Method and device for realizing micro water hammer effect based on sound beam current

Abstract

The invention relates to a method for realizing a micro water hammer effect based on an acoustic beam current. When the special ultrasonic device works, special ultrasound of 0.5-30 kilohertz is generated to act on the liquid environment, so that directional fluid movement in the propagation direction of sound waves in liquid is generated on a solid-liquid interface, and the directional fluid movement comprises a focused columnar sound beam current; the special ultrasonic device is driven to work in at least one driving period with the first power, each driving period comprises a first stage and a second stage, the special ultrasonic device is driven to work in the first stage to generate special ultrasound of 0.5-30 kilomegahertz, and driving of the special ultrasonic device is stopped in the second stage; wherein the size of the first power enables the special ultrasonic device to generate a sound beam current in the first stage; the duty ratio of the second stage in the at least one driving period is adjusted to intermittently generate the sound beam current, the duration of the interval is larger than a threshold value, and the sound beam current generated intermittently under the threshold value can generate the micro water hammer effect.

Description

Technical Field

[0001] The present application relates to the fields of microfluidics and ultra-ultrasound, and in particular to a method and device for realizing a micro-water hammer effect based on an acoustic beam flow, and a liquid feeding device based on the micro-water hammer effect. Background Art

[0002] In the patent application with publication number CN118757487A, a method for generating a micro-scale cylindrical high-speed acoustic beam in a liquid environment and its application are provided.

[0003] How to make further technical improvements to enhance the effect of the acoustic beam flow is a technical problem that needs to be solved. Summary of the Invention

[0004] The present application provides a method and device for realizing a micro water hammer effect based on an acoustic beam flow, and a liquid feeding device based on the micro water hammer effect.

[0005] To achieve the above-mentioned objectives, the first aspect of the present application provides a method for realizing a micro-water hammer effect based on an acoustic beam flow, comprising: a liquid environment; a super-ultrasonic device, which generates 0.5-30 GHz ultrasonic waves to act on the liquid environment when in operation, so as to generate directional fluid motion along the direction of propagation of the sound wave in the liquid at the solid-liquid interface, wherein the directional fluid motion includes a focused columnar acoustic beam flow; the super-ultrasonic device is driven to operate in at least one driving cycle with a first power, each driving cycle including a first stage and a second stage, the super-ultrasonic device is driven to operate in the first stage to generate 0.5-30 GHz ultrasonic waves, and the driving of the super-ultrasonic device is stopped in the second stage; wherein the magnitude of the first power enables the super-ultrasonic device to generate the acoustic beam flow in the first stage; and the duty cycle of the second stage in at least one driving cycle is adjusted to intermittently generate the acoustic beam flow, and the duration of the intermittent period is greater than a threshold, and the acoustic beam flow intermittently generated below the threshold produces a micro-water hammer effect.

[0006] As a possible implementation of the first aspect, the step of adjusting the duty cycle of the second phase in at least one driving cycle to intermittently generate a sound beam flow includes at least one of the following: adjusting the duty cycle of the second phase in each driving cycle; or adjusting the duty cycle of the second phase of at least one of at least two consecutive driving cycles.

[0007] As a possible implementation of the first aspect, the micro water hammer effect is controlled by at least one of the following methods: controlling the strength of the micro water hammer effect by the first power; controlling the interval degree of the micro water hammer effect by the duty cycle of the second stage.

[0008] As a possible implementation of the first aspect, the liquid environment is located in a cavity, the wall of the cavity is provided with a hollow needle extending outward, and the sound beam generated by the ultra-ultrasonic device is directly facing the hollow needle; the hollow needle is used to extend the effective distance of the micro-water hammer effect and / or maintain the directionality of the micro-water hammer effect.

[0009] As a possible implementation of the first aspect, the ultra-ultrasonic device and the corresponding hollow needle are multiple in an array to generate a micro-water hammer effect of the array.

[0010] As a possible implementation method of the first aspect, it also includes: the target object acted upon by the acoustic beam flow of the generated micro-water hammer effect includes at least one of the following: first particles, epidermis or surface, and tissue located within the range of the micro-water hammer effect; the liquid environment includes second particles, and the acoustic beam flow of the generated micro-water hammer effect carries the second particles.

[0011] According to a second aspect of the present application, there is provided an apparatus for achieving a micro-water hammer effect based on an acoustic beam flow, comprising: a liquid environment; a super-ultrasonic device, which, when in operation, generates super-ultrasonic waves of 0.5-30 GHz to act on the liquid environment, so as to generate directional fluid motion at a solid-liquid interface along the direction of propagation of the acoustic wave in the liquid, wherein the directional fluid motion includes a focused columnar acoustic beam flow; the super-ultrasonic device is driven with a first power to operate in at least one driving cycle, each driving cycle including a first stage and a second stage, wherein the super-ultrasonic device is driven to operate in the first stage to generate super-ultrasonic waves of 0.5-30 GHz, and the driving of the super-ultrasonic device is stopped in the second stage; wherein the magnitude of the first power enables the super-ultrasonic device to generate the acoustic beam flow in the first stage; and wherein the duty cycle of the second stage in at least one driving cycle is adjusted to intermittently generate the acoustic beam flow, and the duration of the intermittent period is greater than a threshold, and the acoustic beam flow intermittently generated below the threshold produces a micro-water hammer effect.

[0012] As a possible implementation of the second aspect, the liquid environment is located in a cavity, a hollow needle extending outward is provided on a wall of the cavity, and the acoustic beam generated by the ultra-ultrasonic device is facing the hollow needle.

[0013] The third aspect of the present application provides a liquid feeding device based on the micro-water hammer effect, comprising: a cavity having an open end; a liquid injection hole on the wall of the cavity for injecting liquid into the cavity; a super-ultrasonic device is arranged in the cavity, and after the liquid is injected into the cavity, the super-ultrasonic device is placed in a liquid environment, and based on the method for realizing the micro-water hammer effect based on the acoustic beam flow described in any one of claims 1 to 6, an acoustic beam flow with a micro-water hammer effect is generated toward the open end of the cavity, so that the liquid is injected into the skin closing the open end through the acoustic beam flow with the micro-water hammer effect.

[0014] As a possible implementation of the third aspect, the position of the ultra-ultrasonic device relative to the opening end of the cavity is adjustable.

[0015] The solution provided in this application can generate an intermittent acoustic beam with a micro-water hammer effect. Compared with a continuous acoustic beam, it has a stronger force and can be used in scenarios such as drug delivery, cleaning, and microparticle manipulation. The intermittent acoustic beam based on the micro-water hammer effect is easier to quantify (such as counting the intermittent acoustic beam) and is also flexible to control (such as the ability to control the strength and frequency of the micro-water hammer effect), which has a good application scenario. BRIEF DESCRIPTION OF THE DRAWINGS

[0016] Figure 1 It is an image and schematic diagram of jet flow phenomenon and secondary flow phenomenon;

[0017] Figure 2 is a diagram of an acoustic beam flow generated in a liquid environment according to an embodiment of the present application;

[0018] Figure 3 This is a timing diagram of the output signal of the driving device of the ultra-ultrasonic device provided in an embodiment of the present application:

[0019] Figure 4 Schematic diagram of a driving device of an ultra-ultrasonic device provided in an embodiment of the present application;

[0020] Figure 5 Schematic diagram of the output signal of the water hammer effect generated by the driving device of the ultra-ultrasonic device provided in an embodiment of the present application;

[0021] Figure 6 is a schematic diagram of a drug delivery device provided in a fourth embodiment of the present application;

[0022] Figure 7 is a schematic diagram of the exploded components of the drug delivery device provided in the fourth embodiment of the present application;

[0023] Figure 8 is a schematic diagram of a drug delivery device provided in another fourth embodiment of the present application;

[0024] Figure 9 This is a photograph of the actual drug delivery device provided in the fourth embodiment of the present application;

[0025] Figure 10 This is a partial schematic diagram of a drug delivery device provided in an embodiment of the present application;

[0026] Figure 11 This is a schematic diagram of simulation of intermittent acoustic beam flow generated by several ultra-ultrasonic devices provided in the embodiments of the present application;

[0027] Figure 12This is an experimental photograph showing that the effective area of ​​the acoustic beam of a super-ultrasonic device provided by an embodiment of the present application increases with increasing distance;

[0028] Figure 13 This is a simulation diagram of an intermittent acoustic beam flow generated by an array of three ultra-ultrasonic devices provided in an embodiment of the present application;

[0029] Figure 14 This is a schematic diagram of the structure of three integrated ultra-ultrasound chips provided in an embodiment of the present application;

[0030] Figure 15 This is a comparison chart of the results of a single and three super ultrasonic device arrays provided in the embodiments of the present application;

[0031] Figure 16 This is a simulation diagram of different effects of hollow needles of different lengths provided in the embodiments of the present application;

[0032] Figure 17 This is a simulation diagram of the different effects of hollow needles with different apertures on the acoustic beam flow provided in the embodiments of the present application;

[0033] Figure 18 This is an experimental diagram of two hollow needles provided in the examples of this application;

[0034] Figure 19 This is a graph showing the experimental results of subcutaneous administration to mice provided in the examples of the present application. DETAILED DESCRIPTION

[0035] The technical solution provided by this application is further described below with reference to the accompanying drawings and examples. It should be understood that the system structure and business scenarios provided in the examples of this application are mainly for illustrating possible implementation methods of the technical solution of this application and should not be interpreted as the sole limitation of the technical solution of this application. It is known to those skilled in the art that with the evolution of the system structure and the emergence of new business scenarios, the technical solution provided by this application is also applicable to similar technical problems.

[0036] It should be understood that the embodiments of this application provide solutions for achieving a micro-water hammer effect based on acoustic beam flow, including methods, devices, and applications for achieving this effect based on acoustic beam flow, such as drug delivery, hydration, injection, and cosmetic applications. Because these technical solutions solve the same or similar problems, some repetitions may not be repeated in the description of the specific embodiments. However, these specific embodiments should be considered as having been referenced and can be referenced and combined with each other.

[0037] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as those commonly understood by those skilled in the art to which this application belongs. In the event of any inconsistency, the meanings described in this specification or the meanings derived from the contents recorded in this specification shall prevail. In addition, the terms used herein are only for the purpose of describing the embodiments of this application and are not intended to limit this application. In order to accurately describe the technical content in this application and to accurately understand the present invention, the following explanations or definitions are given for the terms used in this specification before describing the specific embodiments:

[0038] 1) Ultrasonic device: A high-frequency resonator can be a device that generates mechanical vibrations by applying voltage based on the piezoelectric effect. In this application, a piezoelectric resonator that generates ultrasonic waves of not less than 0.5 gigahertz (GHz) when in operation is used. Preferably, a piezoelectric resonator that generates ultrasonic waves of not less than 1 GHz and not more than 30 GHz when in operation is used. For example, it can be 2G-2.5 GHz. Such piezoelectric resonators can be, for example, surface acoustic wave (SAW) devices, bulk acoustic wave (BAW) devices, etc. For example, when it is a BAW, it can be a film bulk acoustic wave resonator (FBAR), a solid-state mounted resonator (SMR), or a Lamb wave resonator (LWR). For the sake of convenience, the piezoelectric resonator that can generate ultrasonic waves of not less than 0.5 GHz will be referred to as an ultrasonic device in the following.

[0039] 2) Jet phenomenon: This phenomenon occurs when the sound waves of a super-ultrasonic device act on a liquid. The regional vibrations generated by the working interface of the super-ultrasonic device can form traveling waves in the liquid, exerting a continuous thrust on the liquid in the liquid environment, causing at least a portion of the liquid to move linearly along the direction of sound wave propagation. This linear motion phenomenon is called jet phenomenon.

[0040] Secondary flow phenomenon: including eddy currents and heat reflux, is another phenomenon produced when ultra-ultrasonic devices act on liquids. It includes eddy currents (or micro-vortices) caused by the local circulation of liquids driven by the jet, and heat reflux caused by the heat generated by the ultra-ultrasonic devices.

[0041] The jet phenomenon and secondary flow phenomenon can be found in Figure 1 The images and schematics are shown. Figure 1 Schematic diagram of particle capture using vortex flow is shown in FIG.

[0042] 3) Acoustic beam flow: Since the acoustic beam flow in this application is generated by a super ultrasonic device, it is also called a super ultrasonic beam flow in this application. In this application, the acoustic beam flow is a unique type of jet phenomenon, which is characterized by the fluid moving at high speed along the direction of sound wave transmission and the jet presenting a thin cylindrical shape within its stroke. Before the acoustic beam flow is significantly attenuated, it is basically in a laminar state with the surrounding liquid and has a low degree of mixing with the surrounding liquid. Figure 2 An image of the generated acoustic beam flow captured by a high-speed camera is shown. Figure 2 It can be seen that the acoustic beam is focused and no longer looks like Figure 1 The jets are clustered and Figure 2 It is obviously not visible Figure 1 Secondary flow phenomenon in .

[0043] The generation condition of the supersonic wave beam flow in the embodiment of the present application is: the supersonic wave device is driven to work in at least one driving cycle with a first power, and each driving cycle includes a first stage and a second stage (see Figure 3 The device is configured to drive the ultra-ultrasonic device to generate an ultra-ultrasonic liquid environment with a frequency of 0.5-30 GHz in the first phase, and to stop driving the ultra-ultrasonic device in the second phase. The first power is sufficient to cause the ultra-ultrasonic device to generate a focused columnar acoustic beam perpendicular to the solid-liquid interface in the first phase. The duration of the first phase at the first power is less than a threshold value, or the duty cycle of the first phase within a driving cycle is less than a threshold value, so that the temperature of the ultra-ultrasonic device is suppressed within a controllable temperature threshold, and the ultra-ultrasonic device is prevented from substantially generating secondary flows (including eddies and backflows) in the liquid environment.

[0044] The intensity of the acoustic beam is related to the duration of the first phase (or the duty cycle within a drive cycle) and the intensity of the first power. For example, a shorter first phase duration suppresses temperature and secondary currents, but also reduces the beam intensity (a shorter first phase duration means a shorter period of energy accumulation). However, a higher first power leads to a higher beam intensity, which in turn increases the temperature rise of the ultra-sonic device. Therefore, applying a higher first power and a shorter first phase not only produces a higher-intensity beam, but also effectively suppresses temperature and secondary currents. Therefore, when real-time control of the acoustic beam intensity is required, a preferred approach is to use a shorter, fixed first phase (e.g., a fixed duty cycle within the cycle) and control the resulting beam intensity by applying varying first powers. A less preferred approach is to apply the same first power and control the resulting beam intensity by adjusting varying first phase values ​​(e.g., the duty cycle within the cycle). Alternatively, a less preferred approach is to control the resulting beam intensity by adjusting both the first phase value and the first power simultaneously.

[0045] Once the liquid environment is determined and the ultrasonic device is selected, the relationship between the acoustic beam intensity and the control parameters (the first power and / or the periodic signal composed of the first and second phases) can be calibrated. In one scenario, if the periodic signal is a constant (i.e., the first and second phases are constant), calibrating the acoustic beam intensity and the first power can reveal the relationship between the first power and the acoustic beam intensity (which corresponds to the distance the acoustic beam can propel the particles). This allows the appropriate first power to be controlled to propel the particles to the desired distance, or along the desired route.

[0046] 4) Regarding the first stage in the driving cycle: In the first stage in the driving cycle, the driving unit continuously outputs a number of signals. For example, when the signal generator outputs a 1GHz signal, assuming that the duration of the first stage is 1 microsecond, the driving unit will output 1000 signals (1GHz*1 microsecond=1000) during the first stage time (1 microsecond). The power loaded during the first stage time (1 microsecond) will be loaded onto the 1000 signals and output to drive the ultra-ultrasonic device. In the second stage of the driving cycle (corresponding to Figure 3 Switch signal low level) no drive signal output.

[0047] In a specific case, for example, the first stage is completed after only one execution, which is equivalent to or regarded as executing only one driving cycle in the present application, and therefore this case also falls within the protection scope of the present application.

[0048] 5) Driving device of ultra-ultrasonic device: such as Figure 4An embodiment is shown, including a control unit and a driving unit, wherein the driving unit includes a signal generator and a power amplifier. The signal output principle can be found in Figure 3 shown.

[0049] The signal generator is used to generate a high-frequency signal. The frequency of the original high-frequency signal generated by the signal generator is the same as or similar to the operating frequency of the ultra-ultrasonic device as the load (or the natural frequency of the ultra-ultrasonic device). The waveform of the signal generator can be a rectangular wave (such as Figure 3 The output signal of the corresponding driving unit is modulated into a rectangular wave, a sawtooth wave, a sharp pulse (or called a triangular wave), a step wave, a sine wave, or a half-wave signal.

[0050] The power amplifier is used to amplify the signal to be output so as to drive the ultra-sonic device.

[0051] The control unit can be a switching power supply, which can output a controllable switching signal. The switching signal can be a periodic signal. The switch-on phase (such as the switching power supply switch tube conduction phase) corresponds to a high level, and the corresponding Figure 3 In the first stage, the switch off stage corresponds to the low level, corresponding to Figure 3 The control unit can also control the operating voltage or amplification factor input to the power amplifier to achieve different amplified output powers, and the output power is the first power mentioned above. The first power can also be understood as the average energy density input to the super-ultrasonic device during a drive cycle (a drive cycle consists of a first stage and a second stage). Since the amount of energy is related to power and time, the amount of energy input to the super-ultrasonic device during a drive cycle is related to the first power level, the duration of the first stage or its duty cycle.

[0052] Among them, the above-mentioned acoustic beam flow and related technologies for driving ultra-ultrasonic devices to generate acoustic beam flow can also be referred to the relevant introduction in Chinese patent application number CN2024108322079.

[0053] 6) Micro water hammer effect: The conventional water hammer effect is an important phenomenon in fluid mechanics. It describes the pressure fluctuation caused by sudden changes in flow velocity in a liquid flow system. For example, when a valve in a pipeline is suddenly closed or opened, a shock wave will be generated in the pipeline due to the inertia of the fluid. This shock wave is like a hammer hitting the pipeline, hence the name "water hammer effect".

[0054] In this application, the micro-water hammer effect refers to the directional (i.e., beam direction) shock waves generated by driving a hypersonic device to generate an intermittent (e.g., pulsed) acoustic beam in a liquid. As will be appreciated, the acoustic beam will attenuate in the liquid. Therefore, the strength of the micro-water hammer effect at a specific location in the liquid is related to the distance from the hypersonic device. The micro-water hammer effect described in this application refers to the distance within which the micro-water hammer effect occurs.

[0055] In addition, due to the high focusing of the acoustic beam, the generated micro-water hammer effect also has a highly focused directionality (it is not difficult to understand that the directionality corresponds to the stage when the acoustic beam has not obviously attenuated), which is the above-mentioned directional shock wave (i.e., the direction of the acoustic beam).

[0056] This application proposes a solution for achieving a micro-water hammer effect based on acoustic beam flow. This solution can control a hypersonic device to intermittently generate a highly concentrated acoustic beam flow in a liquid, thereby creating a water hammer effect. Compared to a continuous acoustic beam flow (i.e., one without water hammer), this water hammer-based acoustic beam flow has a stronger force. This water hammer-based acoustic beam flow can be used for drug delivery, cleaning, and microparticle manipulation.

[0057] Drug administration, for example: injecting liquid or substance in liquid into the target object through the acoustic beam flow of the water hammer effect, such as injecting into the subcutaneous epidermis of an organism. The application scenario of the present application can be subcutaneous drug administration, which can be realized by a device such as a syringe, such as subcutaneous drug administration on the skin of the arm or buttocks, etc. The medicine here includes therapeutic drugs that can be in liquid form or dissolved in liquid, nutrients, etc., such as subcutaneous injection, or subcutaneous supply of nutrients, such as subcutaneous supply of nutrients on the face, neck, etc., nutrients such as hyaluronic acid, collagen, hyaluronic acid gel and other beauty or skin-friendly substances or water, etc. Since the acoustic beam flow has high focusing properties, another application scenario of the present application is fixed-point dyeing of the skin, for example, it is used to make patterns on the skin (such as skin tattoos, skin branding).

[0058] Cleaning: For example, the sound beam flow through the water hammer effect acts on the surface or skin of the material to clean the surface or skin.

[0059] For example, manipulation of particles can involve continuously applying an acoustic beam based on the water hammer effect to a particle (e.g., a cell) to test its mechanical properties, such as force impact resistance (force magnitude) and resistance (impact durability). Another example is changing the spatial position, shape, or structure of the particle (e.g., perforating the membrane on the particle surface).

[0060] As a further example, when the microparticles are cells, the manipulation of the cells can also include, for example, stimulating the cells with an acoustic beam based on the water hammer effect, so that the cells respond to the stimulation and activate mechanosensitive channels, reorganize the cytoskeleton, activate signal transduction pathways, or change secretory activity.

[0061] The solution provided in this application is described in detail below with reference to the accompanying drawings and embodiments.

[0062] The first embodiment of the present application provides a method for realizing micro water hammer effect based on acoustic beam flow, including a liquid environment and a hypersonic device;

[0063] When the ultra-ultrasonic device is in operation, it generates ultra-ultrasonic waves of 0.5-30 GHz to act on the liquid environment, so as to generate directional fluid motion at the solid-liquid interface along the direction of propagation of the sound wave in the liquid, and the directional fluid motion includes a focused columnar acoustic beam flow. Thus, the ultra-ultrasonic device is driven to operate in at least one driving cycle with a first power, and each driving cycle includes a first stage and a second stage. In the first stage, the ultra-ultrasonic device is driven to generate ultra-ultrasonic waves of 0.5-30 GHz, and in the second stage, the driving of the ultra-ultrasonic device is stopped. The magnitude of the first power enables the ultra-ultrasonic device to generate the acoustic beam flow in the first stage.

[0064] Furthermore, the duty cycle of the second phase in at least one driving cycle is adjusted to intermittently generate the acoustic beam flow, and the duration of the intermittent generation is greater than a threshold value, and the intermittently generated acoustic beam flow below the threshold value produces a micro water hammer effect.

[0065] In some embodiments, the duty cycle of the second phase in at least one driving cycle is adjusted to intermittently generate the acoustic beam flow, which can be achieved by adjusting the duty cycle of the second phase in each driving cycle. Figure 5 The example shown in a is described as follows:

[0066] Assumptions Figure 3 Under the output duty cycle driving signal shown, based on the characteristics of the fluid (fluidity, viscosity, continuity), the generated acoustic beam flow is a continuous acoustic beam flow (continuous acoustic beam flow means that there is no or no obvious water hammer effect). Figure 5 As shown in Figure 1, by increasing the duty cycle of the second stage and ensuring that the acoustic beam can be generated, when the duty cycle of the second stage increases to a certain level, an intermittent acoustic beam can be formed to generate a micro-water hammer effect. In this case, the duration of each cycle of the drive device output remains unchanged, and what changes is the distribution ratio of the first stage to the second stage. The shorter the first stage, the less energy the ultra-sonic device obtains in one cycle, and the lower the energy of each micro-water hammer. It is important to note that the first stage cannot be shorter than the duration of the acoustic beam (too low energy makes it difficult to generate an acoustic beam).

[0067] In some embodiments, the duty cycle of the second phase of at least one driving cycle is adjusted to intermittently generate the acoustic beam flow, which can be achieved by adjusting the duty cycle of the second phase of at least one driving cycle for at least two consecutive driving cycles. Figure 5 The examples shown in b and c are introduced as follows:

[0068] Figure 5 In the example shown in b, relative Figure 3 The output driving signal is modulated into a low-level signal every 2n cycles, thereby realizing the generation of intermittent acoustic beam flow to generate a micro water hammer effect.

[0069] Figure 5 In the example shown in c, relative Figure 3 The output driving signal is modulated into a low-level signal every 3n cycles, thereby realizing the generation of intermittent acoustic beam flow to generate a micro water hammer effect.

[0070] in, Figure 5 Compared with b, the frequency of micro water hammer in c is lower, and the duration of the acoustic beam of each micro water hammer is longer, so the energy of each micro water hammer is higher.

[0071] In other embodiments, the micro water hammer may be generated by varying the time interval (or frequency), for example, Figure 3 The second and fifth cycles of the output drive signal are modulated into low-level signals.

[0072] In some embodiments, in addition to adjusting the micro-water hammer effect in the manner provided above, the micro-water hammer effect can also be controlled by at least one of the following methods: controlling the strength of the micro-water hammer effect by the first power strength; controlling the interval degree of the micro-water hammer effect by the duty cycle of the second stage.

[0073] In some embodiments, the liquid environment is located in a cavity, a hollow needle extending outward is provided on a wall of the cavity, and the acoustic beam generated by the ultra-ultrasonic device is directed toward the hollow needle.

[0074] The hollow needle can be used to influence the distance of the micro-water hammer effect and / or the directionality of the micro-water hammer effect. Figure 10 In the example shown, the middle hollow needle is facing the ultrasonic device. For the effect of the hollow needle on the micro water hammer effect, please refer to the following article. Figure 16 and Figure 17 Introduction.

[0075] In some embodiments, the ultra-sonic device and the corresponding hollow needle are multiple in array to produce the micro-water hammer effect of the array. Thus, it can be applied to apply the acoustic beam with micro-water hammer effect to a large area target. Figure 14 Multiple ultrasonic chips are integrated on one substrate. Figure 14 Description of the illustrated embodiment.

[0076] In some embodiments, the method further includes: the target object on which the acoustic beam flow of the generated micro water hammer effect acts includes at least one of the following: a first particle, epidermis or surface, and tissue within the range of the micro water hammer effect.

[0077] In some embodiments, the liquid environment further includes second particles, and the acoustic beam flow generated by the micro water hammer effect carries the second particles.

[0078] The second embodiment of the present application provides a device for realizing micro water hammer effect based on acoustic beam flow, comprising the liquid environment and the ultra-ultrasonic device described in the first embodiment. The ultra-ultrasonic device can intermittently generate acoustic beam flow based on any method described in the first embodiment to produce micro water hammer effect.

[0079] In some embodiments, the liquid environment is located in a cavity, the wall of the cavity is provided with a hollow needle extending outward, and the sound beam generated by the ultra-ultrasonic device is directly facing the hollow needle; the hollow needle is used to extend the effective distance of the micro-water hammer effect and / or maintain the directionality of the micro-water hammer effect.

[0080] The third embodiment of the present application provides a liquid feeding device based on the micro-water hammer effect, comprising: a cavity having an open end; a liquid injection hole on the wall of the cavity for injecting liquid into the cavity; a super-ultrasonic device is arranged in the cavity, and after the liquid is injected into the cavity, the super-ultrasonic device is placed in a liquid environment, and based on any of the methods for realizing the micro-water hammer effect based on the acoustic beam flow described in the first embodiment, an acoustic beam flow with the micro-water hammer effect is generated toward the open end of the cavity, so that the liquid is injected into the skin that closes the open end through the acoustic beam flow with the micro-water hammer effect.

[0081] In some embodiments, the position of the ultra-ultrasonic device relative to the opening end of the cavity is adjustable.

[0082] Based on the principle of any of the methods or devices in the first, second, and third embodiments above, the present application further provides a specific implementation example, namely, a drug delivery device based on the micro-water hammer effect provided in the fourth embodiment, which is hereinafter referred to as an injection device. Figure 6 or Figure 7 The schematic diagram and Figure 9As shown in the actual photograph, the injection device based on the micro water hammer effect of this embodiment may include:

[0083] A cavity 1 having an open end; a liquid injection hole 4 is provided on the wall of the cavity 1 for injecting liquid into the cavity 1; a special ultrasonic device 2 is provided in the cavity 1, and after the liquid is injected into the cavity 1, the special ultrasonic device 2 is placed in a liquid environment, and the special ultrasonic device 2 is used to generate an intermittent acoustic beam flow with a micro water hammer effect in the liquid environment toward the open end of the cavity 1, so as to inject the liquid into the skin that closes the open end through the acoustic beam flow with the micro water hammer effect.

[0084] In some embodiments, the cavity 1 can have any shape, such as a cylinder, a hemisphere, a spherical segment, or a bell. In some embodiments, the open end of the cavity 1 can be in contact with a target object (e.g., skin), thereby sealing the open end of the cavity 1. In some embodiments, when the ultra-ultrasonic device 2 is not activated and the open end of the cavity 1 is not in contact with the target object (e.g., skin), the size of the open end of the cavity 1 can also be designed to prevent the liquid in the cavity 1 from flowing out due to the internal and external pressure difference or the surface tension of the liquid.

[0085] In some embodiments, the ultra-ultrasonic device 2 can be mounted on the inner wall of the cavity 1, or on a support portion protruding inward from the inner wall, or on a bracket 3 that can be mounted on the cavity 1, and the ultra-ultrasonic device 2 faces the open end of the cavity 1.

[0086] The liquid injection hole 4 on the cavity 1 is used to connect an external liquid supply device. In some embodiments, such as Figure 9 As shown, the liquid supply device can be a syringe that can be inserted into the liquid injection hole 4 to inject liquid into the cavity 1. Alternatively, a bottle container such as a medicine bottle can be inserted into the liquid injection hole 4. For example, the syringe can be inserted directly through the tubular opening of the medicine bottle, or a conduit (such as a hose or rigid tube) can be connected between the medicine bottle and the liquid injection hole 4. In other embodiments, the liquid supply device can also be an external liquid supply device connected via a conduit, and the liquid supply device can include a micropump to pump the liquid into the cavity 1.

[0087] In some embodiments, the wall of the cavity 1 away from the open end has a through hole; the through hole is equipped with a bracket 3 that partially extends into the cavity 1, and the end of the bracket 3 located in the cavity 1 is equipped with the ultra-ultrasonic device 2. In some embodiments, the through hole for assembling the bracket 3 can also be located on the side wall of the cavity 1. In some embodiments, as Figure 8 As shown, the liquid injection hole 4 can also be arranged on the bracket 3.

[0088] In some embodiments, the bracket 3 is connected to the through-hole thread 31, and the end of the bracket 3 away from the ultra-ultrasonic device 2 is located outside the cavity 1. The connection through the thread 31 allows the relative position of the bracket 3 and the cavity 1 to be adjusted, so that the position of the ultra-ultrasonic device 2 in the cavity 1 can be adjusted. In some embodiments, the through-hole is located opposite the opening end (i.e., the axial direction of the through-hole is opposite the opening end). By screwing the bracket 3 in or out of the through-hole, the distance between the ultra-ultrasonic device 2 and the opening end can be adjusted. In some embodiments, the range of the distance between the ultra-ultrasonic device 2 and the opening end can be adjusted from 0 to 2 cm. In other embodiments, when the through-hole is not located opposite the opening end (e.g., the axial direction of the through-hole is inclined to the plane of the opening end), by screwing the bracket 3 in or out of the through-hole, the distance between the ultra-ultrasonic device 2 and the opening end is adjusted, and the position of the horizontal component of the ultrasonic device at the opening end is also adjusted.

[0089] In some embodiments, the support 3 is tubular, with wires connected to the ultra-ultrasonic device 2 routed within the tube. In some embodiments, the portion of the support 3 located outside the cavity 1 can serve as a handheld portion for operating the device of this embodiment. Therefore, the portion of the support 3 located outside the cavity 1 can be shaped to be easily held. When the support 3 is tubular, the ultra-ultrasonic device 2 and the tubular support 3 together form an ultra-ultrasonic probe.

[0090] In some embodiments, the drive device and power supply device for driving the ultra-ultrasonic device 2 can be independently provided relative to the aforementioned structure (i.e., the portion including the cavity 1 and the support 3), and the electrical connection between the drive device and the ultra-ultrasonic device 2 is achieved through the aforementioned wires. A push-type switch, a touch switch, a drive power adjustment control, or a display screen can be provided on the handheld portion, or these can be provided on the external drive device and power supply device, wherein the drive device and power supply device can be assembled into a housing.

[0091] In some embodiments, the drive device (including the control unit) and power supply for the ultra-ultrasonic device 2 can be integrated into the aforementioned structure of the bracket 3 serving as the handheld portion, located outside the cavity 1, thereby making the device a handheld device. The corresponding handheld portion can be provided with a mechanical (e.g., push-type) switch, a touch-sensitive switch, a drive power adjustment control (e.g., a knob), or a display screen. These switches or controls can be used to control the start and stop of the injection device, the mode of driving the ultra-ultrasonic device 2 (e.g., intermittent operation, continuous operation), and the power of the ultra-ultrasonic device 2. In some embodiments, the power supply includes a transformer and corresponding circuits (e.g., filtering, modulation module, protection circuit, etc.), and is connected to an external AC power source. In other embodiments, the power supply includes a rechargeable battery and corresponding circuits (e.g., DC / AC, adjustment module, charging circuit, protection circuit, etc.).

[0092] In some embodiments, the ultra-ultrasonic device 2 includes: at least two ultra-ultrasonic chips arranged in an array on the same substrate, and the at least two ultra-ultrasonic chips share electrodes on the substrate. This type of integration can reduce wires and reduce energy loss caused by line resistance. Figure 14 An example is shown in which three ultra-sonic chips are mounted on a substrate (the ultra-sonic chip here refers to the acoustic wave reflection layer and piezoelectric layer located on the substrate). The upper electrodes of the piezoelectric layers of the three ultra-sonic chips are connected to the same terminal on the substrate, and the lower electrodes are also connected to the same terminal. These two terminals are used to connect to an external drive circuit. Figure 14 Figure a is a photo taken under a microscope, and Figure b is a real photo. The three claws in the figure are electrodes and the rectangular boxes are end points (gold fingers).

[0093] In some other embodiments, the ultra-ultrasonic device 2 includes: relatively independent ultra-ultrasonic devices 2 can be arranged to form an array, for example, different ultra-ultrasonic devices 2 composed of different ultra-ultrasonic chips located on different substrates.

[0094] In some embodiments, when multiple hypersonic chips are provided, the parameters of these chips may be the same to achieve the same function or effect under the same drive. In other embodiments, the parameters of these chips may be different to achieve different functions or effects simultaneously under the same drive.

[0095] In some embodiments, when multiple hypersonic chips are present, the chips are arranged in a configuration (e.g., position and orientation) such that the acoustic beams generated by the micro-water hammer effect can be parallel or divergent, thereby increasing the effective area. For example, the chips can be arranged in an array on the same plane or on the same convex surface. In some embodiments, the chips can be arranged in a configuration (e.g., position and orientation) such that the acoustic beams generated by the micro-water hammer effect can converge, thereby increasing the effect on a specific point. For example, the chips can be arranged in an array on the same concave surface.

[0096] The overall shape of the array of the plurality of ultra-ultrasonic chips or the array of the plurality of ultra-ultrasonic devices 2 may be rectangular, circular, linear, or other shapes. For example, Figure 13 The example of the array composed of a plurality of hypersonic chips shown includes three hypersonic chips.

[0097] In some embodiments, as Figure 8As shown, the wall of the cavity 1 is also provided with air holes 7. The air holes 7 are provided to facilitate the exhaust during the process of injecting liquid into the cavity 1, or to replenish air during the process of injecting liquid in the cavity 1 into the subcutaneous tissue. In some embodiments, the air holes 7 are micro-pores, and the aperture of the micro-pores is set to achieve the characteristics of being air-permeable and liquid-tight, that is, the air permeability is guaranteed, and the possibility of the liquid in the cavity being spilled to the outside from the air holes 7 during the use of the device can be reduced. In other embodiments, when the aperture of the air holes 7 is not limited, the position of the air holes 7 can also solve the problems of exhausting, replenishing air and avoiding spillage by applying an elastic film with micropores. The elastic film can be applied to the outer wall or inner wall of the cavity 1 corresponding to the air holes 7. In some embodiments, when it is expected that the part of the device of the present application that contacts the skin can overflow the liquid when the contact is not close, the aperture of the above-mentioned air holes 7 can be slightly larger, for example, when the device of the present application is used as a beauty and skin care device. In other embodiments, when it is expected that the device of the present application and the skin contact part will not overflow the liquid as much as possible when the contact is not close, the size of the aperture of the above-mentioned pore 7 is a size, and the aperture size is large enough to balance the liquid in the cavity with other external air pressure, or the above-mentioned elastic mold with micropores is used to achieve micro-balance of the air pressure inside and outside the cavity 1, so that even in the case of loose contact, the possibility of liquid leakage is reduced when the ultra-ultrasound chip is not started.

[0098] In some embodiments, the ultra-ultrasonic device 2 is further configured to generate one or any combination of the following in the liquid environment: eddy currents, cavitation effects, thermal effects, jets, etc. The different effects produced by a ultra-ultrasonic device 2 can be achieved by adjusting the drive power, such as adjusting the cycle of the drive signal, the proportion of the drive level within a cycle, the power level, the continuous drive duration, etc. In some embodiments, when multiple ultra-ultrasonic chips are present, as described above, when these chips have different parameters, different effects can be achieved under the same power drive. When the ultra-ultrasonic device 2 generates eddy currents, the eddy currents act on the skin, thereby enhancing the cleansing effect on the skin surface. When the ultra-ultrasonic device 2 generates cavitation bubbles, they enhance cleansing of the skin surface. Cavitation removes surface oil, debris, dust, and other substances, unclogging pores and cleansing the face. Furthermore, cavitation softens the stratum corneum and accelerates keratin metabolism, restoring skin elasticity and tightening the skin. Cavitation also opens intercellular spaces, increasing skin permeability, allowing cosmetic substances like collagen and hyaluronic acid to penetrate the epidermis and reach the dermis, achieving transdermal delivery without causing skin trauma. During operation, some of the ultrasonic energy generated by the ultra-ultrasonic device 2 is converted into heat, which accelerates blood circulation, enhances metabolism, improves local tissue nutrition, and enhances enzyme activity. Furthermore, because the power applied to the ultra-ultrasonic device 2 is low, for example, no more than 10W, the thermal effects of the ultra-ultrasound do not damage the skin. Furthermore, when the ultra-ultrasonic device 2 generates a jet, the force of the jet is less than that of the acoustic beam, enabling the jet to cleanse the skin.

[0099] In some embodiments, as Figure 10As shown, the open end of the cavity 1 has a cover 8 that closes the open end, and the position of the cover 8 facing the ultra-ultrasonic device 2 has a hollow needle 81 extending outward. The acoustic beam with a micro-water hammer effect generated by the ultra-ultrasonic device 2 is directed toward the cavity of the hollow needle 81. In other embodiments, the hollow needle 81 can also be set at a position of the cover 8 that is not facing the ultra-ultrasonic device 2. The hollow needle 81 can be inserted into the skin, and the depth of the skin can be different depending on the length of the hollow needle 81. Based on this, it is easier to inject the acoustic beam into the subcutaneous tissue reached by the hollow needle 81. In some embodiments, the cover 8 and the cavity 1 are integrally arranged, for example, the cover 8 and the cavity are pressed together to achieve an integral arrangement. The integral arrangement can better control the distance between the ultra-ultrasonic device 2 and the hollow needle 81 during assembly. In other embodiments, the cover 8 and the cavity 1 can be assembled separately, which can facilitate the replacement of the cover 8 with different hollow needles 81. The hollow needles 81 can be microneedles manufactured using high-precision 3D printing or micro-nanofabrication techniques. In some embodiments, the hollow needles 81 can be arranged in an array. In some embodiments, the structure of the hollow needles 81 can maintain the liquid within the cavity 1 by utilizing liquid tension when the ultra-ultrasonic device 2 is not operating.

[0100] In some embodiments, hollow needles of different shapes can be used. For example, the hollow needle can be Figure 10 As shown, its inner diameter is cylindrical, that is, the inner diameter of the extending direction is the same. In other embodiments, the hollow needle can be as follows Figure 16 or Figure 17 The shape of the hollow needle, such as the inner diameter cylindrical or columnar, the length, and the distance between the hollow needle and the ultra-ultrasonic device will have different effects on the acoustic beam flow.

[0101] In some embodiments, when the inner diameter of the hollow needle is conical, the inner diameter of the hollow needle 81 can be gradually reduced in the direction away from the cavity 1. Based on this structure, the acoustic beam can be further focused, ejected from the tip of the hollow needle 81 and injected subcutaneously. Among them, on the one hand, the structure of the hollow needle 81 reduces the direct transmission of the acoustic beam energy to the external laminar fluid, which can enhance the local pressure of the acoustic beam with a micro-water hammer effect, increase the effective distance of the micro-water hammer effect, limit the generation of vortexes in the acoustic beam, and reduce power dissipation. But on the other hand, the inner wall of the hollow needle 81 itself will also generate resistance to the acoustic beam, which will lead to the loss of some energy. Therefore, a comprehensive analysis is required.

[0102] Among them, different apertures at the tip of the hollow needle 81, different lengths of the hollow needle 81, and different distances between the ultra-ultrasonic device 2 and the facing hollow needle 81 have different effects on the effect of the sound beam being emitted from the needle tip. The above specific parameters can be designed based on the desired effect of the subcutaneous injection, such as the injection depth and the diffusion of the injected liquid.

[0103] For example, when the inner diameter of the hollow needle 81 is conical, for different apertures at the tip of the hollow needle 81: when the aperture is small, the acoustic beam attenuates faster due to the smaller aperture at the outlet and the rapid shrinkage of the aperture (one possibility is the energy loss of the inner wall of the hollow needle 81 to the acoustic beam resistance), the pressure at the outlet is significantly smaller, the effective distance is shortened, but the angle of the effective range (the spray angle ejected from the outlet) is larger (when the energy is not enough to maintain a high directivity, it is more divergent), which can reach 45 degrees. As the aperture increases, the pressure at the outlet increases, the effective distance increases, and the angle of the effective range gradually becomes smaller and the directionality is better. Figure 16 The hollow needle 81 exit aperture is shown.

[0104] For example, when the inner diameter of the hollow needle 81 is conical, for different lengths of the hollow needle 81: when the aperture of the tip of the hollow needle 81 is the same, the longer the length of the hollow needle 81, the more obvious the acceleration effect on the sound beam flow, the better the directionality of the sound beam flow after passing through the hollow needle 81, and the smaller the diffusion angle. The length of the hollow needle 81 is selected depending on the transdermal depth and the transdermal effect to be achieved. In some embodiments, the length of the hollow needle 81 can be 50 to 2000 μm. Figure 17 The figure shows the acceleration effect of the hollow needle 81 with a needle length of 200um and 300um on the acoustic beam. It can be seen that the acoustic beam with a hollow needle length of 300um has a longer range than that of the acoustic beam with a needle length of 200um in basically the same time. When it is an acoustic beam with a micro water hammer effect, the micro water hammer effect is farther.

[0105] For example, when the inner diameter of the hollow needle 81 is conical, for different distances from the hollow needle 81 to the ultra-ultrasonic device: the farther the hollow needle 81 is from the ultra-ultrasonic device, the less energy the sound beam entering the hollow needle 81, and the larger the final injection angle ejected from the outlet of the hollow needle 81 (when the energy is not enough to maintain a high directivity, the divergence is more reflected).

[0106] In some embodiments, when the ultra-ultrasonic device 2 operates in the frequency range of 0.1 to 10 GHz, the drive power is 0.1 to 100 W, and the total pulse period is 10 to 2000 ms, the range, area of ​​action, and intensity of the acoustic beam generated have the following relationship: within 100 μm from the device surface, the area of ​​action of the acoustic beam is similar to the shape and area of ​​the device itself, and the maximum pressure point also occurs within this distance. When the distance exceeds 100 μm, the shape of the acoustic beam gradually becomes circular, the area of ​​action increases, and the intensity decreases. Based on this, the distance between the ultra-ultrasonic device 2 and the facing hollow needle 81 can be designed. In some embodiments, the distance between the ultra-ultrasonic device 2 and the facing hollow needle 81 is 0 to 2000 μm.

[0107] In some embodiments, the open end of the cavity 1 has a cover body that closes the open end, and the cover body has a mesh surface. The direction of the sound beam flow of each special ultrasonic device 2 in the cavity 1 can be directly facing a mesh hole of the mesh surface. The mesh surface structure can use liquid tension to keep the liquid in the working cavity when the special ultrasonic device 2 is not working. The mesh structure can also serve as isolation to keep the special ultrasonic device 2 in the cavity 1 at a required distance from the contact part of the injected target object.

[0108] In some embodiments, the device provided in the embodiments of the present application is fastened to the skin by means of straps or rubber bands, for example Figure 6 In one example shown, the bottom of the cavity may have an outer edge extending outward, and the outer edge may have a hole 5 for fitting a magic tape 6. In other embodiments, the device of the present application may be directly pressed against the skin by hand-held pressure. In some embodiments, the position where the open end of the cavity 1 of the device of the present application contacts the skin may be designed to be smooth so that it can fit tightly when pressed against the skin. In some embodiments, the position where the open end of the cavity 1 contacts the skin may also be fitted with or wrapped with an elastic material with good biocompatibility, such as soft silicone, rubber, etc., to further ensure sealing and reduce the possibility of liquid leakage from the cavity 1.

[0109] In some embodiments, the device provided in the embodiments of the present application may also be equipped with a laser positioning device for alignment, which can emit laser to indicate the area where the ultra-ultrasonic device 2 is currently aligned.

[0110] In some embodiments, when the ultra-ultrasonic device 2 is pulse-driven, the different ratios of the first and second phases in each drive cycle can achieve different pulse effects. The ratio of the first and second phases and the drive cycle length can be adjusted accordingly to achieve a more obvious micro-water hammer effect. Among them, the pressure generated by a conventional pulsed water jet is much greater than the pressure generated by a continuous water jet. By utilizing the fatigue effect of the material of the target object, the periodic transient impact stress wave can cause the target object material to reach the fatigue limit faster than the stagnation pressure of the continuous water jet. This principle of water jet also applies to acoustic beam flow. Compared with continuous acoustic beam flow, the micro-water hammer effect generated by intermittent acoustic beam flow has high energy utilization efficiency and can generate high water pressure in a pulsed manner at a lower liquid flow rate. As described above, the parameters of the intermittent acoustic beam flow can be flexibly adjusted, including pulse frequency (corresponding to the drive cycle), duty cycle (corresponding to the ratio of the first and second phases in the drive cycle), distance from the material surface, etc. In addition, the micro-water hammer effect combined with the focusing of the acoustic beam flow can reduce the transmission of compressive stress on the surface of the target object, enhance the transmission of shear stress along the surface, and reduce the impact on areas not directly impacted.

[0111] In some embodiments, any of the aforementioned injection devices (i.e., drug delivery devices) of this application may also be combined with low-frequency ultrasound. For example, a low-frequency ultrasound device may be provided in the aforementioned introduction portion, thereby enabling the simultaneous or non-simultaneous operation of the low-frequency ultrasound and the ultra-ultrasonic device 2. The low-frequency ultrasound has low energy but a wide range, and is used to treat large areas, while the ultra-ultrasonic device has high energy and is used to treat specific areas. The low-frequency cavitation effect is combined with the high-frequency fixed-point cavitation effect to achieve an increase in transdermal speed.

[0112] In some embodiments, any of the injection devices (i.e., drug delivery devices) described above in the present application can also be used in conjunction with a chemical permeation enhancer. For example, a chemical permeation enhancer can be injected into the liquid reservoir, or applied to the skin to interact with the stratum corneum lipids to change their arrangement structure, thereby enhancing the drug's penetration ability by weakening the barrier function of the stratum corneum without causing significant damage to the cells.

[0113] In some embodiments, any of the above-described injection devices (i.e., drug delivery devices) of the present application can also be combined with radio frequency, microcurrent, and / or LED lights, for example, radio frequency devices, microcurrent needles, and / or LED lights are provided in the above-mentioned introduction portion. These three can be used as auxiliary devices, and their main functions are wrinkle removal and improvement of skin condition. For example, by utilizing the penetrability of radio frequency and / or microcurrent, they penetrate the epidermis and act on the dermis, heat the dermal tissue through the LED thermal effect, and stimulate fibroblasts to synthesize collagen and elastin. Integrate wrinkle removal and improvement of skin condition with transdermal function.

[0114] In some embodiments, any of the above-described injection devices (i.e., drug delivery devices) of the present application can also be combined with electroporation. For example, an electroporation electrode is provided in the above-mentioned introduction part, and electric pulses are used to stimulate the skin or subcutaneous tissue to open the keratin phospholipid bilayer or the gap between skin cells, thereby forming an input channel for the active ingredient and realizing transdermal delivery of the cosmetic substance.

[0115] The present application also provides a corresponding cosmetic device, including any of the above-mentioned injection devices (ie, drug delivery devices) and various optional embodiments, which will not be described in detail.

[0116] The present application is further described below with reference to specific embodiments. In this embodiment, we first investigate the characteristics of a hypersonic device generating an intermittent acoustic beam in a liquid to produce a micro-water hammer effect (also known as the characteristics of the acoustic beam at the solid-liquid interface). We then explore the characteristics of the acoustic beam combined with a microneedle structure, and finally explore an example of its application in an injection device.

[0117] Characteristics of ultrasonic beams with micro-water hammer effects generated by ultra-ultrasonic devices in liquids: Intermittent acoustic beams of pentagonal, circular, and annular ultra-ultrasonic devices were simulated, and some experiments were conducted. The conclusions are as follows:

[0118] 1) When the frequency of the super-ultrasonic device is in the range of 0.1 to 10 GHz, the power of the super-ultrasonic device is in the range of 0.1 to 100 W, and the total pulse period is in the range of 1 to 2000 ms, the range of the acoustic beam, the size of the area of ​​action, and the intensity of action have the following relationship: within 100 μm from the surface of the super-ultrasonic device, the area of ​​action of the acoustic beam is similar to the shape and area of ​​the super-ultrasonic device itself, and the maximum pressure point also occurs within this distance. When the distance is greater than 100 μm, the shape of the acoustic beam gradually tends to be circular, the area of ​​action increases, and the intensity of action decreases. See also Figure 11 The following diagram shows the simulation of pulsed acoustic beams generated by several ultra-ultrasonic devices, and Figure 12 The experimental photograph shows that the effective area of ​​the sound beam increases with the distance.

[0119] 2) When the shape and area of ​​the ultra-ultrasonic device remain unchanged, the effective area and intensity of the acoustic beam flow increase with the increase of driving power.

[0120] 3) When calculating the pressure generated by the acoustic beam at the solid-liquid interface by means of liquid dynamic pressure, the dynamic pressure of the liquid can be: Formula for calculation. Where: p 动 is the dynamic pressure of the liquid, ρ is the liquid density, and v is the liquid velocity at a certain point.

[0121] Dynamic pressure refers to the pressure generated by a fluid due to its velocity, representing its kinetic energy. Dynamic pressure varies with fluid velocity: if the velocity increases, the dynamic pressure increases; if the velocity decreases, the dynamic pressure decreases.

[0122] The energy conversion at the solid-liquid interface is as follows: the acoustic pressure field generated by the ultra-ultrasonic device accelerates the fluid to eject, forming an acoustic beam. The acoustic beam is accelerated by the acoustic pressure field and reaches its maximum speed at a certain point. At this time, the kinetic energy reaches its maximum. Then, due to the existence of liquid resistance, it will decelerate to a certain extent. When it hits the solid wall at the solid-liquid interface, the speed drops to 0. At this time, all kinetic energy is converted into pressure potential energy when it hits the wall. By calculating the kinetic energy at the maximum speed, the pressure potential energy when it hits the wall can be obtained, and the pressure and force at this time can be calculated. The calculation of pressure and force according to the maximum speed is shown in the following table:

[0123] Maximum speed (m / s) Dynamic pressure (Kpa) Force (uN) 5 12.5 50 10 50 200 20 200 800 40 800 3200 80 3200 12800

[0124] 4) It was verified that the intermittent acoustic beam flow has a water hammer effect and its energy utilization efficiency is higher than that of the continuous acoustic beam flow.

[0125] The short-pulse, high-speed, discontinuous acoustic beam flow formed by the present application can achieve rapid, multiple, high-pressure continuous impacts, that is, the formation of a water hammer effect. From another perspective, the present application is equivalent to a miniature water hammer generator. Among them, the initial pressure of the water hammer effect is much higher than the steady-state pressure, so the pulsed output can achieve the effect of significantly increasing the pressure and improving the transdermal efficiency. The following is an introduction to the principle that the initial pressure of the water hammer effect is much higher than the steady-state pressure (such as a continuous acoustic beam flow):

[0126] The water hammer pressure in the initial stage can be derived based on the Bernoulli equation, where the Bernoulli equation is: p = ρ·c·v, where p is the pressure of the fluid at a certain point and ρ is the density of the fluid (water), which is about 1000 kg / km 3 , c is the wave velocity of the fluid (water), which is about 1400m / s in the pipe, and v is the velocity of the fluid (water). Since water hammer pressure is composed of discontinuous sound beam flow, the water hammer pressure formula is derived from the Bernoulli equation: △P=ρ·c·△v, where △v is the change in water velocity (which can be understood as the change in velocity between two sampling points). For example, if △v is 0.5m / s at a certain position in the experiment, the water hammer pressure at that position in the experiment is △P=1000Kg / m 3 ·1400m / s·0.5m / s=700kPa.

[0127] During the stagnant phase, i.e., the steady-state pressure phase (e.g., continuous acoustic beam flow), the pressure can be calculated based on the kinetic energy theorem, where the kinetic energy theorem formula is: Where P is the impulse (pressure) of the fluid (water), ρ is the density of the fluid (water), and v is the velocity of the fluid (water). If v is also 0.5 m / s at this location, P can be calculated to be 125 Pa at this location, which is much lower than the initial water hammer pressure.

[0128] In further experiments, the initial pressures at different distances from the interface of the ultra-ultrasonic device were calculated. When the ultra-ultrasonic device was driven by 16W, the initial pressure within a distance of 1mm was at the MPa level, and the initial pressure gradually increased with the shortening of the distance, and was much greater than the pressure in the stagnation stage.

[0129] From the above, it can be seen that the high-pulse (i.e., intermittently generated) acoustic beam flow has a water hammer effect, and its energy utilization efficiency is higher than that of the continuously driven acoustic beam flow, and the pressure generated is much higher than the pressure generated by the continuous acoustic beam flow.

[0130] 5) Based on the distance between the ultrasonic device and the skin and the power, the treated skin area can be from 0.1mm^2 to 10mm^2.

[0131] 6) Advantages of forming an array of multiple devices: it can increase power utilization while increasing the active area.

[0132] like Figure 13 The figure shows the simulation of an array composed of three ultra-ultrasonic devices generating a pulsed acoustic beam (corresponding to the water hammer effect). Figure 15 Shows a single hypersonic device with Figure 13 The diagrams showing the interface processing of three special ultrasonic devices are as follows: under the same power, a single special ultrasonic device and multiple special ultrasonic devices characterize the interface processing area. By photographing the shape of the red fluorescent particles (5μm) adhered to the interface after the special ultrasonic device is turned on and blown away, the size of the processing area of ​​the device at different heights from the interface is characterized. From the results, it can be seen that under the same driving power, the processing area of ​​multiple special ultrasonic devices is significantly improved compared to a single device. The figure shows three special ultrasonic devices, and the processing area is expanded by about 3 times, which increases the effective area. Among them, the three special ultrasonic devices are driven by one driving module (i.e., one with three), that is, under the same driving power of the same driving module, the processing area is expanded by about 3 times, thereby improving power utilization.

[0133] 7) A microneedle structure with a tapered inner diameter hollow needle in the direction opposite to the ultrasonic device can enhance the local pressure of the acoustic beam, increase the effective range or diffusion angle of the acoustic beam, limit the generation of eddy currents, and reduce power dissipation. For the hollow needle with a tapered inner diameter, simulations have verified that different apertures and lengths of the hollow needle tip have different effects on the effect of the acoustic beam emitted from the needle tip. See [1] for more information. Figure 16 and Figure 17 shown.

[0134] 8) The effect of the acoustic beam flow can be adjusted by using a micro-needle structure such as a hollow needle with an increased inner diameter in the opposite direction of the ultra-ultrasonic device. Figure 18 ,in Figure 18 Figure (a) shows an actual image of the acoustic beam using a 200μm-long microneedle and a schematic diagram of the injection angle. Figure (b) shows an actual image of the acoustic beam using a 400μm-long microneedle and a schematic diagram of the injection angle. Both microneedles have an outlet diameter of 60μm. The ultrasonic device is located at the top of the figure, generating the acoustic beam downward. The microneedle is placed directly below the ultrasonic device for the experiment.

[0135] The following table shows Figure 18 Figure a shows the experimental data of the acoustic beam flow under a 200μm long microneedle:

[0136]

[0137] The following table shows Figure 18 Figure b corresponds to the experimental data of the acoustic beam flow under a 400μm long microneedle:

[0138]

[0139] From the above usage data, we can preliminarily draw the following conclusions when using hollow needles with cylindrical inner diameters:

[0140] a. When the acoustic beam passes through the microneedles, the jet speed is slower, but the jet area is wider. This is mainly due to energy loss caused by part of the acoustic beam not entering the microneedles, and energy loss caused by the inner wall of the microneedles.

[0141] b. The injection speed and injection angle can be changed by controlling the length of the microneedle and the distance between the microneedle and the ultrasonic device, such as Figure 18 As shown in the figure, the farther the microneedle is from the ultra-sonic device, the less acoustic beam enters the microneedle, and the slower the jet speed after passing through the microneedle. However, the jet angle is larger, making it more suitable for diffuse drug delivery over a large area.

[0142] c. Comparison Figure 18 In a and b or the experimental results data above, for 400μm microneedles and 200μm microneedles, under the same distance from the ultra-ultrasonic device, the injection angle of the acoustic beam after being ejected from the microneedle does not change much, but the injection speed is slower when using the 400μm microneedle than when using the 200μm microneedle.

[0143] Hollow needles with different structures (lengths and shapes) and different distances from the ultra-ultrasonic device will have different effects on the sound beam ejected from the hollow needle. Therefore, the corresponding hollow needle structure or distance from the ultra-ultrasonic device can be designed based on this to achieve the speed and injection angle of the liquid (such as medicine) ejected from the hollow needle, thereby realizing different forms of drug delivery.

[0144] Another experiment of this application is as follows: The back of shaved mice was treated with a super ultrasonic device for transdermal treatment. The solution used was a 2mmol rhodamine dye solution. The experimental group turned on the super ultrasonic device with a power of 8W for 10 minutes, while the control group was only immersed in the solution. This was used to test the transdermal effect of the device on small molecules. After treatment, the treated sites of both groups were sectioned, frozen, and stained with DAPI (DAPI is an organic fluorescent dye that can penetrate the cell membrane and bind to double-stranded DNA in the cell nucleus to play a labeling role). Figure 19 The experimental results shown in the figure show a certain degree of transdermal penetration in both sections of the experimental group. In particular, the first section shows that the rhodamine dye has penetrated the epidermis and reached the dermis and subcutaneous tissue. However, in the control group, fluorescence was only observed in the epidermis where the rhodamine dye had infiltrated the epidermis, with virtually no fluorescence observed in deeper layers. This demonstrates that rhodamine itself has difficulty penetrating the mouse epidermis, but treatment with an ultrasonic device can improve its permeability.

[0145] In another set of experiments in this application, ultra-sonic devices were used to perform transdermal treatment on the backs of shaved mice, mainly to explore the differences in transdermal transdermal properties of different molecular weights, as follows:

[0146] Transdermal Experiment A: Solution used: 1% FITC-dextran solution, molecular weight: 3-6k; Ultrasonic probe operating power: 4W; Pulse output cycle: 50ms / 200ms, 15 minutes. Experimental Conclusion: Low-molecular-weight substances can significantly transdermally penetrate the skin under the influence of acoustic fluidics. Different transdermal depths and effects can be achieved by controlling power, distance, and duration.

[0147] Transdermal Test B: Solution used: 1% FITC-dextran solution, molecular weight: 40k; Ultrasonic probe operating power: 8W; Pulse output cycle: 50ms / 200ms, 15 minutes. Conclusion: Medium-molecular-weight substances can penetrate smoothly, but may cause skin damage. Appropriate control of device power, skin distance, and exposure time is required.

[0148] Transdermal Experiment C: Solution used: 0.8% FITC-dextran solution, molecular weight: 250k; Ultrasonic probe operating power: 8W; Pulse output cycle: 50ms / 200ms, 15 minutes. Conclusion: High-molecular-weight substances show no significant transdermal penetration with short-term treatments. Transdermal delivery of high-molecular-weight substances requires integration with other methods (such as microneedles).

[0149] Based on the above experiments, it can be used to design the actual use of special ultrasonic devices for injection, based on the molecular weight of the injected liquid, the injection (transdermal) depth, etc., to predict the driving power, distance from the skin, action time, whether to use microneedles, etc. of the special ultrasonic device to be used.

[0150] The dosing regimen provided in this application can be achieved in a non-invasive manner, that is, transdermal delivery of substances can be achieved without causing trauma to the skin. When an arrayed super-ultrasonic device design is adopted, large-area rapid treatment of the skin can also be achieved. Among them, the precision, high-speed acoustic jet or acoustic beam flow and super-ultrasonic device cavitation have good directionality and regionality, and the transdermal treatment range can be accurately controlled; the treatment process is uniform and controllable, and there will be no problems such as accumulation and agglomeration of cosmetic substances. When a handheld design is adopted, it is easy to use and does not need to be used in a specific place. And it has a high degree of integration and can be integrated with beauty products based on other principles (such as radio frequency, microcurrent, LED light, ultrasound, etc.), and a variety of modes are convenient for users to choose and use.

[0151] The present application also provides a method for administering a drug, using the above-mentioned drug delivery device or any of its optional embodiments to achieve subcutaneous injection. Specific methods for achieving the injection, such as controlling the driving process of the acoustic beam flow, can be found in the relevant description of the above-mentioned injection device and will not be repeated here.

[0152] The present application also provides a corresponding cosmetic method, which is implemented using the above-mentioned cosmetic device or the above-mentioned injection device, or any optional embodiment thereof, and will not be described in detail.

[0153] In the several embodiments provided in this application, it should be understood that the disclosed devices and methods are not limited to the above embodiments, and can also be implemented in other ways. For example, the device embodiments described above are only schematic. For example, the division of the units is only a logical function division. There may be other division methods in actual implementation, such as multiple units or components can be combined or integrated into another system, or some features can be ignored or not executed. Another point is that the mutual coupling or direct coupling or communication connection shown or discussed can be through some interfaces, indirect coupling or communication connection of devices or units, which can be electrical, mechanical or other forms.

[0154] The units described as separate components may or may not be physically separate, and the components shown as units may or may not be physical units, that is, they may be located in one place or distributed across multiple network units. Some or all of these units may be selected to achieve the objectives of this embodiment as needed.

[0155] In addition, the words "first, second, third, etc." or module A, module B, module C and other similar terms in the specification and claims are only used to distinguish similar objects and do not represent a specific ordering of the objects. It can be understood that the specific order or sequence can be interchanged where permitted so that the embodiments of the present application described herein can be implemented in an order other than that illustrated or described herein.

[0156] In the above description, the numbers representing the steps, such as S10, S20, etc., do not necessarily mean that the steps must be executed in this manner. If permitted, the order of the steps can be interchanged or they can be executed simultaneously.

[0157] The term "comprising" as used in the specification and claims should not be construed as limiting to what is listed thereafter; it does not exclude other elements or steps. Thus, it should be interpreted as specifying the presence of the features, integers, steps, or components mentioned, but not excluding the presence or addition of one or more other features, integers, steps, or components, or groups thereof. Thus, the expression "a device comprising means A and B" should not be limited to a device consisting solely of components A and B.

[0158] References in this specification to "one embodiment" or "an embodiment" mean that a particular feature, structure, or characteristic described in connection with the embodiment is included in at least one embodiment of the present application. Therefore, the phrases "in one embodiment" or "in an embodiment" appearing throughout this specification do not necessarily refer to the same embodiment, but may refer to the same embodiment. Furthermore, in one or more embodiments, the particular features, structures, or characteristics can be combined in any suitable manner, as would be apparent to one of ordinary skill in the art from this disclosure.

[0159] Note that the above are only preferred embodiments of the present application and the technical principles employed. Those skilled in the art will understand that the present application is not limited to the specific embodiments described herein, and that various obvious changes, readjustments, and substitutions can be made by those skilled in the art without departing from the scope of protection of the present application. Therefore, although the present application has been described in more detail through the above embodiments, the present application is not limited to the above embodiments and may include many other equivalent embodiments without departing from the scope of protection of the present application, all of which fall within the scope of protection of the present application.

Claims

1. A method for realizing micro water hammer effect based on acoustic beam flow, characterized in that: include: Liquid environment; A hypersonic device, which generates 0.5-30 GHz hypersonic waves to act on the liquid environment to generate directional fluid motion at the solid-liquid interface along the direction of sound wave propagation in the liquid, wherein the directional fluid motion includes a focused columnar acoustic beam flow; The ultra-ultrasonic device is driven to operate in at least one driving cycle at a first power, each driving cycle including a first stage and a second stage, wherein the ultra-ultrasonic device is driven to generate ultra-ultrasonic waves of 0.5-30 GHz in the first stage, and the driving of the ultra-ultrasonic device is stopped in the second stage; wherein the magnitude of the first power enables the ultra-ultrasonic device to generate the acoustic beam flow in the first stage; The duty cycle of the second phase in at least one driving cycle is adjusted to intermittently generate an acoustic beam flow, and the duration of the intermittent generation is greater than a threshold value, and the intermittently generated acoustic beam flow below the threshold value produces a micro water hammer effect.

2. The method according to claim 1, characterized in that The step of adjusting the duty cycle of the second phase in at least one driving cycle to intermittently generate an acoustic beam flow includes at least one of the following: Adjust the duty cycle of the second phase in each drive cycle; For at least two consecutive driving cycles, the duty cycle of the second phase of at least one of the driving cycles is adjusted.

3. The method according to claim 1 or 2, characterized in that The micro water hammer effect is controlled by at least one of the following methods: The strength of the micro water hammer effect is controlled by the first power; The interval degree of the micro water hammer effect is controlled by the duty cycle of the second stage.

4. The method according to any one of claims 1 to 3, characterized in that: The liquid environment is located in a cavity, a hollow needle extending outward is provided on the wall of the cavity, and the acoustic beam generated by the ultra-ultrasonic device is facing the hollow needle; The hollow needle is used to extend the action distance of the micro water hammer effect and / or maintain the directionality of the micro water hammer effect.

5. The method according to claim 4, characterized in that The ultra-ultrasonic device and the corresponding hollow needle are arranged in a plurality in an array to generate a micro-water hammer effect of the array.

6. The method according to any one of claims 1 to 5, characterized in that: Also includes: The target object on which the acoustic beam flow of the generated micro water hammer effect acts includes at least one of the following: a first particle, an epidermis or a surface, or a tissue located within the range of the micro water hammer effect; The liquid environment includes second particles, and the acoustic beam flow generated by the micro water hammer effect carries the second particles.

7. A device for realizing micro water hammer effect based on acoustic beam flow, characterized in that: include: Liquid environment; A hypersonic device, which generates 0.5-30 GHz hypersonic waves to act on the liquid environment to generate directional fluid motion at the solid-liquid interface along the direction of sound wave propagation in the liquid, wherein the directional fluid motion includes a focused columnar acoustic beam flow; The ultra-ultrasonic device is driven at a first power to operate in at least one driving cycle, each driving cycle including a first stage and a second stage, wherein the ultra-ultrasonic device is driven to generate ultra-ultrasonic waves of 0.5-30 GHz in the first stage, and the driving of the ultra-ultrasonic device is stopped in the second stage; wherein the magnitude of the first power enables the ultra-ultrasonic device to generate the acoustic beam flow in the first stage; The duty cycle of the second phase in at least one driving cycle is adjusted to intermittently generate an acoustic beam flow, and the duration of the intermittent generation is greater than a threshold value, and the intermittently generated acoustic beam flow below the threshold value produces a micro water hammer effect.

8. The device according to claim 7, characterized in that The liquid environment is located in a cavity, a hollow needle extending outward is provided on the wall of the cavity, and the acoustic beam generated by the ultra-ultrasonic device is facing the hollow needle.

9. A liquid feeding device based on micro water hammer effect, characterized in that: include: a cavity having an open end; The wall of the cavity is provided with a liquid injection hole for injecting liquid into the cavity; A super ultrasonic device is provided in the cavity. After liquid is injected into the cavity, the super ultrasonic device is placed in a liquid environment. Based on the method for realizing micro-water hammer effect based on acoustic beam flow described in any one of claims 1 to 6, an acoustic beam flow with micro-water hammer effect is generated toward the opening end of the cavity, so that liquid is injected into the skin that closes the opening end through the acoustic beam flow with micro-water hammer effect.

10. The device according to claim 9, characterized in that The position of the ultra-ultrasonic device away from the opening end of the cavity is adjustable.

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