CN219149005U - Electronic equipment - Google Patents

Abstract

The utility model provides electronic equipment, which comprises a power supply device, an input device, an energy switching device and an energy output device, wherein the energy output device comprises at least two electrode assemblies, the power supply device is used for supplying power to the whole electronic equipment, and the energy switching device is used for enabling the energy output device to selectively start one of a radio frequency micro-current working mode and an electroporation ion introducing working mode according to input information generated by the input device; in the radio frequency micro-current working mode, the energy output device alternately outputs radio frequency and micro-current through the same electrode assembly, so that the effect of pulling skin tightly is achieved; in the electroporation iontophoresis working mode, the energy output device alternately outputs electroporation pulses and iontophoresis current through the same electrode assembly, so that penetration and absorption of functional components in the skin care product are promoted; the output of radio frequency, micro-current, electroporation pulse and ion-induced current share the same electrode assembly, so that the structure is simplified, and the convenience of the electronic equipment in use is improved.

Description

Electronic equipment

Technical Field

The utility model belongs to the field of medical equipment, and particularly relates to electronic equipment.

Background

When the 'primary aging' problem of skin is solved, such as the requirements of dryness, water shortage, collagen loss, slow metabolism and the like, the current electronic equipment adopts a radio frequency technology and a microcurrent technology to promote collagen synthesis, accelerates skin metabolism, and an ion introduction technology promotes skin care product permeation, helps skin to moisturize and lock water, and improves the rough skin problem.

Because the two functions of radio frequency and micro current are alternately cooperated to achieve a better effect, the current electronic equipment for preventing aging mainly adopts the radio frequency and micro current technology, but the radio frequency and micro current are usually used as separate and independent functions or equipment. Even if the radio frequency and the micro-current are integrated on the same electronic equipment at the same time, the radio frequency component and the micro-current component are arranged at different positions on the electronic equipment, and the handheld mode needs to be replaced when the functions are switched, so that the operation is particularly inconvenient. In addition, the existing electronic devices have some problems in terms of use efficiency and safety. At present, most of radio frequency design parameters are low frequency and high power, and the actually output heat energy cannot reach the depth of a dermis layer so as to influence the use efficiency, and meanwhile, the low frequency and high power can also cause skin scalding so as to reduce the safety. Moreover, most of the existing electronic devices do not monitor the output of micro-current, and cannot ensure that the output micro-current is always in a safe range, if the device is abnormal, the micro-current exceeds a safe threshold, the device not only can play a role in reacting to stimulate facial nerves to induce facial muscle movement, so that the unbalanced development of muscles is caused, but also can bring pain feeling of current stimulation to a user, and even the muscle injury can be caused.

In addition, for skin rejuvenation, it is also very important to effectively promote the penetration and absorption of the functional components of the skin care product, and it is required to know that the penetration rate of the skin care product is generally not more than 2% under the condition that electronic equipment is not used, so that the absorption rate of the functional components of the skin care product by the skin is very low and the efficacy of the skin care product is not very high. However, most of the current electronic devices do not contain a function of promoting penetration and absorption of functional components of skin care products (abbreviated as penetration promotion). For example, in some electronic devices, radio frequency heating is used to stimulate the dermis to promote absorption of the skin care product by the cells, but the skin care product cannot penetrate the stratum corneum of the skin barrier and has little skin care effect. Some electronic devices also have ion-introducing function, but ion-introducing has a certain limitation on skin care products for promoting permeation due to the action mechanism, and weakly charged and uncharged compounds are difficult to electrophoretically move, so that the effect of promoting permeation of the functional components of the skin care products for macromolecules is difficult to achieve by ion-introducing.

Disclosure of Invention

The utility model aims to provide electronic equipment, which not only realizes the alternate coordination of radio frequency and micro current and the effect of pulling skin to be compact, but also realizes the alternate coordination of electroporation and iontophoresis and promotes the penetration and absorption of functional components in skin care products.

To achieve the above object, the present utility model provides an electronic device comprising:

a power supply device for supplying power;

input means for generating input information, said input means being connected to said power supply means;

an energy switching device connected to the power supply device and the input device; the method comprises the steps of,

the energy output device is connected with the energy switching device and the power supply device and comprises at least two electrode assemblies, and each electrode assembly comprises two electrodes;

the electronic equipment is provided with a radio frequency micro-current working mode and an electroporation iontophoresis working mode;

the electronic equipment is configured to enable one of the radio frequency micro-current working mode and the electroporation iontophoresis working mode selectively according to the input information generated by the input device; in the radio frequency micro-current working mode, the energy output device alternately outputs radio frequency and micro-current through the same electrode assembly; in the electroporation iontophoresis operation mode, the energy output device alternately outputs an electroporation pulse and an iontophoresis current through the same electrode assembly; wherein the radio frequency, the microcurrent, the electroporation pulse and the iontophoresis current are output in common with the same electrode assembly.

In one embodiment, the energy output device further comprises a relay device, a radio frequency generation device, a microcurrent iontophoresis generation device and an electroporation generation device; the relay device is connected with the energy switching device; the energy switching device is used for enabling the relay device to be selectively communicated with one of the radio frequency generation device, the microcurrent iontophoresis generation device and the electroporation generation device; at least one of the electrode assemblies is connected with the radio frequency generating device, the microcurrent iontophoresis generating device and the electroporation generating device; wherein the micro-current iontophoresis generating device is shared by the iontophoresis current and the micro-current output.

In an embodiment, the number of the electrode assemblies is a plurality, at least two electrode assemblies are different in size, and the two electrode assemblies are respectively a first electrode assembly and a second electrode assembly; the output ends of the radio frequency generating device, the microcurrent iontophoresis generating device and the electroporation generating device are selectively connected with one of the first electrode assembly and the second electrode assembly.

In one embodiment, the electronic device further comprises a working head on which all of the electrode assemblies are disposed; the first electrode assembly comprises two concentrically arranged annular electrodes, the two annular electrodes are arranged on the end face of the working head, and/or the second electrode assembly comprises two L-shaped electrodes with arc-shaped outer surfaces, and the two L-shaped electrodes are arranged on the edge of the working head.

In one embodiment, the width of each annular electrode is 3 mm-5 mm, the distance between two annular electrodes is 3.5 mm-4.5 mm, and/or the radius of the arc rounded corner of each L-shaped electrode is greater than 2.5mm, and the distance between two L-shaped electrodes is 3 mm-6 mm.

In one embodiment, the electrode size in the first electrode assembly is greater than the electrode size in the second electrode assembly; the radio frequency micro-current working mode comprises a first working mode corresponding to the first electrode assembly and a second working mode corresponding to the second electrode assembly; in the first working mode, the radio frequency generating device outputs radio frequency of 2 MHz-4 MHz, and the microcurrent iontophoresis generating device outputs microcurrent of 335 mu A-500 mu A; in the second working mode, the radio frequency generating device outputs radio frequency of 1 MHz-2 MHz, and the microcurrent iontophoresis generating device outputs microcurrent of 335 mu A-500 mu A; and/or the electroporation iontophoresis operation mode includes a first operation mode corresponding to the first electrode assembly and a second operation mode corresponding to the second electrode assembly; in the first working mode, the electroporation generating device outputs electroporation pulses with the voltage of 40V-60V, the pulse width of 10 ms-20 ms and the frequency of 20 pps-30 pps, and the microcurrent iontophoresis generatingdevice outputs 200 mu A/cm² ～500μA/cm² Is introduced into the ion guide; in the second working mode, the electroporation generating device outputs electroporation pulse with voltage of 10V-20V, pulse width of 5 ms-10 ms and frequency of 10 pps-20 pps, and the microcurrent iontophoresis generating device outputs 100 mu^A /cm² ～200μA/cm² Is introduced into the ion guide system.

In one embodiment, the relay means comprises two relays, one of which is selectively connected to one of the radio frequency generating means and the microcurrent iontophoresis generating means, and the other of which is selectively connected to one of the microcurrent iontophoresis generating means and the electroporation generating means.

In one embodiment, the radio frequency generating device comprises a radio frequency generating component and a transformer, wherein the radio frequency generating component is used for connecting the relay device, the output end of the radio frequency generating component is connected with the transformer, and the output end of the transformer is connected with the electrode assembly; the radio frequency generating component is used for converting the received square wave into a sine wave and outputting the sine wave to the transformer; the transformer is used for amplifying and boosting sine waves and outputting the sine waves to the electrode assembly as radio frequency signals.

In one embodiment, the microcurrent iontophoresis generating device comprises a microcurrent iontophoresis generating component and a current regulating component, wherein the microcurrent iontophoresis generating component is used for connecting the relay device, the output end of the microcurrent iontophoresis generating component is connected with the current regulating component, and the output end of the current regulating component is connected with the electrode assembly; the microcurrent iontophoresis generating component is used for outputting microcurrent according to the received square wave signal or outputting PWM square wave signal to the current regulating component; the current regulating component is used for regulating the current density of the PWM square wave signal and outputting the PWM square wave signal to the electrode assembly.

In one embodiment, the electroporation device comprises an electroporation pulse generating component and a voltage regulating component, wherein the electroporation pulse generating component is used for connecting the relay device, the output end of the electroporation pulse generating component is connected with the voltage regulating component, and the output end of the voltage regulating component is connected with the electrode assembly; the electroporation pulse generating component is used for outputting electroporation pulses according to the received square wave signals, and outputting the electroporation pulses to the voltage regulating component after regulating the pulse width and the frequency of the electroporation pulses through PWM; the voltage regulating component is used for regulating the voltage of the electroporation pulse and outputting the voltage to the electrode assembly.

In an embodiment, in the radio frequency microcurrent operation mode, the electronic device has a plurality of gears, each gear corresponds to an output state reflecting radio frequency microcurrent output information, all output states reflected by the gears are different, radio frequency currents in all output states are kept constant, radio frequency voltages and microcurrents in different output states are different, and/or in the electroporation iontophoresis operation mode, the electronic device has a plurality of gears, each gear corresponds to an output state reflecting electroporation iontophoresis output information, all output states reflected by the gears are different, and in different output states, at least one of pulse width, frequency, voltage and current intensity of the electroporation pulse is different.

In one embodiment, the number of the electrode assemblies is plural, and at least two of the electrode assemblies are positioned asymmetrically to be adapted to different target areas.

In an embodiment, in the radio frequency micro-current operation mode, the time for the energy output device to output the radio frequency is longer than the time for outputting the micro-current, and in the electroporation iontophoresis operation mode, the time for the energy output device to output the electroporation pulse is shorter than the time for outputting the iontophoresis current.

Compared with the prior art, the technical scheme provided by the utility model has at least the following beneficial effects:

(1) The electronic device of the present utility model includes: a power supply device for supplying power; input means for generating input information, said input means being connected to said power supply means; an energy switching device connected to the power supply device and the input device; and an energy output device connected to the energy switching device and the power supply device, the energy output device including at least two electrode assemblies, each of the electrode assemblies including two electrodes; the electronic equipment integrates four functions of radio frequency, micro-current, electroporation and iontophoresis, and can selectively work in a radio frequency micro-current working mode and an electroporation iontophoresis working mode; in a radio frequency micro-current working mode, the energy output device alternately outputs radio frequency and micro-current through the same electrode assembly, and achieves the effect of pulling skin to be compact through the alternate cooperation of the radio frequency and the micro-current; in the electroporation iontophoresis working mode, the energy output device alternately outputs electroporation pulses and iontophoresis currents through the same electrode assembly, so that penetration and absorption of functional components in the skin care product are promoted through alternate coordination of electroporation and iontophoresis, and the limitation of using the iontophoresis technology alone is avoided. By the arrangement, the electronic equipment can better exert the effects, effectively improve the skin condition and ensure better user experience.

(2) The outputs of the rf, microcurrent, electroporation pulses and iontophoresis share the same electrode assembly. By the arrangement, different electrode assemblies are prevented from being configured for the output of different energies, so that the structure is simplified, a hand-held mode is not required to be replaced when the function is switched, convenience of the electronic equipment in use is improved, and meanwhile the electronic equipment is also facilitated to fully exert the effects of the electronic equipment.

Drawings

Those of ordinary skill in the art will appreciate that the figures are provided for a better understanding of the present utility model and do not constitute any limitation on the scope of the present utility model. Wherein:

fig. 1 is a schematic diagram of an external configuration of an electronic device according to an embodiment of the present application;

fig. 2 is a schematic diagram of an internal structure of an electronic device according to an embodiment of the present application;

fig. 3a is a schematic diagram of an external structure of a working head of an electronic device according to an embodiment of the present disclosure when the working head is covered during non-use;

FIG. 3b is a schematic view of a working head provided with two electrode assemblies according to an embodiment of the present application;

fig. 4 is a schematic structural diagram of a charging base according to an embodiment of the present disclosure;

FIG. 5 is a block diagram of an electronic device according to an embodiment of the present application;

FIG. 6 is a block diagram of an energy output device according to an embodiment of the present application;

FIG. 7 is a block diagram of a configuration for switching radio frequency and micro current and for switching electroporation and iontophoresis using two relays according to one embodiment of the present application;

FIG. 8 is a schematic structural diagram of alternating output of RF micro-currents according to an embodiment of the present application;

FIG. 9 is a graph of a sine wave waveform provided by an embodiment of the present application, wherein the ordinate is voltage and the abscissa is time;

FIG. 10 is a flow chart of alternating output of RF micro-currents according to one embodiment of the present application;

FIG. 11 is a flow chart of monitoring by using a safety threshold when RF micro-currents are alternately output according to an embodiment of the present application;

FIG. 12 is a schematic diagram of an alternate output of electroporation iontophoresis according to an embodiment of the present application;

FIG. 13 is a flow chart of alternate output of electroporation iontophoresis according to an embodiment of the present application;

FIG. 14 is a flow chart of monitoring with a safety threshold during alternate output of electroporation iontophoresis according to an embodiment of the present application;

FIG. 15 is a block diagram illustrating a configuration of an electronic device according to an embodiment of the present disclosure when multiple auxiliary functions are configured;

FIG. 16 is a graph showing the results of the RF microcurrent alternation synergy and comparative example of the present application for improved skin elasticity when only RF and microcurrent are used independently of each other;

FIG. 17 is a graph showing the results of a test for skin roughness improvement using RF alone for RF micro-current alternating synergy and comparative example in an embodiment of the present application;

FIG. 18 shows various output states of RF current constant and RF and micro-current in an embodiment of the present application;

FIG. 19 is a diagram showing different output states of electroporation pulses and iontophoresis in an embodiment of the present application;

FIG. 20 is a schematic diagram of switching a relay with alternating RF and micro-current outputs in an embodiment of the present application;

fig. 21 is a schematic diagram of relay switching for alternate output of electroporation pulses and iontophoresis in an embodiment of the present application.

Detailed Description

The present utility model will be described in more detail below with reference to the drawings, in which preferred embodiments of the utility model are shown, it being understood that one skilled in the art can modify the utility model described herein while still achieving the advantageous effects of the utility model. Accordingly, the following description is to be construed as broadly known to those skilled in the art and not as limiting the utility model.

In the interest of clarity, not all features of an actual implementation are described. In the following description, well-known functions or constructions are not described in detail since they would obscure the utility model in unnecessary detail. It should be appreciated that in the development of any such actual embodiment, numerous implementation details must be made to achieve the developer's specific goals, such as compliance with system-related and business-related constraints, which will vary from one implementation to another. In addition, it will be appreciated that such a development effort might be complex and time-consuming, but would nevertheless be a routine undertaking for those of ordinary skill in the art. The utility model is more particularly described by way of example in the following paragraphs with reference to the drawings. The advantages and features of the present utility model will become more apparent from the following description. It should be noted that the drawings are in a very simplified form and are all to a non-precise scale, merely for convenience and clarity in aiding in the description of embodiments of the utility model.

Furthermore, the terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the application. As used in this application, the singular forms "a", "an" and "the" are intended to include the plural forms as well, unless the context clearly indicates otherwise. It should be appreciated that the terms "first," "second," and the like, as used in this specification do not denote any order, quantity, or importance, but rather are used to distinguish one element from another. Likewise, the terms "a" or "an" and the like do not denote a limitation of quantity, but rather denote the presence of at least one; "plurality" means two and more than two. Unless otherwise indicated, the terms "front," "rear," "lower," and/or "upper" and the like are merely for convenience of description and are not limited to one location or one spatial orientation. The word "comprising" or "comprises", and the like, means that elements or items appearing before "comprising" or "comprising" are encompassed by the element or item recited after "comprising" or "comprising" and equivalents thereof, and that other elements or items are not excluded. It should also be understood that the use of "a number" in the present specification means an indefinite number.

The present application will be described in detail with reference to the drawings and the preferred embodiments, and the following embodiments and features of the embodiments may be mutually complemented or combined without conflict.

Fig. 1 schematically illustrates a schematic front view of an electronic device according to an embodiment of the present utility model, and fig. 2 schematically illustrates an internal structure of an electronic device according to an embodiment of the present utility model.

As shown in fig. 1 to 2, anelectronic device 10 according to an embodiment of the present utility model includes awork head 21 and abody 22. The workinghead 21 is provided at one end of thebody 22. The outer surface (including the end and/or side surfaces) of the workinghead 21 is in direct contact with the target area. The workinghead 21 is provided with an electrode assembly for outputting energy. The working head 31 may or may not rotate relative to thebody 22. The end face of the workinghead 21 is preferably not perpendicular to the axis of themachine body 22, forms a certain included angle, generally forms a 15-degree included angle, accords with the ergonomic design, and is more comfortable and convenient to use. Thebody 22 serves as a handle and as a core control portion of theelectronic device 10 to control the operating state of the entireelectronic device 10. Theelectronic device 10 of the present embodiment may be used as a portable beauty instrument.

As shown in fig. 5, theelectronic device 10 further comprises input means 11, power supply means 12, energy switching means 13 and energy output means 14, preferably further comprises detection means 15. In one embodiment, theenergy switching device 13 is configured to output a square wave with a fixed duty ratio, so as to serve as a signal source of theenergy output device 14, and theenergy switching device 13 preferably employs a microcomputer. Theenergy switching device 13 is connected to theinput device 11, thepower supply device 12, and theenergy output device 14, respectively. Preferably, the energy switching means 13 is also connected to the detection means 15. The detection means 15 are also connected to the energy output means 14 and the power supply means 12. Thepower supply device 12 serves as a power supply portion of the entireelectronic apparatus 10, and can supply power to theinput device 11, theenergy switching device 13, and theenergy output device 14. Preferably, thepower supply device 12 also supplies power to thedetection device 15.

Theinput device 11 is an interface of theelectronic apparatus 10 for communicating with a user, and is configured to generate input information according to an instruction input by the user. Theinput device 11 may be a variety of suitable input interfaces such as a key, a touch screen, etc. The input information may include input information corresponding to an operating mode of theelectronic device 10 and/or input information corresponding to a gear in the operating mode.

Theelectronic device 10 has a radio frequency microcurrent mode of operation and an electroporation iontophoresis mode of operation, and preferably also has a skin detection mode of operation and a refrigeration mode of operation. When theelectronic device 10 is used, the corresponding operation mode can be selected through theinput device 11, so that theelectronic device 10 starts the corresponding operation mode according to the command input by the outside. For example, theelectronic device 10 may choose to output different energy intensities (e.g., output power) for different skin conditions, including normal skin, sensitive skin, and resistant skin, may output different energy intensities for different skin portions, may choose to output low power for periocular skin, and may choose to output high power for facial skin.

As shown in fig. 2 and 3b, theenergy output device 14 includes at least oneelectrode assembly 145 disposed on the workinghead 21. Theelectrode assembly 145 includes two electrodes, typically two electrode pads of opposite polarity. In this embodiment, there are at least twoelectrode assemblies 145, and eachelectrode assembly 145 is composed of two electrode sheets having opposite polarities. The electrodes are arranged in an insulating way, so that mutual conduction is avoided.

Theelectronic device 10 is configured such that the energy switching means 13 is arranged to enable the energy output means 14 to selectively activate one of the radio frequency microcurrent mode of operation and the electroporation iontophoresis mode of operation, based on the input information generated by the input means 11. In the rf micro-current mode of operation, theenergy output device 14 alternately outputs rf and micro-current through thesame electrode assembly 145; in the electroporation iontophoresis mode of operation, theenergy output device 14 alternately outputs electroporation pulses and iontophoresis currents through thesame electrode assembly 145. Wherein the outputs of the rf, microcurrent, electroporation pulses and iontophoresis current share thesame electrode assembly 145. Theenergy output device 14 may share oneelectrode assembly 145 to alternately output the energy, or may share a plurality ofelectrode assemblies 145, and eachelectrode assembly 145 of the plurality ofelectrode assemblies 145 may alternately output the energy. By the arrangement, theelectrode assemblies 145 with different energy outputs are prevented from being configured, so that the structure is simplified, the hand-held mode is not required to be replaced when the function is switched, the convenience of using the electronic equipment is improved, and meanwhile, the electronic equipment is beneficial to fully exerting the effects of the electronic equipment. It should be noted that, the radio frequency and the micro-current are used in combination, and the alternating synergistic effect of the radio frequency and the micro-current makes the skin lifting effect better, and the electroporation pulse and the ion introduction are also used in combination, and the two are used as another group of energy to be used in combination, so as to achieve the effect of promoting the penetration of the skin care product effect and remarkably improve the skin state.

Theelectronic device 10 provided by the utility model can be suitable for various skin parts, such as parts aiming at mandible, apple muscle, eye periphery, forehead and the like.

It should be noted that, even though the existing rf beauty instrument has two functions of rf and micro-current, the rf and micro-current are used as two independent functions, the two energies do not cooperate alternately, and the rf and micro-current are output by different electrode assemblies respectively. When the device is arranged in such a way, a user needs to turn over the instrument when switching functions, so that the device is very inconvenient to use, and the radiofrequency and the micro-current independently act, so that the skin is difficult to lift and tighten, and a better treatment effect is achieved. Theelectronic device 10 provided by the utility model does not use the radio frequency and the micro-current as two independent functions, realizes the alternate coordination of the radio frequency and the micro-current, and plays a better treatment effect, when in treatment, the radio frequency current output by theelectronic device 10 heats the skin of the dermis layer, so that collagen is shrunk and denatured and a back transport wound reaction is generated, and meanwhile, the output micro-current promotes the generation of ATP (adenosine phosphate, energy substances required by the generation of collagen and elastin), thereby accelerating the repair of the callus after the dermis is heated by the radio frequency, promoting the synthesis of the collagen and elastin, and achieving the remarkable effects of reducing fine wrinkles, improving the skin roughness and improving the density of the collagen.

The frequency of the alternating output of the radio frequency and the micro current is not particularly required, and the frequency of the alternating output of the electroporation and the ion introduction is not limited. If in the radio frequency micro-current working mode, after the radio frequency output is 10s, the micro-current output is 5s, then the radio frequency output is 10s, and the micro-current output is 5s, so that the radio frequency and the micro-current are alternately and circularly output. However, the interval between the alternating output of the rf and the micro-current is only illustrative, and is not limiting to the present utility model, and in general, the rf output time is longer than the micro-current output time, so that the combined use of the two methods is good. If in the electroporation iontophoresis operation mode, the electroporation pulse is output for 10s, then the iontophoresis pulse is output for 10s, and the iontophoresis pulse is output for 20s, so that the electroporation pulse and the iontophoresis current are output in an alternating cycle. However, the interval between the output of the electroporation pulse and the output of the ion guide is merely illustrative, and the present utility model is not limited thereto, and in general, the output time of the electroporation pulse is smaller than the output time of the ion guide, and the combination of the two is effective.

The number ofelectrode assemblies 145 is preferably a plurality, such as 2 or more than 2, and all of theelectrode assemblies 145 are disposed on the workinghead 21. In some embodiments, at least twoelectrode assemblies 145 are different in size in order to output different energy intensities. And/or, in some embodiments, the positions of at least twoelectrode assemblies 145 are asymmetric in order to treat different target areas withdifferent electrode assemblies 145, ensuring a use effect. Thus, a small electrode output energy may be used for thinner skin and a large electrode output energy may be used for thicker skin.

Twoelectrode assemblies 145 are illustrated, and as shown in fig. 2 and 3b, the twoelectrode assemblies 145 are afirst electrode assembly 1451 and asecond electrode assembly 1452, respectively. In the illustrated embodiment, the electrode size in thefirst electrode assembly 1451 is larger than the electrode size in thesecond electrode assembly 1452, i.e., thefirst electrode assembly 1451 employs a large electrode and thesecond electrode assembly 1452 employs a small electrode. The large electrode is used for a target area of thicker skin, such as the face, and the small electrode is used for a target area of thinner skin, such as the periocular skin. Preferably, the positions of thefirst electrode assembly 1451 and thesecond electrode assembly 1452 are asymmetric, such as thefirst electrode assembly 1451 is disposed on the end surface of the workinghead 21, and thesecond electrode assembly 1452 is disposed on the side surface of the workinghead 21, so that it is convenient to use different electrode assemblies for treatment of different target areas. Typically,electrode assemblies 145 of different sizes and/or asymmetric positions are not used at the same time. Thefirst electrode assembly 1451 and thesecond electrode assembly 1452 may be various numbers, e.g., the number of thefirst electrode assembly 1451 may be 2 to 4, and the number of thesecond electrode assembly 1452 may be 1 to 2.

It should be noted that, the conventional rf cosmetic apparatus adopts one or more pairs of positive and negative electrodes, and the electrodes have the same size and symmetrical positions, and as the body contact electrode, such electrodes are generally suitable for being applied to relatively flat skin such as cheek, but are not convenient for close fitting around eyes, which may affect the use effect, and may not be in contact with relatively uneven skin such as nose wings. The utility model provideselectrode assemblies 145 of different sizes and/or positions for application to different skin surfaces to accommodate treatment of different target areas, increase the treatment area, and ensure the use effect and safety.

As shown in fig. 3b, in one embodiment, thefirst electrode assembly 1451 includes two concentric ring electrodes, i.e., electrode plates with double ring electrodes and opposite polarity, preferably circular ring electrodes. Two ring-shaped electrodes are provided on the end face of the workinghead 21. Preferably, the width of each annular electrode is 3 mm-5 mm, the distance between the two annular electrodes is 3.5 mm-4.5 mm, the distance can assist the radio frequency energy to reach the position of 2 mm-3 mm under the skin, and the device can cover the skin parts such as flat cheeks, and has large coverage area and high output energy.

As shown in fig. 3b, in one embodiment, thesecond electrode assembly 1452 includes two L-shaped electrodes having arcuate outer surfaces, the polarities of the two L-shaped electrodes being opposite. Preferably, the radius of the arc-face fillet of each L-shaped electrode is larger than 2.5mm, the distance between the two L-shaped electrodes is 3 mm-6 mm, and the L-shaped electrodes are arranged at the edge of the working head 1. The arrangement of the L-shaped electrode enables the electrode in thesecond electrode assembly 1452 to extend from the horizontal direction to the vertical direction, so that the electrode can be well contacted with skin by being held and slid at will during use, and can be tightly attached during use on the other hand when the electrode is applied to uneven nose wings and other parts. Preferably, thefirst electrode assembly 1451 and thesecond electrode assembly 1452 are integrally formed through an in-mold injection molding process, guaranteeing waterproof performance of theelectronic apparatus 10.

The frequency of the alternate output of the rf and the micro-current and the frequency of the alternate output of the electroporation pulse and the iontophoresis current may be preset in theenergy switching device 13, or may be set by the user himself, and the alternate output frequency may be fixed or adjustable.

In a preferred embodiment, the detection means 15 are used to obtain the output information of the energy output means 14. Thedetection device 15 may continuously detect the output information of theenergy output device 14 in real time, or may intermittently detect the output information of theenergy output device 14. The output information may be any output value that reflects the current output state of theenergy output device 14. The output value may be any one of voltage, temperature, current, and the like. For the radio frequency output, the detection means 15 mainly detect the skin surface temperature, and if it is detected that the skin surface temperature exceeds the limit temperature that the skin can withstand (limit temperature is typically 43 ℃), corresponding safety treatment measures are required. For microcurrent, electroporation and iontophoresis output, thedetection device 15 detects mainly the current, and if the detected current exceeds a safety threshold, corresponding safety treatment measures are taken. The safety treatment measure can be to reduce the pressure output or stop the output, so as to reduce the risk of scalding, pain and even muscle injury of the user. The safety treatment measures can also be voice prompts, lamplight prompts and the like.

In a preferred embodiment, theenergy switching device 13 is configured to obtain a system safety result regarding the output state of theenergy output device 11 according to the output information obtained by the detectingdevice 15, and generate a corresponding safety processing measure according to the system safety result and a preset safety policy. Preferably, theenergy switching device 13 is configured to obtain an output value in the output information, and compare the output value with a safety threshold; if the comparison result is that the output value exceeds the safety threshold, theenergy switching device 13 obtains a system safety result that theenergy output device 14 is in abnormal output, and generates a safety processing measure for controlling thepower supply device 12 to step down the output or stop the output in combination with a preset safety policy. At this time, the output of any energy is monitored, so that the output of each energy becomes safe and controllable, thereby improving the use safety of theelectronic device 10.

As shown in fig. 6, in addition to theelectrode assembly 145, in one embodiment, theenergy output device 14 includes a relay device 141, a radiofrequency generation device 142, a microcurrentiontophoresis generation device 143, and anelectroporation generation device 144. The relay device 141 is connected to theenergy switching device 13. Theenergy switching device 13 is used to selectively switch on the relay device 141 to one of the radiofrequency generation device 142, the microcurrentiontophoresis generation device 143 and theelectroporation generation device 144. At least oneelectrode assembly 145 is connected to aradio frequency generator 142, amicrocurrent iontophoresis generator 143, and anelectroporation generator 144. In one embodiment, the outputs of therf generator 142, themicrocurrent iontophoresis generator 143, and theelectroporation generator 144 are selectively coupled to one of thefirst electrode assembly 1451 and thesecond electrode assembly 1452. The radiofrequency generating device 142 is configured to output radio frequencies. The microcurrentiontophoresis generating device 143 is configured to output a pulse current corresponding to the microcurrent and also configured to generate an iontophoresis current.Electroporation generating apparatus 144 is configured to output electroporation pulses. Therefore, the output of the iontophoresis current and the output of the microcurrent share the same microcurrentiontophoresis generating device 143, thereby further simplifying the structure and simplifying the hardware design.

In one embodiment, when therf generator 142 is turned on thefirst electrode assembly 1451, which is relatively large in size, a high frequency output, preferably 2MHz to 4MHz rf, may be used, and in this case, rf energy may be allowed to reach the dermis layer of 2mm to 3mm for a target area (e.g., the face) where the skin is relatively thick.

In one embodiment, when the RF generating means 142 is turned on thesecond electrode assembly 1452, which is smaller in size, a low frequency output, preferably outputting an RF of 1MHz to 2MHz, may be used, at which time RF energy may be allowed to reach a subcutaneous depth for a target area (e.g., the periocular region) where the skin is thinner.

Therefore, theelectronic device 10 of the present utility model can output different intensities of radio frequencies by selecting different sizes ofelectrode assemblies 145 according to different target areas, thereby increasing the safety and effectiveness of use.

As shown in fig. 7, in one embodiment, the relay device 141 includes two relays, afirst relay 1411 and asecond relay 1412, respectively. Thefirst relay 1411 is selectively connected to one of therf generator 142 and themicrocurrent iontophoresis generator 143. Thesecond relay 1412 is selectively connected to one of the microcurrentiontophoresis generating device 143 and theelectroporation generating device 144. Both relays are connected to theenergy switching device 13 such that thefirst relay 1411 is selectively connected to one of therf generator 142 and themicro-current iontophoresis generator 143 under the control of theenergy switching device 13 and thesecond relay 1412 is selectively connected to one of themicro-current iontophoresis generator 143 and theelectroporation generator 144 under the control of theenergy switching device 13. When the user selects the operation mode, if the radio frequency micro-current operation mode is selected, thefirst relay 1411 switches the radio frequency and micro-current alternate output under the control of theenergy switching device 13, and if the electroporation iontophoresis operation mode is selected, thesecond relay 1412 switches the electroporation and iontophoresis alternate output under the control of theenergy switching device 13. In other embodiments of the present application, the relay 141 may also be implemented using a single relay.

Next, the operation of theelectronic device 10 will be further described using thefirst electrode assembly 1451 as a large electrode and thesecond electrode assembly 1452 as a small electrode.

In one embodiment, the rf micro-current operation mode includes a first operation mode corresponding to thefirst electrode assembly 1451 and a second operation mode corresponding to thesecond electrode assembly 1452.

In the first working mode of the radio frequency microcurrent, the radiofrequency generating device 142 is used for outputting radio frequency of 2 MHz-4 MHz, the microcurrentiontophoresis generating device 143 is used for outputting microcurrent of 335 mu A-500 mu A, at this time, the combined application effect of the radio frequency technology and the microcurrent technology is better for the target area with thicker skin, and the safety is also considered. It should be understood that when the output of the radio frequency is limited to 2MHz to 4MHz, the radio frequency energy is ensured to reach the depth of the skin, and the use safety is ensured. It should be appreciated that the rf frequency affects the depth of rf energy reaching the skin, and that 2MHz to 4MHz is a safe energy range that theelectronic device 10 of the present utility model can accept to act on thicker skin such as the face. When the micro-current output is limited to 335-500 muA, the stimulation and damage of the skin caused by the larger current can be avoided, because the larger current can act as a reaction to stimulate facial nerves, resulting in muscle damage. Further, experiments prove that the combined use of micro-current of 335 mu A-500 mu A and radio frequency of 2 MHz-4 MHz can also have better treatment effect, and has outstanding effect of pulling skin of thicker skin areas such as face. Compared with the prior art, theelectronic device 10 provided by the utility model can generate radio frequency with higher frequency, and actually output heat energy can reach the depth of the dermis layer so as to ensure the use efficacy.

In the second working mode of the radio frequency microcurrent, the radiofrequency generating device 142 is used for outputting radio frequency of 1 MHz-2 MHz, the microcurrentiontophoresis generating device 143 is used for outputting microcurrent of 335 mu A-500 mu A, at this time, the combined application effect of the radio frequency and microcurrent technology is better aiming at the target area with thinner skin, and the safety is also ensured. It should be understood that 1MHz to 2MHz is a safe energy range that theelectronic device 10 can accept when acting on thinner skin such as the eye periphery, so that when the output of the radio frequency is limited to 1MHz to 2MHz, the depth of the radio frequency energy reaching the skin is ensured, and the use safety is ensured. Similarly, experiments prove that the combined use of micro-current of 335 mu A-500 mu A and radio frequency of 1 MHz-2 MHz can achieve better treatment effect, and has outstanding effect of pulling skin in thinner skin areas such as periocular skin.

It should also be appreciated that conventional rf beauty instruments do not distinguish between periocular and facial energy, for example, for periocular applications, and also employ high rf output, resulting in damage to periocular skin. The utility model sets different energy intensity for different target areas, effectively ensures the use safety and reduces the danger coefficient during use.

In an embodiment, the electroporation iontophoresis operation mode may include only a first operation mode corresponding to thefirst electrode assembly 1451, and no second operation mode corresponding to thesecond electrode assembly 1452. In other embodiments, the electroporation iontophoresis mode includes a first mode of operation corresponding to thefirst electrode assembly 1451 and a second mode of operation corresponding to thesecond electrode assembly 1452.

In the first mode of electroporation iontophoresis,electroporation generator 144 is used to output electroporation pulses with a voltage of 40V to 60V, PWM, a pulse width of 10ms to 20ms and a pulse frequency of 20pps to 30pps, andmicrocurrent iontophoresis generator 143 is used to output a current density of 200. Mu.A/cm² ～500μA/cm² Is introduced into the current. The first mode of operation of electroporation iontophoresis is mainly directed to a target region of thicker skin, and from the viewpoint of safety, user experience and skin tolerance, the voltage of electroporation pulses is set to 40V to 60V, the pulse width is 10ms to 20ms and the pulse frequency is 20pps to 30pps, and the iontophoresis current density is set to 200. Mu.A/cm² ～500μA/cm² And experiments prove that the combined use of electroporation and iontophoresis under these specific parameters is aimed at thicker parts of the skin The penetration and absorption of the functional components in the skin care product can be effectively promoted, and the use effect is good.

In the second mode of electroporation iontophoresis,electroporation generating apparatus 144 is used for outputting electroporation pulse current with a voltage of 10V-20V, PWM for regulating pulse width of 5 ms-10 ms and pulse frequency of 10 pps-20 pps, and microcurrentiontophoresis generating apparatus 143 is used for outputting current with a density of 100 μA/cm² ～200μA/cm² Is introduced into the current. The second mode of operation of electroporation iontophoresis is mainly directed to a target region of thinner skin, and also from the viewpoints of safety, user experience and skin tolerance, the voltage of electroporation pulse is set to 10V-20V, pulse width is 5 ms-10 ms and pulse frequency is 10 pps-20 pps, and iontophoresis current density is set to 100. Mu.A/cm² ～200μA/cm² Experiments prove that the combined use of electroporation and iontophoresis under the specific parameters can effectively promote the penetration and absorption of the functional components in the skin care product aiming at the thinner parts of the skin, and has good use effect.

Therefore, the two working modes of electroporation iontophoresis solve the problem of treatment of different skin parts, so that the electroporation iontophoresis is more flexible to use, the safety and the effectiveness are improved, and the user experience is improved.

Further, after theelectronic device 10 is turned on, theenergy output device 14 can be started only after the workinghead 21 contacts the skin, that is, only the electrode on the workinghead 21 contacts the skin, so that theelectronic device 10 can output energy, which not only saves electricity, but also has good safety.

In one embodiment, after theelectronic device 10 is turned on, the detectingdevice 15 automatically detects a load resistance value (i.e. skin impedance) of the target object (skin), and sends the detected load resistance value to theenergy switching device 13. Theenergy switching device 13 determines whether to activate theenergy output device 14 according to the detected load resistance value. Theenergy switching device 13 compares the load resistance with a preset resistance, and when the load resistance and the preset resistance are the same, theenergy switching device 13 controls the relay device 141 to switch on theenergy output device 14. Therefore, theelectronic device 10 also has a power-on detection function, after theelectronic device 10 is powered on, the detection means 15 automatically acquires skin impedance first, and the energy switching means 13 compares the skin impedance with a preset load resistance value, and acquires a system security result regarding the contact state of theelectronic device 10, if the system security result regarding the contact state of the electronic device is that thework head 21 is not currently contacting the skin, according to a preset security policy, the security processing means for locking the energy output means 14 is performed, no energy is output, and if the system security result regarding the contact state of the electronic device is that thework head 21 is currently contacting the skin, the security processing means for starting the energy output means 14 is performed according to the preset security policy.

As shown in fig. 8, in one embodiment, thepower supply device 12 includes abattery 121 for storing electrical energy, which may be charged. Thebattery 121 is typically a lithium battery. Since the maximum voltage output by a lithium battery typically does not exceed 4.2V, the voltage output by a lithium battery requires a buck or boost process in order to meet different power supply requirements. For this reason, in an embodiment, thepower supply device 12 further includes avoltage regulator 122 for regulating the voltage output from thebattery 121 to increase the voltage output from thebattery 121 or decrease the voltage output from thebattery 121.

In one embodiment, thevoltage regulator 122 is capable of regulating the voltage output by thebattery 121 to 5.5V-18V (preferably 13.3V) and supplying power to theenergy output device 14.

In one embodiment, thevoltage regulator 122 is also capable of regulating the voltage output by thebattery 121 to 3.3V-5V (preferably 3.3V) and supplying power to an MCU (micro control unit) in theenergy switching device 13. The MCU in theenergy switching device 13 can control the relay.

In one embodiment, thevoltage regulator 122 is also capable of regulating the voltage output by thebattery 121 to 3V-12V (preferably 5V) and powering the relay.

In one embodiment, thevoltage regulator 122 includes a boost component and a buck component. The boosting means is for boosting the voltage output from thebattery 121. The boost component may be selected to be a DC-DC boost chip. The step-down part serves to reduce the voltage output from thebattery 121. The step-down component may be an LDO step-down chip.

The kind of theenergy switching device 13 is not particularly limited in this embodiment, and may be hardware for performing a logic operation, for example, a single chip microcomputer, a microprocessor, a programmable logic controller (PLC, programmable Logic Controller) or a Field programmable gate array (FPGA, field-Programmable Gate Array), or a software program, a function module, a function, a target library (Object Libraries) or a Dynamic-Link library (Dynamic-Link Libraries) for implementing the above functions on a hardware basis. Moreover, the person skilled in the art can understand how theenergy switching device 13 controls the switching process of the relay device 141 according to the prior art, and can understand how theenergy switching device 13 communicates with other devices (such as the detectingdevice 14, theLED lighting device 23, the refrigeratingdevice 24, theskin detecting device 25, thedisplay device 26, and the sound prompting device 27) according to the prior art. The kind of the detectingdevice 15 is also not particularly limited in this embodiment, such as: temperature sensors, current sensors, voltage sensors, etc. The detection means 15 typically comprise a variety of sensors to detect different data.

As shown in fig. 8, in one embodiment, therf generating device 142 includes anrf generating component 1421 and atransformer 1422. The radiofrequency generating component 1421 is configured to directly energize thefirst relay 1411. An output of therf generating part 1421 is connected to atransformer 1422, and an output of thetransformer 1422 is directly connected to theelectrode assembly 145.

When thefirst relay 1411 is turned on to therf generating part 1421, therf generating part 1421 converts the square wave output from theenergy switching device 13 into a sine wave and outputs the sine wave to thetransformer 1422, thetransformer 1422 amplifies and boosts the sine wave and outputs the sine wave as an rf signal to theelectrode assembly 145, and finally the energy output from theelectrode assembly 145 acts on the target area. In the embodiment of the application, thetransformer 1422 can amplify and boost the sine wave output by the radiofrequency generating component 1421 to different voltages so as to meet different requirements. Alternatively, thetransformer 1422 can amplify the sine wave to 50V-120V. Here, the person skilled in the art can set the rf voltage according to the need, but is not limited to 50V to 120V as exemplified herein, and it is understood that the higher the rf voltage, the higher the rf energy. In practice, the radio frequency voltage is set to not more than 120V in view of safety.

The manner in which the radiofrequency generating component 1421 converts the square wave to a sine wave is not limited in this application, as should be understood by those skilled in the art in view of the present disclosure. Therf generating part 1421 is preferably capable of outputting a sine wave of an rf frequency of 1MHz to 4MHz in order to achieve a high frequency output. For example, in one embodiment, therf generating component 1421 uses a GaN MOS driver chip to adjust the rf frequency to 1 MHz-4 MHz, and may adjust the rf to a sine wave through an adaptive circuit. The GaN MOS driving chip provided by the utility model can realize high-frequency output, and has the advantages of high energy conversion efficiency, low heating value and small waveform distortion. Specifically, therf generating part 1421 of the present utility model may output a sine wave as shown in fig. 9 after using a GaN MOS driving chip. The higher the radio frequency voltage is, the higher the energy intensity of the radio frequency is, and the radio frequency voltage is controlled to be not more than 120V, namely-60V to +60V in consideration of safety. And it can be seen that the waveform shown in fig. 9 has a small overall distortion, realizes stable output, and has high energy conversion efficiency.

When the first relay 141 is turned on with the micro-currentiontophoresis generating device 143, the micro-currentiontophoresis generating device 143 converts the square wave signal outputted from theenergy switching device 13 into a pulse signal corresponding to the micro-current and outputs the pulse signal to theelectrode assembly 145, and the energy outputted from theelectrode assembly 145 acts on the target region.

Preferably, in the rf micro-current operation mode, theelectronic device 10 has a plurality of gear positions, each of the gear positions corresponds to an output state reflecting the rf micro-current output information, all of the gear positions reflect different output states, the rf current in all of the output states is kept constant, and the rf voltage and the micro-current in different of the output states are different. And/or, in the electroporation iontophoresis operation mode, theelectronic device 10 also has a plurality of gear positions, each of the gear positions corresponds to an output state reflecting electroporation iontophoresis output information, all of the output states reflected by the gear positions are different, and at least one of pulse width, frequency, voltage and current intensity of the electroporation pulse is different in different output states. Therefore, the output with different intensities can be realized according to the settings of different gears, and the use is more flexible and convenient.

In an exemplary embodiment, theinput device 11 includes a plurality of keys for receiving input information to control the power-on of theelectronic device 10, the selection of an operation mode, the selection of different gear positions, the selection of an auxiliary function mode, and the like. The present application is not limited to a specific number of keys, and may be 2, 3 or more, preferably 3 keys.

As shown in fig. 1 and 3a, in one embodiment, theinput device 11 includes afirst key 111, asecond key 112, and athird key 113, which are disposed on thebody 22 and can be directly pressed or touched by a user. Thefirst key 111 is used for power-on control, and is also used for selectively generating input information corresponding to one of a radio frequency micro-current operation mode and an electroporation iontophoresis operation mode. Thesecond key 112 is used to generate gear information corresponding to the input information after thefirst key 111 generates the input information, the gear information reflecting the output state of theenergy output device 14. Thethird key 113 is used for generating input information corresponding to an auxiliary function mode, such as input information reflecting an auxiliary function mode of skin detection, ice compress refrigeration, and the like. If thefirst key 111 is pressed for a long time, theelectronic device 10 is controlled to start up, so that theelectronic device 10 is in a standby mode. Thefirst key 111 is pressed short, so that the working mode can be selected, and thefirst key 111 is pressed short in sequence to switch different working modes. Thesecond key 112 is pressed short, and the gear can be selected, and thesecond key 112 is pressed short in sequence to switch different gears. Short presses of the third key 113 enter auxiliary function modes such as skin detection mode, ice pack cooling mode.

In one embodiment, thefirst key 111 may generate a first input information corresponding to a first operation mode of the rf micro-current, a second input information corresponding to a second operation mode of the rf micro-current, and a third input information corresponding to an electroporation iontophoresis mode. The first input information is a first function, the second input information is a second function, and the third input information is a third function.

If thefirst key 111 is pressed briefly, a first function is selected, and the first function is a first operation mode of radio frequency micro-current. When the first function is selected, thefirst electrode assembly 1451 turns on therf generating device 142 and the micro-currentiontophoresis generating device 143. When thefirst electrode assembly 1451 is attached to the skin, theRF generator 142 outputs RF of 2MHz to 4MHz, and themicrocurrent iontophoresis generator 143 outputs microcurrent of 335 μA to 500 μA. Alternatively, thefirst relay 1411 is controlled by theenergy switching device 13 to make therf generating device 142 output for 10s and the micro-currentiontophoresis generating device 143 output for 5s, at which frequency the micro-current iontophoresis generating device outputs alternately. Alternatively, in the first operation mode of the rf micro-current, therf generating part 1421 outputs a sine wave (rf) of 2MHz to 4MHz to thetransformer 1422, and thetransformer 1422 amplifies the sine wave to 90V to 110V and outputs the amplified sine wave to thefirst electrode assembly 1451.

If thefirst key 111 is pressed for a short time, the operation is switched to a second function, and the second function is a second operation mode of radio frequency micro-current. When the second function is selected, thesecond electrode assembly 1452 turns on therf generating device 142 and the micro currentiontophoresis generating device 143. When thesecond electrode assembly 1452 is attached to the skin, theRF generator 142 outputs an RF of 1MHz to 2MHz (preferably 1 MHz), and themicrocurrent iontophoresis generator 143 outputs a microcurrent of 335 μA to 500 μA (preferably 335 μA). Alternatively, thefirst relay 1411 is controlled by theenergy switching device 13 to make therf generating device 142 output for 5s and the micro-currentiontophoresis generating device 143 output for 2s, at which frequency the micro-current iontophoresis generating device outputs alternately. Alternatively, in the second operation mode of the rf micro-current, therf generating part 1421 outputs a sine wave of 1MHz to 2MHz to thetransformer 1422, and thetransformer 1422 amplifies the sine wave to 40V to 60V (preferably 50V) and outputs the amplified sine wave to thesecond electrode assembly 1452. At this time, the power and current are reduced for the thin part of the epidermis, and skin damage is avoided. It will be appreciated that the rf current is constant and that varying the rf frequency and rf voltage achieves different intensities of output.

Three gear positions are shown schematically, see fig. 18. When the first function is selected, the first gear of the first operation mode of the rf micro-current is turned on by default, and in the first gear, after thefirst electrode assembly 1451 is attached to the skin, therf generating part 1421 outputs a sine wave of 2MHz to 4MHz to thetransformer 1422, thetransformer 1422 amplifies and boosts the sine wave to 90V, and after switching to the micro-current, the micro-currentiontophoresis generating device 143 outputs a micro-current of 355 μa. If thesecond key 112 is pressed for a short time, the second gear of the first operation mode of the rf micro-current is turned on, in the second gear, therf generating unit 1421 outputs a sine wave of 2MHz to 4MHz to thetransformer 1422, thetransformer 1422 amplifies and boosts the sine wave to 100V, and after switching to the micro-current, the micro-currentiontophoresis generating device 143 outputs a micro-current of 425 μa. If thesecond key 112 is pressed for a short time, the third gear of the first operation mode of the rf micro-current is turned on, in the third gear, therf generating unit 1421 outputs a sine wave of 2MHz to 4MHz to thetransformer 1422, thetransformer 1422 amplifies and boosts the sine wave to 110V, and after switching to the micro-current, the micro-currentiontophoresis generating device 143 outputs a micro-current of 500 μa.

In the output state shown in fig. 18, the rf current remains constant, and the rf frequency and the micro-current are different in different output states. In the rf micro-current mode of operation, one skilled in the art can set a number of different output states as desired and should not be limited to the situation illustrated in fig. 18. When the radio frequency current is constant, the radio frequency output power is different due to the fact that the radio frequency voltage is different, and when the radio frequency current is sequentially switched from the first gear to the third gear, the output power is gradually increased, and the heating efficiency acting on the skin is higher. Aiming at micro-current, when different gears are switched, the output power is also changed, so that the ions under the action of the micro-current can deeply penetrate into the skin to reach the dermis, promote the metabolism of cells and synthesize collagen.

The embodiment of the present application further provides a control method of an electronic device, which is used for controlling theelectronic device 10 of the present embodiment, where the control method includes: theenergy output device 14 determines to start a radio frequency micro-current working mode according to the input information of theinput device 11, and after the radio frequency micro-current working mode is started, theenergy output device 14 alternately outputs radio frequency and micro-current at a specific frequency according to the received square wave signal; alternatively, theenergy output device 14 determines the electroporation iontophoresis operation mode according to the input information of theinput device 11, and after the electroporation iontophoresis operation mode is started, theenergy output device 14 alternately outputs electroporation pulses and iontophoresis currents at a specific frequency according to the received square wave signal.

Referring to fig. 10, as an embodiment, when the control method is executed, the control of the rf micro-current includes the following steps:

step S301: receiving the input information generated by theinput device 11, theenergy switching device 13 outputs a square wave signal with a fixed duty ratio according to the input information; specifically, theenergy switching device 13 outputs a square wave with a fixed duty ratio through a PWM adjusting function of an MCU (micro control unit);

step S302: theenergy output device 14 alternately outputs radio frequency and micro current at a specific frequency according to control information of the corresponding square wave signal generated by theenergy switching device 13;

step S303: thedetection device 15 acquires output information of theenergy output device 14; the output information comprises radio frequency output information and micro-current output information;

step S304: theenergy switching device 13 obtains a system safety result about the output state of theenergy output device 14 according to the output information of theenergy output device 14, and generates a corresponding safety processing measure according to the system safety result and a preset safety policy.

As an embodiment, as shown in fig. 11, step S304 includes the following steps:

step S3041: theenergy switching device 13 acquires an output value in the output information and compares the output value with a safety threshold;

Step S3042: if the comparison result is that the output value does not exceed the safety threshold, thepower supply device 12 maintains the current voltage and continues to alternately output the radio frequency and the micro current;

step S3043: if the comparison result is that the output value exceeds the safety threshold, thepower supply device 12 steps down or stops outputting.

Preferably, after the radio frequency micro-current operation mode is started, before alternately outputting radio frequency and micro-current, the control method further includes: theenergy output device 14 determines a first working mode for starting the radio frequency micro-current working mode according to the input information; theenergy output device 14 alternately outputs a radio frequency of 2MHz to 4MHz and a micro current of 335 mua to 500 mua in the first operation mode; alternatively, theenergy output device 14 determines a second operating mode for starting the rf micro-current operating mode according to the input information; theenergy output device 14 alternately outputs a radio frequency of 1MHz to 2MHz and a micro current of 335 mua to 500 mua in the second operation mode.

Preferably, after the radio frequency micro-current operation mode is started, before alternately outputting radio frequency and micro-current, the control method further includes: theenergy output device 14 determines the current output gear according to the input information; theenergy output device 14 alternately outputs radio frequency and micro current under the output condition determined by the current output gear; the output conditions include radio frequency voltage, radio frequency current, radio frequency and micro current.

Preferably, after the rf micro-current operation mode is started, therf generating device 142 adjusts the square wave corresponding to the square wave signal to an rf (sine wave) output with an rf frequency of 1MHz to 4MHz after receiving the square wave signal, and the micro-currentiontophoresis generating device 143 adjusts the square wave corresponding to the square wave signal to a pulse output with a micro-current of 335 μa to 500 μa. Therefore, when the radio frequency is output, the radio frequency is low-power high-frequency output, so that the problem that high heat stays on the surface layer and cannot quickly reach the connective tissue of the dermis layer is solved; when the microcurrent is output, the output value of the microcurrent is controlled to be 335 mu A-500 mu A, and when the collagen is promoted to be generated, the excessive contraction leads to the relaxation of the fiber damaged muscle, the water content and the conductivity of fascia are improved, and the metabolism is promoted.

As shown in fig. 12, in one embodiment, the microcurrentiontophoresis generating device 143 includes a microcurrentiontophoresis generating component 1431 and acurrent adjusting component 1432. The microcurrentiontophoresis generating part 1431 is used to directly turn on thesecond relay 1411 or thefirst relay 1412. The output end of the microcurrentiontophoresis generating component 1431 is connected with acurrent regulating component 1432, and the output end of thecurrent regulating component 1432 is directly connected with theelectrode assembly 145.

When thefirst relay 1411 is turned on with the micro-currentiontophoresis generating part 1431, the micro-currentiontophoresis generating part 1431 receives the square wave signal outputted from theenergy switching device 13, and outputs a pulse corresponding to the micro-current after adjusting the current value. When thesecond relay 1412 is turned on with the micro-currentiontophoresis generating part 1431, the micro-currentiontophoresis generating part 1431 receives the square wave signal output from theenergy switching device 13, and further outputs the PWM square wave signal to thecurrent adjusting part 1432, and thecurrent adjusting part 1432 adjusts the current density of the PWM square wave signal and outputs it to theelectrode assembly 145. Thecurrent regulating member 1432 directly outputs a low-intensity constant current corresponding to the iontophoresis to theelectrode assembly 145 and acts on the skin.

As shown in FIG. 12, in one embodimentelectroporation generating apparatus 144 includes electroporationpulse generating component 1441 andvoltage regulating component 1442. Theelectroporation pulse generator 1441 is configured to directly communicate with thesecond relay 1412. The output end of the electroporationpulse generating component 1441 is connected to thevoltage adjusting component 1442, and the output end of thevoltage adjusting component 1442 is directly connected to theelectrode assembly 145. When thesecond relay 1412 turns on the electroporationpulse generation unit 1441, the electroporationpulse generation unit 1441 receives the square wave signal output from theenergy switching device 13, outputs an electroporation pulse (pulse bi-directional current wave), and adjusts the pulse width and frequency of the electroporation pulse by its own PWM and outputs it to thevoltage adjustment unit 1442. Thevoltage adjusting unit 1442 adjusts the voltage of the electroporation pulse, and outputs the voltage to theelectrode assembly 145, and acts on the skin. Thevoltage adjusting unit 1442 may output the required electroporation pulse voltage, so as to output different electroporation pulse voltages according to actual needs. The pulse width and frequency of the pulse bidirectional current can be set according to the bearable range of human skin.

Referring to fig. 13, in one embodiment, when the control method is performed, the control of the electroporation iontophoresis output includes the steps of:

step S601: receiving input information generated by theinput device 11, theenergy switching device 13 outputs a square wave signal with a fixed duty ratio according to the input information; specifically, theenergy switching device 13 outputs a square wave with a fixed duty ratio through the PWM adjusting function of the MCU;

step S602: theenergy output device 14 alternately outputs electroporation pulses and iontophoresis currents at a specific frequency according to control information corresponding to the square wave signal generated by theenergy switching device 13;

step S603: thedetection device 15 acquires output information of theenergy output device 14; the output information here includes electroporation output information and iontophoresis output information;

step S604: theenergy switching device 13 obtains a system safety result about the output state of theenergy output device 14 according to the output information of theenergy output device 14, and generates a corresponding safety processing measure according to the system safety result and a preset safety policy.

As an embodiment, as shown in fig. 14, step S604 includes the following steps:

step S6041: theenergy switching device 13 compares the output value corresponding to the output information with a safety threshold;

Step S6042: if the comparison result is that the output value does not exceed the safety threshold, thepower supply device 12 maintains the current voltage and continues to alternately output electroporation pulses and iontophoresis currents;

step S6043: if the comparison result is that the output value exceeds the safety threshold, thepower supply device 12 steps down or stops outputting.

In a specific embodiment, thedetection device 15 acquires the iontophoresis output current in real time and sends the iontophoresis output current to theenergy switching device 13, theenergy switching device 13 compares the output current with a safety threshold, and if the output current is greater than the safety threshold of 500 μΑ, theenergy switching device 13 controls thepower supply device 12 to stop outputting, so as to avoid discomfort and skin damage caused by overlarge current.

Preferably, after the electroporation iontophoresis operation mode is started, theelectroporation generating device 144 adjusts the square wave corresponding to the square wave signal to a voltage of 10V-60V, a pulse width of 5 ms-20 ms after receiving the square wave signalElectroporation output of the electric pulses with a frequency of 10pps to 30pps, and theiontophoresis generating device 143 adjusts the square wave corresponding to the square wave signal to a current density of 100 μA/cm² ～500μA/cm² Is used for ion-induced current output. At this time, in order to promote the penetration of the functional components in the skin care product, the electroporation technology and the ion introduction technology are combined to enable the electroporation pulse to be applied instantaneously, and a high-voltage electric field is applied on lipid bilayer molecular layers such as cell membranes to generate reversible temporary hydrophilic electric pore channels, so that the capability of molecules passing through the skin is improved, the ion introduction boosting can promote the penetration of the skin care product and the skin moisture more effectively, and the limitation of the ion introduction technology alone is avoided. Specifically, when electroporation and iontophoresis are alternately applied, an instantaneous high-voltage electric field is applied to lipid bilayer molecular layers such as cell membranes by electroporation pulses to generate reversible temporary hydrophilic electric pore channels, so that the capability of molecules passing through the skin is improved, and iontophoresis boosting can more effectively promote permeation of skin care products and skin moisturizing.

Further, after initiating the electroporation iontophoresis mode of operation, the method further comprises, prior to alternately outputting the electroporation pulse and iontophoresis: the energy output means 14 determines a first mode of operation for initiating the electroporation iontophoresis mode of operation based on the input information; theenergy output device 14 alternately outputs electroporation pulses with a voltage of 40V to 60V, a pulse width of 10ms to 20ms and a frequency of 20pps to 30pps, and a current density of 200 μA/cm in the first operation mode² ～500μA/cm² Is introduced into the current; alternatively, theenergy output device 14 determines a second mode of operation for initiating the electroporation iontophoresis mode of operation based on the input information; theenergy output device 14 alternately outputs electroporation pulses with a voltage of 10V-20V, a pulse width of 5 ms-10 ms and a frequency of 10 pps-20 pps and a current density of 100 μA/cm in the second operation mode² ～200μA/cm² Is introduced into the current.

Further, after the electroporation iontophoresis operation mode is started, the method alternately outputs electroporation pulses and iontophoresis, and further comprises: theenergy output device 14 determines the current output gear according to the input information; theenergy output device 14 alternately outputs electroporation pulses and iontophoresis under output conditions determined by the current output gear; the output conditions include voltage, pulse width and frequency of electroporation and current density of iontophoresis.

In one embodiment, thefirst button 111 is pressed briefly to select a third function, which is an electroporation iontophoresis mode of operation. When the third function is selected, thefirst electrode assembly 1451 turns on the microcurrentiontophoresis generating device 143 and theelectroporation generating device 144. In use, after thefirst electrode assembly 1451 is applied to the skin, the electroporation pulse generating component 1441PWM adjusts the pulse bi-directional current wave with a pulse width of 5ms to 20ms, a frequency of 10pps to 30pp, and a voltage of 10V to 60V, and the microcurrentiontophoresis generating device 143 outputs 100 μA/cm² ～500μA/cm² Constant current of (c). Alternatively, thesecond relay 1412, under the control of theenergy switching device 13, causes theelectroporation generating device 144 to output 5s and the microcurrentiontophoresis generating device 143 to output 10s, alternately at this frequency. It is to be understood that the electroporation pulse is applied to the skin load to realize the transient skin impedance reduction and form a micro-pore canal, and then the iontophoresis is used to push the functional components in the skin care product into the dermis layer through the micro-pore canal by the principle of homopolar repulsion so as to promote the absorption of the skin care product.

Three gear positions are used as an illustration, as shown in fig. 19. When the third function is selected, the first gear of the electroporation iontophoresis operation mode is default turned on, in the first gear, after thefirst electrode assembly 1451 is attached to the skin, the electroporation pulse generating unit 1441PWM adjusts the pulse width to 10ms and the pulse frequency to 20pps and outputs the bidirectional pulse square wave to thevoltage adjusting unit 1442, thevoltage adjusting unit 1442 adjusts the bidirectional pulse square wave to the bidirectional pulse square wave with the voltage of 40V through the adapting circuit and the resistor, and after the iontophoresis is switched to, the micro-currentiontophoresis generating unit 1431 outputs the PWM square wave to thecurrent adjusting unit 1432, and thecurrent adjusting unit 1432 adjusts the current intensity value of the PWM square wave to 100 μA/cm through the operation discharging circuit² . When the third function is selected, if thesecond key 112 is pressed for a short time, the second gear of the electroporation iontophoresis operation mode is turned on, and in the second gear, the electroporationpulse generation unit 1441 adjusts by PWMThe pulse width of the section is 15ms and the pulse frequency is 25pps and outputs a bi-directional pulse square wave to thevoltage regulating part 1442, thevoltage regulating part 1442 regulates the bi-directional pulse square wave to a bi-directional pulse wave with the voltage of 50V through an adaptive circuit and a resistor, and after the bi-directional pulse square wave is switched to ion introduction, the micro-current ionintroduction generating part 1431 outputs a PWM square wave to thecurrent regulating part 1432, and thecurrent regulating part 1432 regulates the current intensity value to 150 mu A/cm through an operational amplifier circuit² . When the third function is selected, thesecond key 112 is pressed for a short time, the third gear of the electroporation iontophoresis operation mode is started, in the third gear, the electroporationpulse generating unit 1441 adjusts the pulse width value to 20ms and the pulse frequency to 30pps through PWM and outputs the bidirectional pulse square wave to thevoltage adjusting unit 1442, thevoltage adjusting unit 1442 adjusts the bidirectional pulse square wave to the bidirectional pulse wave with the voltage of 60V through the adapting circuit and the resistor, and after the iontophoresis is switched to, themicro-current generating unit 1431 outputs the PWM square wave to thecurrent adjusting unit 1432, and thecurrent adjusting unit 1432 adjusts the current intensity value to 200 mu A/cm through the operational discharge circuit² 。

Therefore, the output intensity of the electroporation pulse and the output intensity of the ion introduction can be changed by switching different gears so as to meet different use requirements. However, in the electroporation iontophoresis mode, the output state of theelectronic device 10 includes, but is not limited to, the situation illustrated in fig. 19, and in fact, a person skilled in the art may set a plurality of different output states as desired.

Fig. 15 shows a block diagram of an electronic device in an embodiment of the utility model. As shown in fig. 15, theelectronic device 10 further includes anLED lighting device 23, where theLED lighting device 23 is configured to generate light waves with a wavelength of 415nm to 850nm, and an LED lamp is fixed on the workinghead 21. In a specific embodiment, theLED lighting device 23 may emit light waves with corresponding wavelengths under the control of theenergy switching device 13. The LED light-emittingdevice 23 can help repair the epidermis barrier when emitting yellow light with a wavelength of 560nm to 590 nm; when the LED light-emittingdevice 23 emits red light with the wavelength of 620-650 nm, the cell activity can be enhanced, the enzymatic reaction can be accelerated, the metabolism of cells can be promoted, and the regeneration of collagen can be stimulated; when the LED light-emittingdevice 23 emits near infrared light with the wavelength of 820-850 nm, blood circulation can be accelerated, and a new collagen fiber net can be constructed. When the LED light-emittingdevice 23 emits blue light with a wavelength of 410nm to 430nm, the skin can be relieved by diminishing inflammation.

Further, theelectronic device 10 further includes acooling device 24 disposed on the workinghead 21, and configured to cool the working surface of the workinghead 21, so as to implement the ice compress function of the workinghead 21. In a specific embodiment, the refrigeratingdevice 24 continuously outputs the ice feeling of 10-15 ℃ under the control of theenergy switching device 13, and particularly when the refrigerating device is used in combination with blue light, discomfort caused by heating of skin by radio frequency is effectively relieved.

Further, theelectronic device 10 further includes askin detection device 25 disposed in thebody 22 for detecting skin moisture and elasticity to verify the efficacy of theelectronic device 10 after use. In one embodiment, theskin detection device 25 detects skin moisture and elasticity under the control of the energy switching device 1 3.

Further, theelectronic device 10 further includes adisplay device 26 disposed on themain body 22 for displaying an operation state of the electronic device 10 (e.g. displaying a current operation mode, output information in a current gear, etc.), which may have a translucent display window 261 (see fig. 3 a). Thedisplay device 26 is used for displaying the operating state of the electronic device under the control of theenergy switching device 13.

Further, theelectronic device 10 further comprises anaudible prompting device 27, which is arranged on thebody 22 and is used as operation prompting feedback of theelectronic device 10, for example, when the electrode contacts the skin to output energy, the audible prompting device can generate sound, for example, vibration. Theaudible prompting device 27 issues audible prompts under the control of theenergy switching device 13.

As shown in fig. 3a and 4, theelectronic device 10 further comprises aportable charging base 28, which can be used as both a charging base and a protective cover for the workinghead 21. As shown in fig. 3a, when not in use, the chargingbase 28 is covered on the workinghead 21 to protect the workinghead 21. As shown in fig. 1, when the electric power tool is used, the chargingbase 28 on the workinghead 21 is taken away, so that the workinghead 21 can be normally used. As shown in fig. 15, the chargingbase 28 preferably includes a chargingmember 281 and a sterilizingmember 282. The chargingpart 281 is for charging thebattery 121 in thepower supply device 12, and the sterilizingpart 282 is for sterilizing the workinghead 21 and theelectrode assembly 145, preferably UVC sterilization. Further, thesecond electrode assembly 1452 is inserted into the chargingbase 28 to contact with the chargingmember 281 after being turned off, and can be used as a charging electrode, i.e. after thesecond electrode assembly 1452 is used, the workinghead 21 is inserted into the chargingbase 28, and at this time, two electrode plates in thesecond electrode assembly 1452 can be used as charging electrodes to charge theelectronic device 10.

As shown in fig. 20, in a preferred embodiment, theenergy switching device 13 includes a Micro Control Unit (MCU) 131, and themicro control unit 131 selectively turns on one of a radio frequency generating circuit, denoted by rf+ and RF-, and a micro current generating circuit, denoted by mc+ and MC-, which turns on theelectrode assembly 145 when outputting radio frequency, and turns on theelectrode assembly 145 when outputting micro current, and thus, the switching frequency and timing of thefirst relay 1411 are controlled by themicro control unit 131. Since both energies are alternately output, temperature monitoring and current sensing are also monitored simultaneously, theelectronic device 10 also needs to match the corresponding control and safety logic design according to the output requirements.

As shown in fig. 21, in a preferred embodiment, themicro-control unit 131 controls thesecond relay 1412 to be selectively connected to one of the electroporation generating circuit and the iontophoresis generating circuit, and themicro-control unit 131 controls the switching frequency and timing of thesecond relay 1412. Wherein the electroporation generating circuit is represented by EP+ and EP-, and the iontophoresis generating circuit is represented by ion+ and ION-. Electroporation generating circuits ep+ and EP-switch onelectrode assembly 145 when electroporation pulses are output, and ION-switch onelectrode assembly 145 when ION-switch on currents are output.

The technical effects achieved by the utility model are further demonstrated by experimental data.

FIG. 16 shows the efficacy of skin elasticity improvement achieved by the product of the present utility model and the product of the comparative example, wherein 2W represents 2 weeks of use, 4W represents 4 weeks of use, and the ordinate represents the skin elasticity R2 value; the height of the histogram is the test result, which is skin elasticity data compared with the skinelasticity base value 0.

As shown in fig. 16, after using 2W, the skin elasticity change rate R2 was 1.1% only when the radio frequency was applied, the skin elasticity change rate R2 was 3.2% when the radio frequency and the micro current were applied independently, and the skin elasticity change rate R2 was 3.4% when the radio frequency and the micro current were applied alternately and cooperatively; after using 4W, the skin elasticity change rate R2 is 9.3% only when the radio frequency is applied, the skin elasticity change rate R2 is 10.3% when the radio frequency and the micro current are applied respectively, and the skin elasticity change rate R2 is 13.8% when the radio frequency and the micro current are alternately cooperated. The greater the value of the rate of change R2 of skin elasticity, the more pronounced the improvement in skin elasticity. It can be seen that the therapeutic effect on the skin is better and the skin elasticity is significantly improved when the radio frequency and the micro-current alternately cooperate.

FIG. 17 shows the efficacy of skin roughness improvement achieved by the product of the present utility model and the product of the comparative example, the skin roughness being measured as a reduction in pore area, wherein 2W indicates 2 weeks of use, 4W indicates 4 weeks of use, and the ordinate indicates the total pore area change rate; the height of the histogram is a test result, and compared with thebasic value 0 of the total pore area, the change rate of the total pore area can be obtained, and the change rate of the total pore area is a negative value because the change rate of the total pore area is reduced compared with the basic value.

As shown in fig. 17, after using 2W, the total pore area change rate was-10.6% when only rf was applied, the total pore area change rate was-3.8% when rf and micro-current were applied, respectively, and the total pore area change rate was-6.5% when rf and micro-current were alternately applied in cooperation; after using 4W, the total pore area change rate is-0.4% when only the radio frequency acts, the total pore area change rate is-16.7% when the radio frequency and the micro current act respectively, and the total pore area change rate is-35.3% when the radio frequency and the micro current act alternately and cooperatively. The greater the rate of change of the total pore area, the more pronounced the improvement in skin roughness. Therefore, when the alternating synergistic effect of the radio frequency and the micro current is used, the therapeutic effect on the skin is better, and the skin roughness is also obviously improved.

Table 1 below is the immediate effect test data for the penetration enhancing function of the product of the present utility model and the direct application of the skin care product of the comparative example. As can be seen from the data in table 1, the penetration promoting function of the electroporation iontophoresis of the present utility model significantly improved moisture, oil and fat supplementation and roughness, which are all higher than those of the skin care product directly applied, and the improvement effect was statistically significant, wherein the electroporation iontophoresis function was used for 4min at one time, and the data in table 1 are immediate effects after one time use.

Table 1: immediate Effect test data for direct application of skin Care Using the penetration enhancing function of the present utility model and comparative examples

Remarks: the data in table 1 are statistically significant compared to the basal values, and in table 1, P <0.05, P <0.01, P <0.001.

In addition, experiments also prove that when the ion introducing function is simply used, the absorption rate of the functional components in the skin care product by the skin is extremely low, and the moisturizing and roughness improving efficiency of the skin around eyes are not ideal. When the electroporation iontophoresis is combined, the absorption rate of the functional components in the skin care product by the skin is greatly improved, and the moisture retention and the roughness of the skin around eyes are obviously improved.

It should be understood that the technical concept of integrating four energy outputs by theelectronic device 10 of the present utility model is to use the combination of the radio frequency and micro-current technologies on the premise of efficacy, so as to directly generate the efficacy of improving the skin and achieve better therapeutic efficacy; the electroporation and the iontophoresis do not exert a tightening effect on the skin, but the skin care product which is tightened by matching with the electroporation and the iontophoresis can promote the absorption of the skin care product, thereby achieving the effect of half the effort. In addition to the combined application of the two technologies, the skin at different parts of the face needs to be matched with different energy intensities, so that theelectronic device 10 of the utility model can have multiple working modes to output different energy intensities, thereby achieving the purposes of safety and effectiveness.

Further, when theelectronic device 10 of the present utility model is used as a handheld portable cosmetic instrument, when the radio frequency, micro-current, electroporation and iontophoresis functions are integrated in the limited space of theelectronic device 10, the design of the circuit and structure requires high requirements, which are specifically expressed in the following aspects:

(1) Because the space of theelectronic device 10 is limited, the whole hardware design (corresponding structural design) needs to consider a common generating device (such as ion introduction and micro-current output sharing), the final output energy form is adjusted through a back-end matching circuit, and the electrode assembly is shared, so that the hardware design and logic requirements are high;

(2) Different energy outputs are aimed at different target areas, and requirements are also provided for hardware design and structure; the traditional radio frequency beauty instrument can only output one radio frequency, most of which is 1MHz frequency output, but has difficulty in realizing stable high frequency (such as more than 3 MHz) and high power conversion rate; theelectronic device 10 of the present utility model can output frequencies ranging from 1MHz to 4MHz, and can be precisely applied to the face and thinner periocular skin in cooperation with electrode sheets of different sizes and locations.

It should be noted that modifications and additions to the present disclosure may be made by those of ordinary skill in the art without departing from the scope of the present disclosure, which is also to be considered as being within the scope of the present disclosure. Equivalent embodiments of the present utility model will be apparent to those skilled in the art having the benefit of the teachings disclosed herein, when made with the changes, modifications, and variations to the utility model; meanwhile, any equivalent changes, modifications and evolution of the above embodiments according to the essential technology of the present utility model still fall within the scope of the technical solution of the present utility model.

Claims (13)

1. An electronic device, comprising:

a power supply device for supplying power;

input means for generating input information, said input means being connected to said power supply means;

an energy switching device connected to the power supply device and the input device; the method comprises the steps of,

the energy output device is connected with the energy switching device and the power supply device and comprises at least two electrode assemblies, and each electrode assembly comprises two electrodes;

the electronic equipment is provided with a radio frequency micro-current working mode and an electroporation iontophoresis working mode;

the electronic equipment is configured to enable the energy output device to selectively start one of the radio frequency micro-current working mode and the electroporation iontophoresis working mode according to the input information generated by the input device; in the radio frequency micro-current working mode, the energy output device alternately outputs radio frequency and micro-current through the same electrode assembly; in the electroporation iontophoresis operation mode, the energy output device alternately outputs an electroporation pulse and an iontophoresis current through the same electrode assembly; wherein the radio frequency, the microcurrent, the electroporation pulse and the iontophoresis current are output in common with the same electrode assembly.

2. The electronic device of claim 1, wherein the energy output means further comprises relay means, radio frequency generation means, microcurrent iontophoresis generation means, and electroporation generation means; the relay device is connected with the energy switching device; the energy switching device is used for enabling the relay device to be selectively communicated with one of the radio frequency generation device, the microcurrent iontophoresis generation device and the electroporation generation device; at least one of the electrode assemblies is connected with the radio frequency generating device, the microcurrent iontophoresis generating device and the electroporation generating device; wherein the micro-current iontophoresis generating device is shared by the iontophoresis current and the micro-current output.

3. The electronic device of claim 2, wherein at least two of the electrode assemblies are different in size, and the two electrode assemblies different in size are a first electrode assembly and a second electrode assembly, respectively; the output ends of the radio frequency generating device, the microcurrent iontophoresis generating device and the electroporation generating device are selectively connected with one of the first electrode assembly and the second electrode assembly.

4. The electronic device of claim 3, further comprising a working head on which all of the electrode assemblies are disposed; the first electrode assembly comprises two concentrically arranged annular electrodes, the two annular electrodes are arranged on the end face of the working head, and/or the second electrode assembly comprises two L-shaped electrodes with arc-shaped outer surfaces, and the two L-shaped electrodes are arranged on the edge of the working head.

5. The electronic device of claim 4, wherein each of the ring-shaped electrodes has a width of 3mm to 5mm, a spacing between two of the ring-shaped electrodes is 3.5mm to 4.5mm, and/or a radius of a rounded arc surface of each of the L-shaped electrodes is greater than 2.5mm, and a spacing between two of the L-shaped electrodes is 3mm to 6mm.

6. The electronic device of claim 3, wherein an electrode size in the first electrode assembly is larger than an electrode size in the second electrode assembly;

the radio frequency micro-current working mode comprises a first working mode corresponding to the first electrode assembly and a second working mode corresponding to the second electrode assembly; in the first working mode, the radio frequency generating device outputs radio frequency of 2 MHz-4 MHz, and the microcurrent iontophoresis generating device outputs microcurrent of 335 mu A-500 mu A; in the second working mode, the radio frequency generating device outputs radio frequency of 1 MHz-2 MHz, and the microcurrent iontophoresis generating device outputs microcurrent of 335 mu A-500 mu A;

And/or the electroporation iontophoresis operation mode includes a first operation mode corresponding to the first electrode assembly and a second operation mode corresponding to the second electrode assembly; in the first working mode, the electroporation generating device outputs electroporation pulses with the voltage of 40V-60V, the pulse width of 10 ms-20 ms and the frequency of 20 pps-30 pps, and the microcurrent iontophoresis generating device outputs 200 mu A/cm² ～500μA/cm² Is introduced into the current; in the second working mode, the electroporation generating device outputs electroporation pulse with voltage of 10V-20V, pulse width of 5 ms-10 ms and frequency of 10 pps-20 pps, and the microcurrent iontophoresis generating device outputs 100 mu A/cm² ～200μA/cm² Is introduced into the current.

7. The electronic device of claim 2, wherein the relay means comprises two relays, one of the relays selectively connected to one of the radio frequency generation means and the microcurrent iontophoresis generation means, and the other relay selectively connected to one of the microcurrent iontophoresis generation means and the electroporation generation means.

8. The electronic device of claim 2, wherein the radio frequency generating means comprises a radio frequency generating part and a transformer, the radio frequency generating part being configured to turn on the relay device, an output terminal of the radio frequency generating part being connected to the transformer, an output terminal of the transformer being connected to the electrode assembly; the radio frequency generating component is used for converting the received square wave into a sine wave and outputting the sine wave to the transformer; the transformer is used for amplifying and boosting sine waves and outputting the sine waves to the electrode assembly as radio frequency signals.

9. The electronic device according to claim 2, wherein the microcurrent iontophoresis generating means includes a microcurrent iontophoresis generating member for turning on the relay means, an output terminal of the microcurrent iontophoresis generating member being connected to the current regulating member, and an output terminal of the current regulating member being connected to the electrode assembly; the microcurrent iontophoresis generating component is used for outputting microcurrent according to the received square wave signal or outputting PWM square wave signal to the current regulating component; the current regulating component is used for regulating the current density of the PWM square wave signal and outputting the PWM square wave signal to the electrode assembly.

10. The electronic device of claim 2, wherein the electroporation generating means comprises electroporation pulse generating means for switching on the relay means, an output of the electroporation pulse generating means being connected to the voltage regulating means, and an output of the voltage regulating means being connected to the electrode assembly; the electroporation pulse generating component is used for outputting electroporation pulses according to the received square wave signals, and outputting the electroporation pulses to the voltage regulating component after regulating the pulse width and the frequency of the electroporation pulses through PWM; the voltage regulating component is used for regulating the voltage of the electroporation pulse and outputting the voltage to the electrode assembly.

11. The electronic device according to any one of claims 1-10, wherein in the rf microcurrent mode of operation the electronic device has a plurality of gear steps, each of which corresponds to an output state reflecting rf microcurrent output information, all of which reflect different output states, the rf current in all of which output states is kept constant, the rf voltage and microcurrent in different of which output states are different, and/or wherein in the electroporation iontophoresis mode of operation the electronic device has a plurality of gear steps, each of which corresponds to an output state reflecting electroporation iontophoresis output information, all of which reflect different output states, and at least one of the pulse width, frequency, voltage and amperage of the iontophoresis pulse is different in different of which output states.

12. The electronic device of any of claims 1-10, wherein the number of electrode assemblies is plural, and at least two of the electrode assemblies are positioned asymmetrically to accommodate different target areas.

13. The electronic device of any one of claims 1-10, wherein in the rf microcurrent mode of operation the energy output device outputs the rf for a greater time than the microcurrent, and in the electroporation iontophoresis mode of operation the energy output device outputs the electroporation pulse for a lesser time than the iontophoresis current.

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