that uses RF energy as an energy source for treatment and transmits RF energy to a treatment location.

[0052] As illustrated in FIG. 1, a transmission device according to one embodiment of the present invention includes a main body (10) including an input unit, a control unit, an RF energy generation unit, and a handpiece (20) as an example of an RF energy transmission unit connected to the main body (10), and may further include a return unit (30). The main body (10) is equipped with various components for operating the transmission device of the present embodiment.

[0053] The outer surface of the main body (10) may be provided with an input section for inputting the treatment operation and treatment mode of the transmission device and a display section for displaying treatment-related information to the user. The interior of the main body (10) may be provided with components such as an RF energy generation section (50) and a cooling section.

[0054] As one embodiment of the present invention, a handpiece (20) is configured to perform treatment at a treatment location, and is provided in a form that a user can hold and use. An electrode (141) that non-invasively contacts the patient's skin surface and transmits RF energy is provided at one end of the handpiece (20). Various operating parts for manipulating the treatment motion may be provided on the outer surface of the handpiece (20), and a conductive path for transmitting RF energy to the electrode (141) and a cooling channel for cooling the electrode are provided on the inside of the handpiece (20).

[0055] The return portion (30) is configured in the form of a pad containing a return electrode. The return electrode is composed of a conductive material and is positioned so as to contact a location on the patient's body opposite the treatment location where the electrode of the handpiece contacts the skin during treatment. Accordingly, when RF energy is applied to the skin, the return electrode, together with the electrode (141) of the handpiece, forms a path through which the RF energy is transmitted to the patient's body.

[0056] As illustrated in Fig. 1, the handpiece (20) and the return portion (30) are each connected to the main body by a connecting portion. The connecting portion may be formed of a cable or the like, and each is electrically connected to the main body to form an RF transmission path and is configured to transmit or receive various signals.

[0057] In this embodiment, the electrode (141) of the handpiece is configured as a monopolar type having a single polarity and is provided with a separate return portion; however, the present invention is not limited thereto. As another example, if the handpiece is configured as a bipolar type having electrodes of different polarities, the handpiece may be implemented without including the aforementioned return electrode pad.

[0058] Fig. 2 is a block diagram illustrating the main configuration of the transmission device according to Fig. 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 from the control unit according to the patient's constitution, treatment purpose, treatment area, etc., and generates RF energy. The parameters may be at least one of output, pulse duration (on-time), pulse interval (off-time), and frequency.

[0059] The RF energy generating unit (50) of the present embodiment may generate RF energy having various frequencies. For example, the RF energy generating unit (50) may generate RF energy having a first frequency and RF energy having a second frequency, respectively, and in some cases, may generate RF energy having both the first frequency and the second frequency.

[0060] In addition, the RF energy generating unit (50) can generate RF energy having a selected frequency according to the progress of the selected treatment mode or treatment process, while making the time for which RF energy is generated longer or shorter, and can also generate RF pulses of different frequencies over the first and second sections, while making the number of sub-RF pulses of each frequency different.

[0061] The electrode (141) is a component that transmits RF energy generated from an RF energy generating unit to the patient's skin tissue, and may be included in the RF energy transmitting unit (20). The electrode (141) is provided at one end of a handpiece, which is an embodiment of the RF energy transmitting unit (20), and is positioned so as to make non-invasive contact with the patient's skin tissue when in use.

[0062] The electrode (141) is configured to be detachable from one end of the handpiece (20), and is configured to allow the user to select any one of a plurality of electrodes with different electrode areas. Depending on the area of ​​the electrode (141), the area through which RF energy is transmitted varies.

[0063] The electrode (141) forms an RF circuit passing through the patient's skin tissue together with the return portion (30) positioned to contact the patient's skin at a position opposite to the handpiece (20), thereby transmitting RF energy to the patient's skin tissue.

[0064] The monitoring unit (35) is configured to monitor RF energy delivered to the patient's skin tissue. The monitoring unit (35) monitors by measuring at least one RF parameter on the path of the RF circuit formed by the RF energy generation unit (50), the electrode unit (141), and the return unit (30), and calculating the RF energy delivered to the skin tissue based on the measured RF parameter.

[0065] The cooling unit (60) is configured to cool a treatment location where treatment is performed by a handpiece or an electrode that non-invasively contacts the treatment location. The cooling unit (60) can utilize various cooling methods, and as an example, the cooling unit (60) of the present embodiment is configured to cool using the heat of vaporization of a liquid refrigerant. In the present embodiment, the treatment location can be indirectly cooled by spraying a refrigerant onto a surface of the electrode (141) placed on the handpiece side that contacts the treatment location during treatment, thereby cooling the electrode. In this case, the skin surface in contact with the electrode (141) is cooled, thereby preventing excessive thermal damage to the skin surface during treatment.

[0066] The cooling unit (60) includes a refrigerant receiving portion that receives refrigerant, a cooling channel that forms a path through which the refrigerant received in the refrigerant receiving portion is delivered, and a cooling module that sprays the refrigerant delivered through the cooling channel to the rear surface of the electrode of the handpiece. The refrigerant receiving portion is provided in the main body or in a separate location. The cooling channel is connected from the refrigerant receiving portion to the cooling module, and at least a portion of the cooling channel is provided inside the handpiece. The cooling channel comprises at least one valve and sensor, and the control unit monitors the cooling process of the cooling unit (60) and controls the cooling performance using the same. Here, the cooling performance refers to the performance that can lower the temperature of the object for the same period of time, and may be the amount of refrigerant sprayed per unit time through the cooling module.

[0067] The sensing unit (80) is a component that senses various information necessary for the operation of the transmission device during treatment or before and after treatment. For example, the sensing unit (80) may be at least one of an impedance sensor that measures the impedance of skin tissue, a temperature sensor (142, temperature measuring unit) that measures the temperature of the electrode or the skin, a contact sensor that detects whether the electrode of the handpiece is in contact with the skin surface, a movement sensor that detects the movement speed of the handpiece, and a pressure sensor that detects the pressure of the cooling channel. As an example, in the present embodiment, the temperature sensor (142) and the contact sensor (not shown) are arranged at a position adjacent to the electrode of the handpiece, and a pressure sensor for monitoring the pressure at which the refrigerant is provided may be arranged in the cooling channel.

[0068] The input unit (70) is provided in the main body and is configured to input various operations of the transmission device, including the treatment mode, and the user can select and set the treatment mode to be performed through the input unit (70). Specifically, the user can set the target RF energy and treatment mode to be delivered to the skin tissue using RF energy pulses through the input unit (70). The target RF energy to be delivered to the skin tissue may be a specific numerical value or a preset level. Alternatively, the treatment lesion, the target skin tissue to be treated, the target depth, etc. may be set.

[0069] The storage unit (90) is configured to store various information required for treatment and includes a memory element. The storage unit (90) is provided in the main body (10) and may additionally be provided in the handpiece (20) or the tip module (100). The storage unit (90) can store parameter information for each treatment mode, patient-related information, control information according to sensed conditions, etc. In addition, the storage unit can update and record information sensed during treatment and information input by the user. In addition, the memory provided in the handpiece (20) or the tip module (100) can be configured to store identification information for the handpiece or the tip module.

[0070] The control unit (40) is a component that controls 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 using content input by the user through 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 controls various components using the received information. For example, the control unit (40) receives a temperature value sensed by a temperature sensor and controls the parameters of the RF pulse and the cooling performance for the electrode based on the temperature value. Alternatively, the control unit (40) controls the parameters of the RF pulse based on the information monitored by the monitoring unit. Here, the control unit (40) is configured to include a calculation unit, and can calculate a control value using the received information using a preset algorithm, and control various components based on the control value.

[0071] Fig. 3 is a perspective view illustrating the handpiece of Fig. 1. As illustrated in Fig. 3, the handpiece (20) comprises a main body (21) and a tip module (100). One end of the main body (21) is connected to a connecting portion, and various components for performing a treatment operation, such as an RF transmission circuit and a cooling path, are provided inside. An operation portion and a display portion, such as a display, may be provided on the outer surface of the main body (21). The tip module (100) is provided with an electrode (141) for transmitting RF energy by contacting the skin, and is detachably coupled to one end of the main body (21). The tip module (100) is provided with a circuit for transmitting RF energy to the electrode and a cooling structure for cooling the electrode and the treatment site. Hereinafter, the structure of the tip module will be described in more detail with reference to Figs. 4 and 5.

[0072] Fig. 4 is an exploded perspective view illustrating the main configuration of the tip module of Fig. 3, and Fig. 5 is a cross-sectional view illustrating the main configuration of the tip module of Fig. 3. Referring to Figs. 4 and 5, the tip module may be configured to include a tip housing (110), an electrode module (140), a cooling module (150), an internal case (120), and a rear cover (130).

[0073] The tip housing (110) and the inner case (120) are coupled to each other to support the electrode module (140). A cooling module (150) is arranged inside the inner case (120). The rear cover (130) is coupled to the rear of the tip housing (110) while the electrode module (140), the inner case (120), and the cooling module (150) are arranged inside the tip housing (110). The tip housing (110) or the rear cover (130) is provided with a coupling structure for being fastened to the end of the main body (21) of the handpiece.

[0074] As illustrated in FIG. 4, the electrode module (140) is configured as a flexible substrate that is foldable, and an electrical element and a circuit for electrically forming the same are formed therein. The electrode (141) is arranged at the front of the electrode module (based on the state in which the electrode module is folded) and is exposed through the opening of the tip housing (110) to come into contact with the skin surface. The electrode (141) is configured to include 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 through the dielectric layer, and when RF energy is applied to the electrode, the electrode transmits the RF energy to the skin tissue while being capacitively coupled with the skin tissue by the dielectric layer.

[0075] Meanwhile, as described above, the temperature sensor (142) and the contact sensor of the sensing unit are provided at a position adjacent to the electrode (141) among the electrode modules (140) to measure the temperature of at least one of the electrode or the skin surface and detect whether the electrode is in contact with the skin. The temperature sensor (142) of the sensing unit is an example of a temperature measuring unit. In addition, the electrode module (140) further includes a memory, and the memory can store information of the tip module, such as the type of electrode, the size of the electrode, the pattern of the electrode, the size of the cooling space, etc. The electrode module (140) is provided with a conductive lead that extends rearward and is connected to the electrode, each sensor, and the memory described above. A terminal formed at the end of the conductive lead is exposed rearward when the rear cover (130) is coupled, and is electrically connected to the RF circuit on the main body (21) side of the handpiece when the tip module (100) is coupled.

[0076] And, as described above, the cooling module (150) is configured to spray the refrigerant delivered from the refrigerant receiving portion (210) along the cooling passage (201) to the rear of the electrode (141). A conduit having a cooling passage formed therein is provided on the rear side of the cooling module (150), and a plurality of injection holes (151) are provided on the front side of the cooling module (150). The rear end of the conduit is exposed to 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 passage of the conduit is coupled with the cooling passage on the main body (21) side to form a path through which the refrigerant provided from the refrigerant receiving portion (210) is delivered.

[0077] The tip module (100) having such a structure is detachably coupled to the main body end of the handpiece as described above. When the tip module (100) is coupled, the control unit (40) receives information about the tip module from the memory of the tip module (100), and in consideration of the information, controls the RF generator (50) and the cooling unit (60) to transmit RF energy to the electrode of the tip module (100) and perform a process of cooling the electrode. In addition, the tip module (100) may be configured as a consumable, and may be replaced with a new tip module (100) when treating a new patient or exceeding the allowed number of uses. At this time, the counting of the allowed number of uses may be done based on the number of shots, which is the RF energy transmission period according to one transmission operation by the user. Meanwhile, the tip module (100) may be selected in various sizes depending on the area of ​​the electrode in contact with the skin, and for example, the area of ​​the electrode may be 0.1㎠ to 80㎠.

[0078] This ensures hygiene even when the tip module (100) comes into contact with the skin, and prevents problems such as damage to the electrode or inconsistent RF energy transmission quality that may occur when the tip module (100) is used without replacement.

[0079] The RF energy transmission device described above is electrically connected at least in part to the patient's body to form an RF circuit, and transmits RF energy to the patient's skin tissue through this to perform treatment.

[0080] Figure 6 is a schematic circuit diagram of an RF circuit formed during patient treatment using the transmission device of Figure 1. The aforementioned transmission device utilizing RF energy forms an RF circuit by being electrically connected to at least a portion of the patient's body, thereby transmitting RF energy to the patient's skin tissue to perform treatment.

[0081] Specifically, the electrode unit (141) provided at the end of the handpiece comes into contact with one side of the patient's skin surface by the user's treatment motion during treatment. In addition, the return electrode of the return unit (30) comes into contact with the patient's skin surface at a position opposite to the electrode unit (141). The electrode unit (141) of the handpiece (20) is connected to the RF energy generating unit (50) provided in the main body through a connecting unit. In addition, the return electrode of the return unit (30) is connected to a separate grounding unit.

[0082] Accordingly, when treating a patient using an RF energy transmission device, an RF circuit as shown in FIG. 6 is formed. Here, the patient's body comes into contact with the electrode unit (141) and the return unit (30) and is capacitively coupled therewith. That is, the electrode unit (141) and the return unit (30) act as a charge plate of the capacitive element, and the patient's skin tissue interposed between the electrode unit (141) and the return unit (30) acts as a dielectric of the capacitive element. Therefore, the electrode unit (141) connected to the RF generation unit (50) acts as an active electrode and applies an RF pulse to the inside of the patient's skin tissue, and the return unit (30) connected to the ground unit acts as a return electrode and forms a path along which the RF pulse applied to the inside of the skin tissue returns. Through the RF circuit formed in this manner, an RF energy pulse is applied to the patient's skin tissue to transmit RF energy, and treatment of the skin tissue is performed by the transmitted RF energy.

[0083] Meanwhile, Fig. 7 is an exemplary cross-sectional view of facial skin tissue from the surface. Those skilled in the art to which the present invention pertains will readily appreciate that cross-sectional views of skin tissue may vary depending on the body part, and thus should be mindful of this.

[0084] Skin tissue can be divided into epidermis, dermis (papillary dermis, reticular dermis), hypodermis, and fat layer from the surface. At this time, the division of each layer of skin tissue can be explained as an example, the epidermis layer, the dermis layer (papillary dermis and reticular dermis), the hypodermis layer, and the subcutaneous fat layer (fat layer). However, since the structure of skin tissue may vary depending on the physiological characteristics, age, gender, etc. of an individual, the division of such layers should not be construed as limiting the technical scope of the present invention. Therefore, a person having ordinary skill in the art to which the present invention pertains will be able to understand the concept of skin layers that can be similarly applied according to various anatomical criteria without being limited to the above division, and it is obvious that the technical idea of ​​the present invention can be equally applied to various skin tissue structures.

[0085] Each layer of skin tissue can exhibit different conductivity and permittivity in response to RF frequencies. When RF energy is delivered through the skin, the depth of heating can vary depending on the frequency of the RF energy. When the RF electrode is configured as a monopolar, RF energy is delivered from the handpiece electrode to a return electrode (not shown) separately attached to the body. The degree to which RF energy is delivered within skin tissue varies depending on the frequency. By utilizing these electrical characteristics of skin tissue and adjusting the frequency of RF energy, the desired tissue within the skin can be heated more effectively.

[0086] In general, RF energy tends to have a tendency that the deeper the energy is effectively transmitted within the skin tissue, the lower the frequency within a specific range. The control unit can adjust the frequency of the RF energy to a first frequency and a second frequency to control the portion of the skin tissue to be heated. For example, the first frequency may be selected as a frequency capable of heating the skin tissue from the epidermis to the dermis and then to the hypodermis. For example, the second frequency may be selected as a frequency capable of heating the skin tissue from the epidermis to the dermis. As described above, by applying RF energy having a specific frequency according to the electrical characteristics of each portion of the skin tissue, it is possible to effectively heat not only the epidermis to the upper dermis and the lower dermis, but also the fat layer.

[0087] Meanwhile, the control unit controls the RF energy generation unit to generate RF energy based on the pulse train generated by the control unit during one shot. Here, one shot refers to the RF energy transmission period following one transmission operation from the user.

[0088] Hereinafter, an example will be described of a method in which a control unit generates a pulse train for generating RF energy based on information regarding a target RF transmission energy to be delivered to the skin during one shot and information regarding a selection of a mode that defines the transmission form of the RF energy.

[0089] First, the user inputs information regarding the target RF energy to be delivered to the skin during a single shot and information regarding the selection of a mode that defines the form of delivery of the RF energy through the input unit of an RF energy delivery device according to one embodiment of the present invention. The form of inputting the information may be a touch display, button-type, or dial-type.

[0090] The input section may have a tab for selecting an energy level, which is information about the target RF energy to be delivered to the skin during one shot. The user may input a specific numerical value for the target RF energy to be delivered to the skin during one shot, or may directly input a preset energy level.

[0091] Additionally, the input unit includes a tab for selecting a mode that defines the form of RF energy delivery during a single shot. The user can select one of multiple modes depending on the target location to be treated within the patient's skin tissue. In one embodiment, the user can select the first mode, the second mode, or the third mode depending on the user's purpose, such as how deep the target location to which RF energy is primarily to be delivered is from the skin surface. In this case, the first and second modes may be modes for treatment using a single frequency, and the third mode may be a mode for treatment using multiple frequencies.

[0092] As another example, even if the user selects the desired mode, an undesired area may be treated depending on the thickness or moisture content of each skin tissue that constitutes the skin, the condition at the time of treatment, etc., for each person. To prevent this, the user may be asked to reconfirm the selection of the mode, or a mode that can deliver RF energy with optimal efficiency depending on the heating location and the energy to be delivered to the location may be recommended to the user, or the control unit may automatically modify the mode to deliver RF energy with optimal efficiency to the heating location.

[0093] Meanwhile, the input unit may be configured to automatically recognize and input the size of the module tip or the area size of the electrode selected by the user, or may be configured to allow the user to directly input the information. The control unit may receive electrode area information from the input unit, and based on the received electrode area information, optimize parameters such as the number of sub-RF pulses of the pulse train and cooling conditions. In one embodiment, as the size of the module tip selected by the user increases, the control unit may control the number of sub-RF pulses included in the pulse train to increase.

[0094] The control unit generates a pulse train that generates RF energy based on information received from the input unit. The pulse train generated by the control unit is input to the RF energy generation unit and configured to generate RF energy according to the pulse train. That is, referring to the pulse train as an example illustrated in FIG. 8, the pulse train generated by the control unit is an on-time (t) at which RF energy is transmitted to the skin. on ) and off-time (t) during which RF energy is not delivered to the skin. off ) is composed of. In the pulse train, the on-time is arranged alternately with the off-time, and the sub-RF pulses (t) are composed of the on-time and off-time in sequence or the off-time and on-time in sequence in the pulse train. sub ) may be included in a pulse train.

[0095] Below, we explain in detail the criteria by which each pulse train is generated when the user selects mode 1 or 2.

[0096] The first mode is a mode capable of transmitting RF energy from the epidermis layer to the upper dermis layer using a single frequency, and the second mode is a mode capable of transmitting RF energy from the epidermis layer to the upper dermis layer and the lower dermis layer using a single frequency. However, the present invention is not limited thereto, and in fact, if the RF energy transmitted through the second mode reaches the subcutaneous tissue, which is a deeper region of the skin, it is also included in the technical idea and scope of the rights of the present invention.

[0097] The control unit obtains, through the input unit, information about the target RF transmission energy to be delivered to the skin during one shot selected by the user and information about the selection of a mode that defines the transmission form of the RF energy.

[0098] The information regarding the target RF delivery energy may, for example, refer to the total amount of RF energy ultimately intended to be delivered to the skin during a single shot. Furthermore, the target RF delivery energy information may be limited to a selectable range within a preset reference range, taking into account the user's safety and treatment efficiency. For example, the system may pre-store upper and lower limits for the total amount of RF energy delivered or the maximum output energy per sub-RF pulse, and the system may be configured to allow the user to select a desired value within the range.

[0099] Additionally, information regarding the selection of a mode that defines the form of delivery of RF energy may include information that the user has selected either a first mode or a second mode that is capable of delivering RF energy to a deeper area of ​​the skin than when the first mode is selected.

[0100] The frequency of the sub-RF pulse included in the pulse train of the first mode and the frequency of the sub-RF pulse included in the pulse train of the second mode can be set to be the same.

[0101] The frequency of the RF energy used in the first and second modes can be set differently depending on the depth of the treatment target area, the patient's skin characteristics (e.g., skin moisture content, fat layer distribution, etc.), and the treatment purpose. However, based on statistical analysis and clinical data, it is preferably effective to select within the range of about 6 MHz to 8 MHz, and as a more preferable range, a frequency range of about 6.5 MHz to 6.9 MHz can be selected, and even more preferably, a frequency range of about 6.7 MHz to 6.8 MHz can be selected. Among these ranges, referring to FIG. 10, 6.78 MHz in particular showed an excellent effect in the degree of skin tissue degeneration, and is also advantageous in terms of treatment effect and safety, and thus can be adopted as a specific embodiment.

[0102] The frequency range of 6 MHz to 8 MHz as described above may generally be a frequency band in which RF energy can effectively penetrate from the skin surface to the dermis layer, beyond the epidermis layer. However, the actual penetration depth of RF energy may vary depending on the individual skin characteristics of the patient, such as skin moisture content, thickness of subcutaneous fat, body temperature, physiological conditions at the time of treatment, etc. In one embodiment of the present invention, it may be configured to select or automatically adjust an appropriate frequency considering the user's characteristics.

[0103] Meanwhile, when comparing the case where the amount of RF energy delivered to the skin in the first mode and the amount of RF energy delivered to the skin in the second mode are selected to be the same, the number of sub-RF pulses, on-time, and off-time of the first mode and the second mode can be set to be different from each other, and the number of sub-RF pulses of the first mode can be greater than the number of sub-RF pulses of the second mode, and the on-time and off-time of the first mode can be set shorter than the on-time and off-time of the second mode.

[0104] Fig. 9(A) illustrates an example of a pulse train of the first mode when using a single frequency, and Fig. 9(B) illustrates an example of a pulse train of the second mode when using a single frequency.

[0105] In the embodiment illustrated in FIG. 9, in the first mode, except for the first tuning pulse, the pulse train has 12 sub-RF pulses having the same power (W) of about 200 watts (W), the on-time of the sub-RF pulses is about 80 ms, and the off-time of the sub-RF pulses is about 50 ms. In addition, in the second mode, except for the first tuning pulse, the pulse train has 6 sub-RF pulses having the same power (W) of about 150 watts (W), the on-time of the sub-RF pulses is about 150 ms, and the off-time of the sub-RF pulses is about 100 ms.

[0106] Referring to FIG. 9, when the target RF transmission energy selected by the user is the same in the first and second modes, when the first mode is selected, the number of sub-RF pulses included in the pulse train generated by the control unit (hereinafter, sub-RF pulses of the first mode) is greater than the number of sub-RF pulses included in the pulse train generated by the control unit (hereinafter, sub-RF pulses of the second mode) when the second mode is selected, and the on-time and off-time of the sub-RF pulses of the first mode can be configured to be shorter than the on-time and off-time of the sub-RF pulses of the second mode.

[0107] When the second mode is selected, the control unit may be configured to control the number of sub-RF pulses included in the pulse train within a range of 3 to 10, preferably 4 to 7. In addition, when the first mode is selected, the control unit may control the number of sub-RF pulses of the first mode within a range corresponding to 2 to 10 times the number of sub-RF pulses of the second mode. For example, when 5 sub-RF pulses are included in the second mode, the control may be configured to include 10 to 50 sub-RF pulses in the first mode.

[0108] When the target RF delivery energy is the same, the first mode generates a pulse train to output shorter pulses and higher power than the second mode. When RF pulse energy is delivered to the skin based on this pulse train, RF energy is accumulated while minimizing thermal diffusion, so that heat can be effectively delivered from the epidermis to the upper dermis.

[0109] In the second mode, a small number of sub-RF pulses can be used to deliver focused, low-power RF pulse energy with sufficiently long on-times to the lower dermis. This is achieved by balancing sustained heat accumulation with cooling periods (thermal relaxation), allowing heat to be delivered to the dermis and superficial adipose tissue. Under certain conditions, fibrous septa can be targeted and heated without affecting fat cells.

[0110] As another embodiment, the number of sub-RF pulses included in the pulse trains of the first and second modes can be controlled according to the area of ​​the electrode of the RF energy transmission unit. For example, the larger the area of ​​the electrode selected by the user, the greater the number of sub-RF pulses in the first and second modes can be controlled. This is because the larger the area of ​​the electrode, the wider the area to which RF energy is applied to the skin, but the lower the density of RF energy compared to the same amount of RF energy applied to the corresponding area. Therefore, by controlling the number of sub-RF pulses to increase, RF energy can be configured to be intensively transmitted to the epidermis.

[0111] Meanwhile, the sub-RF pulse of the first mode and the sub-RF pulse of the second mode can be 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 differently.

[0112] However, the power of the sub-RF pulse of the first mode is determined according to the number of sub-RF pulses set in the first mode, and the power of the sub-RF pulse of the second mode can also be determined according to the number of sub-RF pulses set in the second mode. In this way, in order to maintain the total target RF transmission energy constant, the number and power of the sub-RF pulses in each mode can be controlled in conjunction with each other.

[0113] In addition, the output power (W) of each of the plurality of sub-RF pulses included in the first mode can be controlled to be maintained the same, and the plurality of sub-RF pulses included in the second mode can also be controlled to be output with the same power.

[0114] This configuration ensures output uniformity between sub-RF pulses within each mode, ensuring even energy distribution across skin tissue under identical treatment conditions. As a result, it prevents excessive or insufficient energy from being concentrated in specific areas, reducing side effects such as pain, overheating, and burns during or after treatment, and enhancing treatment precision and safety.

[0115] In addition, the uniform control of the output power increases the reliability of the system, which allows the user to obtain more predictable and consistent treatment results. In addition, when the target RF transmission energy to be applied to the skin is the same in the first and second modes, the control unit can set the power of each of the plurality of sub-RF pulses in the second mode to a value lower than the power of each of the plurality of sub-RF pulses in the first mode. This is because, in order to effectively heat a relatively deeper location of the skin tissue, the sub-RF pulse must have a long on-time, which causes the patient to feel pain, and therefore, the power of the sub-RF pulse can be reduced to reduce the patient's pain.

[0116] Meanwhile, for each sub-RF pulse of the RF pulse train of the first mode, the on-time may be set to be 30 ms or more and 100 ms or less, and the off-time may be set to be 10 ms or more and 50 ms or less, and for each sub-RF pulse of the RF pulse train of the second mode, the on-time may be set to be 100 ms or more and 300 ms or less, and the off-time may be set to be 50 ms or more and 200 ms or less.

[0117] The setting of on-time and off-time within this range is to implement an energy delivery pattern suitable for the treatment purpose of each mode, and the inventors of the present invention were able to confirm that RF energy was effectively delivered to the epidermal layer and dermal layer of the skin. It is presumed that in the first mode, uniform thermal stimulation is provided to the epidermal layer and upper dermal layer of the skin through short and rapid repetitive stimulation, and in the second mode, deep energy delivery that reaches the epidermal layer and upper and lower dermal layers of the skin is implemented through relatively long stimulation.

[0118] That is, in order to secure the target amount of accumulated RF energy even in a short period of time, the sub-RF pulse of the first mode is configured to be applied briefly with high power, and conversely, the second mode is configured to be applied long with relatively low power, so that the depth and skin tissue to which RF energy is delivered can be different even when the first and second modes are set to the same energy.

[0119] Accordingly, the power (W) of each of the plurality of sub-RF pulses included in the first mode can be configured to be maintained identically, and the plurality of sub-RF pulses included in the second mode can also be controlled to be output with the same power. This enables uniform energy transfer of the sub-RF pulses within each mode, thereby achieving a stable therapeutic effect.

[0120] As shown in an experimental example in Fig. 10, when the target RF transmission energy to be applied to the skin is the same in the first and second modes, and the degree of skin tissue degeneration is compared by heating the skin tissue using a frequency of 6.78 MHz, it can be confirmed that when the first mode is performed (left), degeneration progresses a lot in a relatively shallow area, and when the second mode is performed (right), it can be confirmed that degeneration progresses a lot in a relatively deep area.

[0121] As in the experimental examples shown in Figures 11 and 12, when the target RF transmission energy to be applied to the skin is the same as 75 J in the first and second modes, the degree of heating can be confirmed at positions 3.0 mm and 5.0 mm inside the skin from the skin surface.

[0122] Specifically, when RF energy was applied by a pulse train having on / off times of sub-RF pulses corresponding to the first mode, the temperature change was 7.1℃ (34.1℃-27℃) at a location 3.0 mm inside the skin, and the temperature change was 3.9℃ (29.9℃-26℃) at a location 5.0 mm inside the skin. On the other hand, when RF energy was applied by a pulse train having on / off times of sub-RF pulses corresponding to the second mode, the temperature change was 12.2℃ (39.2℃-27℃) at a location 3.0 mm inside the skin, and the temperature change was 8℃ (29.9℃-26℃) at a location 5.0 mm inside the skin.

[0123] These experimental results confirmed that the second mode, which has relatively long on-time and off-time of sub-RF pulses, can effectively transfer energy to and heat skin tissue 3.0 mm to 5.0 mm inward of the skin (generally corresponding to the lower dermis region) compared to the first mode.

[0124] Therefore, according to the present invention, the user can select an appropriate energy level and delivery mode according to the patient's skin condition or treatment purpose, and the control unit can adjust the configuration of the pulse train accordingly, thereby enabling stable and efficient delivery of RF energy.

[0125] Below, the third mode is explained in detail with examples.

[0126] The control unit obtains, through the input unit, information about the target RF transmission energy to be delivered to the skin during one shot selected by the user and information about the selection of a mode that defines the transmission form of the RF energy.

[0127] At this time, a third mode (multi-mode) may be selected in which the user divides the target RF transmission energy into a first section and a second section following the first section and delivers the energy to the skin.

[0128] The first section and the second section each include one or more pulse trains, and the control unit can control the generation of pulse trains corresponding to each section under different conditions to deliver RF energy to the skin.

[0129] The plurality of sub-RF pulses included in the pulse train of the first section can be configured to have a higher frequency than the plurality of sub-RF pulses included in the pulse train of the second section. That is, in the first section, RF energy having a higher frequency than the frequency of the sub-RF pulses in the second section can be applied, and in the second section, sub-RF pulses having a lower frequency than the frequency of the sub-RF pulses in the first section can be controlled to be generated.

[0130] The frequency of the sub-RF pulse included in the pulse train in the first section (hereinafter, “first frequency”) can be preferably set within a range of 6 MHz or more and 8 MHz or less, and the frequency of the sub-RF pulse in the second section (hereinafter, “second frequency”) can be preferably set within a range of 1 MHz or more and 3 MHz or less.

[0131] As illustrated in FIG. 13, the power between sub-RF pulses in the first section, which is a section composed of sub-RF pulses having a frequency of 6.78 MHz in the pulse train, can be configured to be approximately 200 watts (W), and the power between sub-RF pulses in the second section, which is a section composed of sub-RF pulses having a frequency of 2.00 MHz, can be configured to be approximately 150 watts (W).

[0132] In the first section, RF energy having a frequency of 6.78 MHz is delivered to the skin tissue with the target heating location being from the epidermis layer to the dermis layer of the skin, and subsequently, in the second section, RF energy having a frequency of 2.00 MHz, which is lower than the sub-RF pulse in the first section with the target heating location being from the epidermis layer to the fat layer of the skin, is delivered to the skin tissue. Therefore, the density of RF energy delivered to the skin tissue in the second section is lower than the energy density delivered in the first section, and as a result, the temperature of the epidermis layer and the upper dermis layer of the skin is not increased above the target temperature but can be maintained at the target temperature.

[0133] This can be confirmed through experiments as shown in Figures 14 and 15.

[0134] Fig. 14(A) shows the state of collagen when RF energy was not delivered (Baseline), Fig. 14(B) shows the state of collagen when RF energy was delivered using a 6.78 MHz single-frequency RF pulse, and Fig. 14(C) shows the state of collagen when RF energy at a frequency of 6.78 MHz and RF energy at a frequency of 2.00 MHz were sequentially delivered. Comparing the degree of collagen denaturation, it was found that when RF energy was delivered at 6.78 MHz + 2.00 MHz, the diameter of the collagen was thicker and the length was shorter, and the staining intensity was stronger, confirming that the collagen existed at a higher density, compared to when RF energy was delivered using a 6.78 MHz single-frequency RF pulse (Baseline) and when RF energy was delivered using a 6.78 MHz single-frequency RF pulse.

[0135] In addition, these results can also be confirmed through the graph of Fig. 15. When RF energy was delivered at 6.78 MHz + 2.00 MHz, it can be confirmed that the diameter of collagen is significantly thicker compared to the state where RF energy was not delivered (Baseline) and when RF energy was delivered using a 6.78 MHz single-frequency RF pulse.

[0136] In addition, the control unit can control the pulse train of each section so that the total amount of RF energy delivered to the skin in the first section is greater than the total amount of RF energy delivered to the skin in the second section. At this time, when the sum of the total amount of RF energy delivered to the skin in the first section and the total amount of RF energy delivered to the skin in the second section is 100%, the ratio of the total amount of RF energy delivered to the skin in the first section may be greater than 50%, preferably greater than 55% and less than 70%, and particularly preferably 60%.

[0137] Comparative data of RF energy delivered to collagen while changing the ratio of the total energy amount of the first section where a sub-RF pulse with a frequency of 6.78 MHz is generated and the total energy amount of the second section where a sub-RF pulse with a frequency of 2.00 MHz is generated, but the sum of the total energy amounts of the first section and the second section is the same at 150 J are shown in Figs. 16 and 17. As can be seen in Figs. 16 and 17, the diameter of collagen was large in conditions 4, 5, and 6 where the total energy amount of the first section was greater than the total energy amount of the second section, and in particular, the diameter of collagen was the largest in condition 4 where the total energy amount of the first section was 90 J and the total energy amount of the second section was 60 J.

[0138] According to this configuration, the first section utilizes high frequency to provide more focused and concentrated energy stimulation to skin tissues closer to the surface, such as the epidermis and dermis, thereby achieving effects such as enhanced skin elasticity and inducing collagen production. Conversely, the second section delivers less energy at low frequency than the first section, thereby achieving an overall treatment balance for skin tissues closer to the deeper layers, such as the lower dermis and fat layer, compared to the first section.

[0139] Because the energy delivered can vary depending on the location and depth of the skin layer targeted for heating in each section, frequency settings can be varied. Specifically, the first section primarily targets the epidermis and dermis, and by using the relatively high-frequency first frequency, precise thermal stimulation limited to the skin's surface can be provided.

[0140] On the other hand, in the second section, since the target for heating is a deeper layer including the upper and lower dermis layers as well as the epidermis layer, the second frequency, which is a low-frequency region with a greater penetration depth, can be used to enable effective heat transfer to the lower dermis layer and fat layer.

[0141] Additionally, the control unit can control the output power (power, W) between the plurality of sub-RF pulses included in the pulse train of the first section to be the same as each other, and can also control the output power between the plurality of sub-RF pulses included in the pulse train of the second section to be the same as each other.

[0142] According to this configuration, the energy transfer deviation between sub-RF pulses within each section can be minimized, and as a result, the RF energy delivered to the skin is uniformly distributed across sections, so that a consistent heating effect can be obtained throughout the treatment area.

[0143] In addition, the on-time of the 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 the 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. The on-time of the sub-RF pulses of the first and second sections is set to 100 ms or more so that RF energy can be deeply transmitted to the lower dermis layer and fat layer of the skin layer.

[0144] Below, the cooling unit configuration is described.

[0145] The cooling unit is configured to cool the treatment site where treatment is performed by the RF energy transmission unit or to cool the electrodes included in the RF energy transmission unit. As an example, the cooling unit of the present embodiment is configured to cool the treatment site or electrodes using the heat of vaporization of a liquid coolant. Of course, the cooling unit may be configured to cool the treatment site or electrodes using the temperature of the gaseous coolant itself.

[0146] Specifically, the cooling unit includes a refrigerant receiving portion that receives refrigerant, a cooling channel forming a path through which the refrigerant received in the refrigerant receiving portion is delivered, and a cooling module that sprays the refrigerant delivered through the cooling channel toward the electrode of the RF energy transmitting portion or toward a treatment location at the rear of the electrode. The refrigerant receiving portion is provided in the main body or in a separate location. The cooling channel is connected from the refrigerant receiving portion to the cooling module, and at least a portion of the cooling channel may be provided inside the handpiece, which is an embodiment of the RF energy transmitting portion. The cooling channel comprises at least one valve and sensor, and the control unit monitors the cooling process of the cooling unit and controls the cooling performance using the same. Here, the cooling performance refers to a performance capable of lowering the temperature of the target object for the same period of time, and may be the amount of refrigerant sprayed per unit time through the cooling module.

[0147] Components such as an intelligent cooling device (ICD) filter, pressure sensor, bubble sensor, joint coupling, and ICD valve can be placed on the cooling path.

[0148] Specifically, the refrigerant receiving portion comprises a pressure vessel that receives liquid refrigerant. The refrigerant receiving portion is provided with a discharge port at one end, and the discharge port is installed downward to facilitate the discharge of the refrigerant. The discharge port is connected to one end of the cooling channel, and the liquid refrigerant is supplied to the cooling channel through the discharge port at a predetermined pressure.

[0149] Based on the direction of refrigerant flow, the front portion of the cooling channel is provided on the inside of the main body, and the rear portion 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 connected so that they can be selectively separated by a joint coupling. The joint coupling is provided on the outside of the main body, for example, and is configured so that the cooling channel can be separated from the outside of the main body when necessary.

[0150] An ICD filter, a pressure sensor, and a bubble sensor are provided on the cooling channel located in the main body.

[0151] The ICD filter is installed at the discharge end of the refrigerant receiving portion and is configured to filter foreign substances in the liquid refrigerant discharged from the refrigerant receiving portion.

[0152] A pressure sensor is installed on a cooling channel and measures the pressure of the cooling channel. The pressure of the cooling channel is determined by the pressure at which the refrigerant is discharged from the refrigerant receiving portion, and the pressure of the refrigerant receiving portion can be determined based on the value measured by the pressure sensor. Here, the pressure of the cooling channel measured by the pressure sensor can be the same as the pressure of the refrigerant receiving portion, or the pressure of the refrigerant receiving portion can be determined by reflecting a weighting factor on the measured pressure of the cooling channel. Since the pressure of the cooling channel affects the cooling performance of the treatment site, the pressure sensor monitors the pressure value during the cooling process and transmits the measured value to the control unit.

[0153] The bubble sensor detects whether the liquid refrigerant passing through the refrigerant passage contains bubbles. If the pressure or temperature of the refrigerant passage is not appropriate, bubbles may form within the refrigerant passage. Therefore, if the bubble sensor (250) detects bubbles, it transmits the detection to the control unit, which then reflects this information and performs control.

[0154] Furthermore, an emergency discharge path is additionally provided on the cooling path located in the main body. The emergency discharge path is a path that branches off from the cooling path and discharges the refrigerant to the outside. An emergency discharge valve is provided on the emergency discharge path. During a normal cooling process, the emergency discharge valve closes the emergency discharge path, and during an abnormal cooling process, it selectively opens. When the emergency discharge valve is opened, the refrigerant supplied from the refrigerant reservoir is discharged to the outside through the emergency discharge path rather than toward the handpiece.

[0155] Meanwhile, the rear portion of the cooling channel formed on the outside of the main body has one end connected to a joint coupling (260) and the other end forms a cooling channel inside the handpiece and is connected to the cooling module (150) described above. This cooling channel on the outside of the main body may be provided within the connection part of FIG. 1 or may form a separate conduit.

[0156] Specifically, the method of generating a cooling pulse that controls the cooling performance of the cooling unit by the control unit is explained by dividing it into cases where the first and second modes (a mode for treating using a single frequency) are selected and cases where the third mode (a mode for treating using multiple frequencies) is selected.

[0157] First, let's explain the case where mode 1 and 2 are selected.

[0158] The control unit, as in Fig. 18(A), when the first mode is selected, can control the cooling unit by outputting a first cooling pulse so that the cooling unit cools the electrode until the next on-time starts for each off-time of each sub-RF pulse of the RF pulse train of the first mode.

[0159] The control unit, as in Fig. 18(B), when the second mode is selected, can control the cooling unit by outputting a second cooling pulse so that the cooling unit cools the electrode until the next on-time starts for each off-time of each sub-RF pulse of the RF pulse train of the second mode.

[0160] This configuration allows the electrodes to be periodically cooled between each sub-RF pulse, stably lowering their temperature immediately before RF energy is applied to the patient's skin. This effectively prevents electrode overheating, which can cause skin damage. Furthermore, maintaining a consistent electrode temperature ensures that RF energy is delivered to the skin with consistent quality, improving treatment consistency and effectiveness.

[0161] Additionally, by keeping the temperature of the RF energy transmission unit that directly contacts the skin low, the heat or pain felt by the patient can be alleviated, which contributes to increasing user satisfaction and skin safety during the overall procedure.

[0162] In addition, when RF energy is delivered to skin tissue with the same amount of energy in the first mode and the second mode, the power of the sub-RF pulse in the first mode is greater, which causes a problem of increased patient pain. To solve this problem, the control unit can set the power of the cooling pulse arranged for each off-time of the sub-RF pulse in the first mode to be greater than that in the second mode.

[0163] Meanwhile, the cooling control of the present invention has been described as a preferred embodiment in which a cooling pulse is outputted before the next on-time is initiated at each off-time of each sub-RF pulse. However, the present invention is not limited thereto, and the control unit may control the cooling unit to output a cooling pulse not only during the off-time of the sub-RF pulse but also until a certain point after the next on-time, as needed. This enables more active cooling under conditions where heat accumulation is expected, and enables flexible temperature control in various treatment environments.

[0164] Next, we explain the case where the treatment mode is selected using the third mode.

[0165] Even when the user selects a mode for treatment using multiple frequencies, the control unit may control the cooling unit by outputting a first cooling pulse so that the cooling unit cools the electrode until the next on-time starts for each off-time of a plurality of sub-RF pulses included in the first section, similarly to the case where the user selects a mode for treatment using the single frequency, and may control the cooling unit by outputting a second cooling pulse so that the cooling unit cools the electrode until the next on-time starts for each off-time of a plurality of sub-RF pulses included in the second section.

[0166] Likewise, even in modes where RF energy is sequentially applied across different sections based on multiple frequencies, the off-time between sub-RF pulses in each section is utilized to effectively cool the electrode, preventing overheating and maintaining a constant electrode temperature. This allows for stable delivery of energy to the skin while minimizing irritation to the patient's skin, thereby enhancing treatment safety and user satisfaction.

[0167] In addition, as illustrated in FIG. 18(C), although the power of the cooling pulse in the first section and the second section is shown to be the same, the control unit can also control the power of the cooling pulse according to the power of each sub-RF pulse in the first section and the second section. In one embodiment, when 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 pulse included in the first section can be set to be greater than the total amount of RF energy in the second section.

[0168] Meanwhile, the RF energy transmission device may additionally be equipped with one or more temperature measurement units for detecting the temperature of the electrode in real time. The temperature measurement units may be installed on the surface or inside of the electrode and configured to continuously measure and monitor the temperature of the electrode during RF energy generation and transmission.

[0169] As illustrated in Fig. 19, the control unit can control the generation of RF energy and the generation and output of the pulse train, which are currently in operation, to immediately stop in order to ensure the safety of the electrode and reduce the patient's pain when the temperature of the electrode detected by the temperature measuring unit rises above a preset threshold temperature. At the same time, the control unit can control the cooling unit by generating and outputting a third cooling pulse so that the cooling unit can quickly cool the electrode.

[0170] This allows for real-time detection of excessive electrode heating during RF energy delivery, enabling immediate response, preventing adverse effects such as electrode damage or burns to the patient's skin tissue. Furthermore, the automatic temperature control mechanism enhances the device's stability and reliability, ensuring a safe treatment environment without user intervention.

[0171] Below, a second aspect of the present invention, a method for transmitting RF energy, will be described. However, any details that overlap with the configuration or operation already described in the first aspect of the present invention will be omitted.

[0172] The RF energy transmission method of the present invention, as illustrated in FIG. 20, includes an input step (S100) of receiving information about target RF transmission energy to be transmitted to the skin during one shot, which is an RF energy transmission period according to one transmission operation from a user, and information about selection of a mode that defines a transmission form of the RF energy; a control step (S200) of generating a pulse train for generating RF energy according to the target RF transmission energy and the mode input from the input step by a control unit; an RF energy generation step (S300) of generating RF energy based on the pulse train generated in the control step by an RF energy generation unit; and an RF energy transmission step (S400) of transmitting the RF energy generated in the RF energy generation step to the skin through an electrode by an RF transmission unit.

[0173] Here, in the S200 control step, the method by which the control unit generates pulse trains for the first and second modes using a single frequency and the mode using multiple frequencies is as described in the first aspect.

[0174] In addition, the RF energy transmission method further includes a cooling step of cooling the electrode by a cooling unit, and the manner in which the cooling unit performs the cooling step is as described in the first aspect.

[0175] In addition, the RF energy transmission method further includes a temperature measurement step of measuring the temperature of the electrode by a temperature measurement unit, and when the temperature measured in real time by the temperature measurement unit is a predetermined temperature, for example, 43 degrees or higher, the control unit can terminate the generation and output of the pulse train, and at the same time, the control unit can control the cooling unit by generating and outputting a third cooling pulse so that the cooling unit can quickly cool the electrode.

[0176] Although the embodiments described above focus on a device that transmits RF energy to treat skin tissue in a non-invasive manner, the present invention is not limited thereto and can also be applied to RF energy transmission devices that utilize various energy sources such as optical energy and ultrasonic energy. In addition, the above-described content is primarily applied to the field of treating facial skin tissue using RF energy, and of course, it can also be used for skin tissue in other areas similar to facial skin tissue.

[0177] While one embodiment of the present invention has been described in detail above, the present invention is not limited to the above-described embodiment. It will be apparent to those skilled in the art that various modifications or variations of the present invention can be made without departing from the scope of the technical features defined in the appended claims.

Claims

1. An RF energy delivery device configured to deliver RF energy to the skin according to a pulse train including a plurality of sub-RF pulses consisting of an on-time during which RF energy is delivered to the skin and an off-time during which RF energy is not delivered to the skin, An input unit for receiving information about target RF energy to be delivered to the skin during one shot, which is an RF energy delivery period according to one delivery operation from a user, and information about selection of a mode that defines the form of delivery of the RF energy; A control unit for generating the pulse train for generating RF energy according to the target RF transmission energy input from the input unit and the mode; An RF energy generating unit that generates RF energy based on a pulse train generated by the above control unit; An RF energy transmission unit that transmits RF energy generated from the RF energy generation unit to the skin through an electrode; Includes, The above control unit, When a multi-mode is input that divides the target RF transmission energy into a first section and a second section following the first section and delivers it to the skin, The pulse trains of the first and second sections are generated so that the frequency of the plurality of RF sub-pulses included in the pulse train of the first section is higher than the frequency of the plurality of RF sub-pulses included in the pulse train of the second section, and the total amount of energy delivered to the skin in the first section is greater than the total amount of energy delivered to the skin in the second section. RF energy transmission device.

2. In paragraph 1, The above first frequency is 6 MHz or more and 8 MHz or less, The above second frequency is 1 MHz or more and 3 MHz or less, RF energy transmission device.

3. In paragraph 1 or 2, The power (W) of the plurality of sub-RF pulses in the first section above is equal to each other, The power of the multiple sub-RF pulses in the second section is the same. RF energy transmission device.

4. In paragraph 1 or 2, In the plurality of 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 plurality of 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, RF energy transmission device.

5. In paragraph 1 or 2, The RF energy transmitting unit further includes a cooling unit that cools the electrode; The above control unit, Controlling the cooling unit by outputting a first cooling pulse so that the cooling unit cools the electrode until the next on-time starts for each off-time of a plurality of sub-RF pulses included in the first section; Controlling the cooling unit by outputting a second cooling pulse so that the cooling unit cools the electrode until the next on-time starts for each off-time of a plurality of sub-RF pulses included in the second section. RF energy transmission device.

6. In paragraph 5, The RF energy transmitting unit further includes one or more temperature measuring units for detecting the temperature of the electrode; The above control unit, When the temperature detected from the above temperature measuring unit is higher than a predetermined temperature, the generation of the pulse train is stopped, The cooling unit controls the cooling unit by outputting a third cooling pulse to cool the electrode. RF energy transmission device.

7. In an RF energy delivery method for delivering RF energy to the skin according to a pulse train including a plurality of sub-RF pulses consisting of an on-time in which RF energy is delivered to the skin and an off-time in which RF energy is not delivered to the skin, An input step for receiving information about target RF energy to be delivered to the skin during one shot, which is an RF energy delivery period according to one delivery operation from a user, and information about selection of a mode that defines the delivery form of the RF energy through an input unit; A control step for generating the pulse train for generating RF energy according to the target RF transmission energy input from the input unit and the mode by the control unit; An RF energy generation step for generating RF energy based on a pulse train generated in the above control step by an RF energy generation unit; An RF energy transmission step in which the RF energy generated in the RF energy generation step is transmitted to the skin through an electrode by an RF energy transmission unit; Includes, In the above control step, the control unit, When a multi-mode is selected to divide the target RF transmission energy into a first section and a second section following the first section and deliver it to the skin, The pulse trains of the first and second sections are generated so that the frequency of the plurality of RF sub-pulses included in the pulse train of the first section is higher than the frequency of the plurality of RF sub-pulses included in the pulse train of the second section, and the total amount of energy delivered to the skin in the first section is greater than the total amount of energy delivered to the skin in the second section. RF energy delivery method.

8. In paragraph 7, The above first frequency is 6 MHz or more and 8 MHz or less, The above second frequency is 1 MHz or more and 3 MHz or less, RF energy delivery method.

9. In paragraph 7 or 8, In the above control step, the control unit, The power (W) of the plurality of sub-RF pulses in the first section above is equal to each other, Controlling the power of multiple sub-RF pulses in the second section to be equal to each other, RF energy delivery method.

10. In paragraph 7 or 8, In the above control step, the control unit, In the plurality of 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 plurality of sub-RF pulses included in the second section, the on-time is set to 100 ms or more and the off-time is set to 50 ms or more. RF energy delivery method.

11. In paragraph 7 or 8, It further includes a cooling step of cooling the electrode by a cooling unit; In the above cooling step, the control unit, Controlling the cooling unit by outputting a first cooling pulse so that the cooling unit cools the electrode until the next on-time starts for each off-time of a plurality of sub-RF pulses included in the first section; Controlling the cooling unit by outputting a second cooling pulse so that the cooling unit cools the electrode until the next on-time starts for each off-time of a plurality of sub-RF pulses included in the second section. RF energy delivery method.

12. In paragraph 11, It further includes a temperature measuring step for detecting the temperature of the electrode by a temperature measuring unit; In the above cooling step, the control unit, When the temperature of the electrode detected in the above temperature measurement step is higher than a predetermined temperature, the generation of the pulse train is stopped, The cooling unit controls the cooling unit by outputting a third cooling pulse to cool the electrode. RF energy delivery method.

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