Method and apparatus for realizing micro water hammer effect based on acoustic beam

Abstract

This application relates to a method for achieving a micro-water hammer effect based on an acoustic beam, comprising: a liquid environment; an ultrasonic device that generates 0.5-30 GHz ultrasonic waves during operation, which 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, the directional fluid motion including a focused columnar acoustic beam; driving the ultrasonic device to operate for at least one driving cycle with a first power, each driving cycle including a first stage and a second stage, wherein the ultrasonic device is driven to generate 0.5-30 GHz ultrasonic waves in the first stage, and the driving of the ultrasonic device is stopped in the second stage; wherein the magnitude of the first power causes the ultrasonic device to generate an acoustic beam in the first stage; adjusting the duty cycle of the second stage in the at least one driving cycle to intermittently generate an acoustic beam, and the duration of the intermittent generation is greater than a threshold, wherein the intermittently generated acoustic beam can generate a micro-water hammer effect.

Description

Technical Field

[0001] This application relates to the fields of microfluidics and ultrasonic technology, and in particular to a method and apparatus for realizing micro water hammer effect based on acoustic beam flow, and a liquid delivery device based on micro water hammer effect. Background Technology

[0002] Patent application CN118757487A discloses a method for generating microscale columnar high-speed acoustic beams in a liquid environment and its application.

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

[0004] This application provides a method and apparatus for realizing the micro water hammer effect based on acoustic beam flow, and a liquid supply device based on the micro water hammer effect.

[0005] To achieve the above objectives, a first aspect of this application provides a method for realizing a micro-water hammer effect based on an acoustic beam, comprising: a liquid environment; an ultrasonic device that generates 0.5-30 GHz ultrasonic waves during operation, which 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, the directional fluid motion including a focused columnar acoustic beam; driving the ultrasonic device to operate for at least one driving cycle with a first power, each driving cycle including a first stage and a second stage, wherein the ultrasonic device is driven to generate 0.5-30 GHz ultrasonic waves in the first stage, and the driving of the ultrasonic device is stopped in the second stage; wherein the magnitude of the first power causes the ultrasonic device to generate the acoustic beam in the first stage; adjusting the duty cycle of the second stage in the at least one driving cycle to intermittently generate the acoustic beam, and the duration of the intermittent interval is greater than a threshold, wherein the intermittently generated acoustic beam generates a micro-water hammer effect below the threshold.

[0006] As one possible implementation of the first aspect, adjusting the duty cycle of the second stage in at least one drive cycle to intermittently generate an acoustic beam includes at least one of the following: adjusting the duty cycle of the second stage in each drive cycle; adjusting the duty cycle of the second stage in at least one of at least two consecutive drive cycles.

[0007] As one 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 controlling the strength of a first power; controlling the interval of the micro-water hammer effect by controlling the duty cycle of the second stage.

[0008] As one possible implementation of the first aspect, the liquid environment is located in a cavity, the wall of which is provided with hollow needles extending outward, and the sound beam generated by the ultrasonic device is directed towards the hollow needles; the hollow needles extend the action distance of the micro water hammer effect and / or maintain the directionality of the micro water hammer effect.

[0009] As one possible implementation of the first aspect, the ultrasonic device and the corresponding hollow needle are arranged in an array of multiple arrays to generate an array of micro water hammer effects.

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

[0011] A second aspect of this application provides a device for realizing a micro-water hammer effect based on an acoustic beam, comprising: a liquid environment; an ultrasonic device that generates 0.5-30 GHz ultrasonic waves during operation, which 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, the directional fluid motion including a focused columnar acoustic beam; the ultrasonic device is driven by a first power to operate in at least one driving cycle, each driving cycle including a first stage and a second stage, wherein the ultrasonic device is driven to generate 0.5-30 GHz ultrasonic waves in the first stage, and the driving of the ultrasonic device is stopped in the second stage; wherein the magnitude of the first power causes the ultrasonic device to generate the acoustic beam in the first stage; the duty cycle of the second stage in at least one driving cycle is adjusted to intermittently generate the acoustic beam, and the duration of the intermittent generation is greater than a threshold, the intermittently generated acoustic beam below the threshold generating a micro-water hammer effect.

[0012] As a possible implementation of the second aspect, the liquid environment is located in a cavity, the walls of which are provided with hollow needles extending outward, and the sound beam generated by the ultrasonic device is directed towards the hollow needles.

[0013] A third aspect of this application provides a liquid delivery device based on the micro-water hammer effect, comprising: a cavity having an open end; an injection hole on the wall of the cavity for injecting liquid into the cavity; an ultrasonic device disposed in the cavity, wherein after liquid is injected into the cavity, the ultrasonic device is placed in a liquid environment, and a sound beam with the micro-water hammer effect is generated in the direction of the cavity opening end according to any one of claims 1-6, so as to inject liquid into the skin that closes the opening end through the sound beam with the micro-water hammer effect.

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

[0015] The solution provided in this application can generate intermittent acoustic beams with a micro-water hammer effect, which have a stronger force than continuous acoustic beams and can be applied to scenarios such as drug delivery, cleaning, and manipulation of microparticles. Intermittent acoustic beams based on the micro-water hammer effect are easier to quantify (e.g., by counting intermittent acoustic beams) and more flexible in control (e.g., the strength and frequency of the micro-water hammer effect can be controlled), making them suitable for various applications. Attached Figure Description

[0016] Figure 1 These are images and diagrams illustrating jet and secondary flow phenomena.

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

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

[0019] Figure 4 This is a schematic diagram of the driving device for the ultrasonic device provided in the embodiments of this application;

[0020] Figure 5 This is a schematic diagram of the output signal of the water hammer effect generated by the driving device of the ultrasonic device provided in the embodiments of this application;

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

[0022] Figure 7 This is a schematic diagram showing the disassembled components of the drug delivery device provided in the fourth embodiment of this application;

[0023] Figure 8 These are schematic diagrams of drug delivery devices provided in four other embodiments of this application;

[0024] Figure 9 These are photographs of the actual drug delivery device provided in the fourth embodiment of this application;

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

[0026] Figure 11 This is a simulation diagram of several special ultrasonic devices generating intermittent sound beams provided in the embodiments of this application;

[0027] Figure 12These are experimental photographs showing the increase in the area of ​​the ultrasonic device acting on the sound beam with increasing distance, as provided in the embodiments of this application.

[0028] Figure 13 This is a simulation diagram of the intermittent acoustic beam generated by the operation of the three special ultrasonic device arrays provided in the embodiments of this application;

[0029] Figure 14 This is a schematic diagram of a structure integrating three ultrasonic chips provided in an embodiment of this application;

[0030] Figure 15 This is a comparison diagram of the effects of a single and three-element ultrasonic device arrays provided in the embodiments of this application;

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

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

[0033] Figure 18 These are experimental diagrams of two types of hollow needles provided in the embodiments of this application;

[0034] Figure 19 This is a diagram showing the experimental results of subcutaneous drug administration to mice provided in the embodiments of this application. Detailed Implementation

[0035] The technical solutions provided in this application will be further described below with reference to the accompanying drawings and embodiments. It should be understood that the system architecture and business scenarios provided in the embodiments of this application are mainly for illustrating possible implementations of the technical solutions of this application and should not be construed as the sole limitation on the technical solutions of this application. Those skilled in the art will recognize that the technical solutions provided in this application are equally applicable to similar technical problems as system architectures evolve and new business scenarios emerge.

[0036] It should be understood that the solutions for achieving micro-water hammer effects based on acoustic beams provided in the embodiments of this application include methods, devices, and applications for achieving micro-water hammer effects based on acoustic beams, such as applications in drug delivery, hydration, injection, and cosmetic procedures. Since these technical solutions solve problems using the same or similar principles, some repetitive details may not be repeated in the description of specific embodiments. However, it should be considered that these specific embodiments have already referenced each other and can be mutually referenced and combined.

[0037] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs. In case of any inconsistency, the meaning set forth in this specification or derived from the content described herein shall prevail. Furthermore, the terminology used herein is for the purpose of describing embodiments of this application only and is not intended to limit this application. To accurately describe the technical content of this application and to accurately understand the invention, the following explanations or definitions of the terms used in this specification are provided before describing specific embodiments:

[0038] 1) Ultrasonic Device: A high-frequency resonator, which can be a device that generates mechanical vibration by applying voltage based on the piezoelectric effect. In this application, a piezoelectric resonator that generates ultrasonic waves of not less than 0.5 GHz (GHz is equivalent to gigahertz) during operation is used. Preferably, it is a piezoelectric resonator that generates ultrasonic waves of not less than 1 GHz and not more than 30 GHz during operation, for example, it can be 2 GHz to 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 BAW, it can be a thin-film bulk acoustic wave resonator (FBAR), a solid-state assembled resonator (SMR), or a Lamb wave resonator (LWR). For ease of description, the piezoelectric resonator that can generate ultrasonic waves of not less than 0.5 GHz will be referred to as an ultrasonic device from now on.

[0039] 2) Jet phenomenon: This is a phenomenon that occurs when the sound waves from an ultrasonic device act on a liquid. The regional vibration generated at the working interface of the ultrasonic device can form a traveling wave in the liquid and exert a continuous thrust on the local liquid in the liquid environment, causing at least a portion of the liquid to move in a straight line along the direction of sound wave propagation. This phenomenon of straight-line movement is called jet phenomenon.

[0040] Secondary flow phenomena, including eddies and thermal backflow, are another phenomenon generated when ultrasonic devices act on liquids. They include eddies (or micro vortices) caused by local circulation generated by the jet driving the liquid, and thermal backflow generated by the heating of ultrasonic devices.

[0041] The jet phenomenon and secondary flow phenomenon can be found in [reference needed]. Figure 1 The images and diagrams shown. Figure 1 The diagram shows a schematic of using eddies to capture particles.

[0042] 3) Acoustic Beam: Since the acoustic beam in this application is generated based on a supersonic device, it is also referred to as a supersonic acoustic beam. In this application, the acoustic beam is a unique type of jet phenomenon, characterized by the fluid moving at high speed along the direction of sound wave propagation and the jet appearing as a thin cylinder within its path. Before significant attenuation, the acoustic beam is essentially in a laminar state with the surrounding liquid, exhibiting low mixing with the surrounding liquid. Figure 2 An image of the resulting acoustic beam, captured by a high-speed camera, is shown. Figure 2 It can be seen that the acoustic beam has focusing properties and is no longer like... Figure 1 A cluster of jets, and Figure 2 It is clearly not visible in the middle Figure 1 Secondary flow phenomena in [the context of something].

[0043] The conditions for generating the ultrasonic beam in this embodiment are: driving the ultrasonic device with a first power for at least one driving cycle, each driving cycle including a first stage and a second stage (see...). Figure 3 The drive unit outputs a signal portion that, in the first stage, drives the ultrasonic device to generate a 0.5-30 GHz ultrasonic effect in a liquid environment, and in the second stage, stops driving the ultrasonic device. The first power is sufficient to enable the ultrasonic device to generate a focused columnar acoustic beam perpendicular to the solid-liquid interface within the first stage. The duration of the first stage at the first power is less than a threshold, or the duty cycle of the first stage within one drive cycle is less than a threshold, to suppress the temperature of the ultrasonic device within a controllable temperature threshold and to prevent the ultrasonic device from 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 stage (or the duty cycle within a driving cycle) and the intensity of the first power. For example, a shorter first stage duration better suppresses temperature and secondary current, but the acoustic beam intensity is also lower (a shorter first stage duration means a shorter time for energy accumulation). Conversely, a higher first power results in a higher acoustic beam intensity, leading to a higher temperature rise in the ultrasonic device. Therefore, applying a higher first power and a shorter first stage not only yields a higher intensity acoustic beam but also effectively suppresses the temperature and secondary current. Thus, when real-time control of the acoustic beam intensity is required, the preferred approach is to use a shorter, fixed first stage (e.g., the duty cycle of the first stage within the cycle is fixed) and control the intensity of the generated acoustic beam by applying different first power values. A secondary approach is to apply the same first power value and adjust different first stage values ​​(e.g., the duty cycle of the first stage within the cycle) to control the intensity of the generated acoustic beam, or to simultaneously adjust both the first stage value and the first power to control the intensity of the generated acoustic beam.

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

[0046] 4) Regarding the first stage within the drive cycle: In the first stage of the drive cycle, the drive unit continuously outputs several signals. For example, when the signal generator outputs a 1GHz signal, assuming the duration of the first stage is 1 microsecond, the drive unit will output 1000 signals (1GHz * 1 microsecond = 1000) during this first stage time (1 microsecond). The power applied during the first stage time (1 microsecond) will be applied to these 1000 signals to drive the ultrasonic device. In the second stage of the drive cycle (corresponding to...) Figure 3 (Switch signal low level) No drive signal output.

[0047] In certain cases, such as when the first phase is executed only once and then the process ends, this is equivalent to or considered as executing only one drive cycle in this application, and therefore this situation is also within the scope of protection of this application.

[0048] 5) Driving device for special ultrasonic devices: such as Figure 4One embodiment is shown, including a control unit and a drive unit, the drive unit comprising a signal generator and a power amplifier. Its signal output principle can be found in [reference needed]. Figure 3 As shown.

[0049] The signal generator is used to generate high-frequency signals. The frequency of the original high-frequency signal it generates is the same as or approximately the operating frequency (or natural frequency) of the ultrasonic device used as a load. The waveform of the signal generator can be a rectangular wave (e.g.,...). Figure 3 The signals shown include square waves, sawtooth waves, sharp pulses (or triangular waves), stepped waves, sine waves, or half-waves. The output signal of the corresponding drive unit is modulated into rectangular waves, sawtooth waves, sharp pulses (or triangular waves), stepped waves, sine waves, or half-waves.

[0050] A power amplifier is used to amplify the signal to be output so that it can drive a high-performance ultrasonic device.

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

[0052] The acoustic beam and related technologies for driving ultrasonic devices to generate acoustic beams, as described above, can also be found in the relevant description 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 phenomenon caused by a sudden change in flow velocity in a liquid flow system. For example, when a valve in a pipeline suddenly closes or opens, 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 wave generated by the intermittent (e.g., pulsed) sound beam produced by driving an ultrasonic device in a liquid. It is easy to understand that the sound beam attenuates in a liquid; therefore, the strength of the micro-water hammer effect at a certain location in the liquid is related to the distance from that location to the ultrasonic device. The micro-water hammer effect described in this application refers to the area within which the micro-water hammer effect occurs.

[0055] In addition, due to the high focusing of the acoustic beam, the resulting 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 attenuated significantly), which is the aforementioned directional shock wave (i.e., the direction of the acoustic beam).

[0056] The scheme for achieving micro-water hammer effect based on acoustic beam provided in this application can control an ultrasonic device to intermittently generate a highly focused acoustic beam in a liquid, thereby forming a water hammer effect. The acoustic beam based on the water hammer effect has a stronger force than a continuous acoustic beam (i.e., one without water hammer effect). The acoustic beam based on the water hammer effect can be applied to drug delivery, cleaning, and manipulation of microparticles.

[0057] Drug delivery, for example, involves injecting liquids or substances in liquids into a target object using a sound beam with the water hammer effect, such as injecting it under the epidermis of a living organism. This application can be used for subcutaneous drug delivery, enabling devices such as syringes to deliver drugs to the skin of areas like the arm or buttocks. The drugs include therapeutic medications that are liquid or soluble in liquids, nutrients, etc., such as subcutaneous injections or subcutaneous nutrient supplies, such as those for the face or neck. Nutrients include cosmetic or skin-beneficial substances like hyaluronic acid, collagen, hyaluronic acid gel, or water. Due to the high focusing power of the sound beam, another application of this application is targeted skin staining, such as creating patterns on the skin (e.g., skin tattoos, skin branding).

[0058] Cleaning, for example, involves using a sound beam with the water hammer effect to clean the surface or epidermis of a material.

[0059] Manipulation of microparticles includes, for example, continuously applying a sound beam based on the water hammer effect to a microparticle (such as a cell) to test its mechanical properties, such as testing the impact resistance (magnitude of the force) and its durability (impact resistance, etc.). Other examples include altering the spatial position, shape, and structure of the microparticle (such as perforation of the microparticle surface membrane).

[0060] Furthermore, when the particles are cells, the manipulation of cells can also include, for example, stimulating cells with a sound beam based on the water hammer effect, so that the cells respond to the stimulus by activating mechanosensitive channels, reorganizing the cytoskeleton, activating signal transduction pathways, or changing secretory activity.

[0061] The solutions provided in this application will now be described in detail with reference to the accompanying drawings and embodiments.

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

[0063] The ultrasonic device generates 0.5-30 GHz ultrasonic waves when in operation, which 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. This directional fluid motion includes a focused columnar acoustic beam. The ultrasonic device is driven by a first power for at least one driving cycle, each driving cycle including a first stage and a second stage. In the first stage, the ultrasonic device is driven to generate 0.5-30 GHz ultrasonic waves, and in the second stage, the driving of the ultrasonic device is stopped. The magnitude of the first power causes the ultrasonic device to generate the acoustic beam during the first stage.

[0064] In addition, the duty cycle of the second stage in at least one drive cycle is adjusted to generate the acoustic beam intermittently, and the duration of the intermittent interval is greater than a threshold, at which the intermittently generated acoustic beam produces a micro water hammer effect.

[0065] In some embodiments, adjusting the duty cycle of the second stage in at least one drive cycle to intermittently generate the acoustic beam can be achieved by adjusting the duty cycle of the second stage in each drive cycle. See also... Figure 5 The example shown in 'a' is described below:

[0066] Assumption Figure 3 Under the shown output duty cycle drive signal, based on the fluid characteristics (flowability, viscosity, continuity), the generated acoustic beam is a continuous acoustic beam (a continuous acoustic beam means that there is no or minimal water hammer effect). See also Figure 5 As shown in Figure 'a', increasing the duty cycle of the second stage, while still ensuring the generation of an acoustic beam, allows for the formation of an intermittent acoustic beam to generate a micro-water hammer effect when the duty cycle of the second stage increases to a certain extent. In this case, the duration of each cycle output by the drive device remains constant; what changes is the distribution ratio between the first and second stages. The shorter the first stage, the less energy the ultrasonic device receives within 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 sufficient to generate an acoustic beam (too low an energy level makes it difficult to generate an acoustic beam).

[0067] In some embodiments, adjusting the duty cycle of the second stage in at least one drive cycle to intermittently generate a sound beam can be achieved by adjusting the duty cycle of the second stage in at least one of at least two consecutive drive cycles. See also... Figure 5 Examples b and c in the text are described below:

[0068] Figure 5 In the example shown by b, relative Figure 3 The output drive signal is modulated into a low-level signal every 2n cycles, thereby generating an intermittent acoustic beam to produce a micro water hammer effect.

[0069] Figure 5 In the example shown by c, relative Figure 3 The output drive signal is modulated into a low-level signal every 3n cycles, thereby generating an intermittent acoustic beam to produce a micro water hammer effect.

[0070] in, Figure 5 Compared to b, c generates micro water hammers at a lower frequency, and each micro water hammer has a longer acoustic beam duration, resulting in higher energy per micro water hammer.

[0071] In other embodiments, the generation of micro-water hammer can also be achieved through variable time intervals (or variable frequencies), for example, relative to... Figure 3 The output drive signal is modulated into a low-level signal in its second and fifth cycles.

[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 in at least one of the following ways: controlling the strength of the micro-water hammer effect by controlling the strength of a first power level; controlling the interval degree of the micro-water hammer effect by controlling the duty cycle of the second stage.

[0073] In some embodiments, the liquid environment is located within a cavity, the walls of which are provided with hollow needles extending outward, and the sound beam generated by the ultrasonic device is directed towards the hollow needles.

[0074] The hollow needle can influence the effective distance of the micro-water hammer effect and / or affect its directionality. For example... Figure 10 In the example shown, the hollow needle in the middle is directly facing the ultrasonic device. For information on the role of the hollow needle in the micro-water hammer effect, please refer to the following section. Figure 16 and Figure 17 Introduction.

[0075] In some embodiments, the ultrasonic devices and corresponding hollow needles are arranged in an array of multiple arrays to generate an array-like micro-water hammer effect. This makes it suitable for applying acoustic beams with a micro-water hammer effect to large-area targets. The ultrasonic devices can be discrete multiple devices, or they can be arranged as follows: Figure 14 Multiple ultrasound chips are integrated onto a single substrate; details can be found later. Figure 14 Description of the illustrated embodiment.

[0076] In some embodiments, the target object acted upon by the acoustic beam of the generated micro water hammer effect includes at least one of the following: a first particle, epidermis or surface, or tissue located within the range of the micro water hammer effect.

[0077] In some embodiments, the liquid environment further includes a second particle carried in the acoustic beam of the micro water hammer effect.

[0078] The second embodiment of this application provides a device for realizing the micro water hammer effect based on an acoustic beam, including the liquid environment and the ultrasonic device described in the first embodiment. The ultrasonic device can intermittently generate an acoustic beam to produce the micro water hammer effect based on any of the methods described in the first embodiment.

[0079] In some embodiments, the liquid environment is located in a cavity, the wall of which is provided with hollow needles extending outward, and the sound beam generated by the ultrasonic device is directed towards the hollow needles; the hollow needles are used to extend the action distance of the micro water hammer effect and / or maintain the directionality of the micro water hammer effect.

[0080] The third embodiment of this application provides a liquid delivery device based on the micro water hammer effect, comprising: a cavity having an open end; the wall of the cavity having an injection hole for injecting liquid into the cavity; a supersonic device disposed in the cavity; after the liquid is injected into the cavity, the supersonic device is placed in a liquid environment; and a sound beam with micro water hammer effect is generated in the direction of the cavity opening end based on any of the methods described in the first embodiment based on the sound beam to achieve the micro water hammer effect, so as to inject liquid into the skin that closes the opening end through the sound beam with micro water hammer effect.

[0081] In some embodiments, the position of the ultrasonic device from the cavity opening can be adjusted.

[0082] Based on the principles of any of the methods or devices in the first, second, and third embodiments described above, this application also provides a specific implementation example, namely, a drug delivery device based on the micro-water hammer effect provided in the fourth embodiment, which will be referred to below as an injection device. Figure 6 or Figure 7 The diagram shown and Figure 9The photograph of the actual object shown illustrates that the injection device based on the micro-water hammer effect in this embodiment may include:

[0083] A cavity 1 has an open end; the wall of the cavity 1 has a liquid injection hole 4 for injecting liquid into the cavity 1; a special ultrasound device 2 is disposed in the cavity 1, and after the liquid is injected into the cavity 1, the special ultrasound device 2 is placed in a liquid environment, and the special ultrasound device 2 is used to generate an intermittent sound beam 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 sound beam with the micro water hammer effect.

[0084] In some embodiments, the cavity 1 can be any shape, such as cylindrical, hemispherical, spherical, or bell-shaped. In some embodiments, the open end of the cavity 1 can contact the target object (e.g., skin) to seal the opening end of the cavity 1. In some embodiments, when the ultrasound device 2 is not activated, the design of the size of the open end of the cavity 1, when not in contact with the target object (e.g., skin), can also prevent the liquid inside the cavity 1 from flowing out due to the internal and external air pressure difference or the surface tension of the liquid.

[0085] In some embodiments, the ultrasonic device 2 may 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 ultrasonic device 2 faces the opening end of the cavity 1.

[0086] The injection hole 4 on cavity 1 is used for connecting 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 injection port 4 to inject liquid into the cavity 1. Alternatively, it can be a bottled container such as a medicine bottle that can be inserted into the injection port 4. For example, it can be directly inserted through the tubular opening end of the medicine bottle, or it can be connected to the injection port 4 through a conduit (such as a flexible tube or rigid tube). In other embodiments, the liquid supply device can also be an external liquid supply device connected through a conduit, which has a micro-pump to pump liquid into the cavity 1.

[0087] In some embodiments, the wall of the cavity 1 away from the opening has a through hole; a bracket 3, partially extending into the cavity 1, is fitted at the through hole, and the ultrasonographic device 2 is fitted at the end of the bracket 3 located inside the cavity 1. In some embodiments, the through hole for mounting the bracket 3 may also be located on the side wall of the cavity 1. In some embodiments, such as Figure 8 As shown, the injection hole 4 can also be located on the bracket 3.

[0088] In some embodiments, the bracket 3 is threadedly connected to the through hole 31. One end of the bracket 3, away from the ultrasonic device 2, is located outside the cavity 1. The threaded connection 31 allows the relative position of the bracket 3 and the cavity 1 to be adjusted, thus allowing the position of the ultrasonic device 2 within the cavity 1 to be adjusted. In some embodiments, the through hole is directly opposite the opening end (i.e., the axial direction of the through hole is directly opposite the opening end). By screwing the bracket 3 into or out of the through hole, the distance between the ultrasonic device 2 and the opening end can be adjusted. In some embodiments, the adjustable range of the distance between the ultrasonic device 2 and the opening end can be 0–2 cm. In other embodiments, when the through hole is not directly 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 into or out of the through hole, the position of the horizontal component of the ultrasonic device at the opening end is simultaneously adjusted while adjusting the distance between the ultrasonic device 2 and the opening end.

[0089] In some embodiments, the support 3 is tubular, with wires connecting the ultrasonic device 2 arranged inside the tube. In some embodiments, the portion of the support 3 located outside the cavity 1 can serve as a handheld part for operating the device of this embodiment; therefore, the shape of the portion of the support 3 located outside the cavity 1 can be made to facilitate handheld operation. When the support 3 is tubular, the ultrasonic device 2 and the tubular support 3 together form an ultrasonic probe.

[0090] In some embodiments, the driving device and power supply device for driving the ultrasonic device 2 can be independently arranged relative to the aforementioned structure (i.e., the part including the cavity 1 and the support 3), and the driving device and the ultrasonic device 2 are electrically connected through the aforementioned wires. A push-button switch, a touch switch, a drive power adjustment control, or a display screen may be provided on the handheld part, or these may be located at the external driving device and power supply device, wherein the driving device and power supply device can be assembled into a housing.

[0091] In some embodiments, the driving device (including a control unit) and power supply of the ultrasonic device 2 can be integrated into the aforementioned structure of the support 3, which serves as the handheld part, located outside the cavity 1, thereby making the device a handheld device. The corresponding handheld part can be equipped with mechanical (e.g., push-button) switches, touch switches, drive power adjustment controls (e.g., knobs), or displays, etc., through which the start and stop of the injection device, the driving mode of the ultrasonic device 2 (e.g., intermittent operation, continuous operation), and the driving power of the ultrasonic device 2 can be controlled. In some embodiments, the power supply includes a transformer and corresponding circuits (e.g., filtering, modulation modules, protection circuits, etc.), connected to external mains power; in other embodiments, the power supply includes a rechargeable battery and corresponding circuits (e.g., DC / AC, adjustment modules, charging circuits, protection circuits, etc.).

[0092] In some embodiments, the ultrasonic device 2 includes at least two ultrasonic chips arranged in an array on the same substrate, the at least two ultrasonic chips sharing electrodes on the substrate. This type of integration can reduce wires and energy loss due to line resistance, etc. Figure 14 An example is shown where a substrate has three ultrasonic chips (here, ultrasonic chips refer to the acoustic wave reflecting layer and piezoelectric layer located on the substrate). The upper electrodes of the piezoelectric layers of the three ultrasonic chips are connected to the same endpoint on the substrate, and the lower electrodes are also connected to the same endpoint. These two endpoints are used for external driving circuitry. Figure 14 Image a is a photograph taken under a microscope, and image b is a photograph of the actual object. The three claw-shaped objects in the images are electrodes, and the rectangular frames are the endpoints (gold fingers).

[0093] In other embodiments, the ultrasound device 2 includes: an array of relatively independent ultrasound devices 2, such as different ultrasound devices 2 composed of different ultrasound chips located on different substrates.

[0094] In some embodiments, when multiple ultrasonic chips are used, these chips may have identical parameters to achieve the same function or effect under the same drive. In other embodiments, these chips may have different parameters to achieve different functions or effects simultaneously under the same drive.

[0095] In some embodiments, when multiple ultrasonic chips are present, the arrangement of these chips (e.g., position and orientation) allows the generated acoustic beams with micro-water hammer effects to be parallel or divergent to increase the effective area; for example, the chips are arranged in an array on the same plane or on the same convex surface. In some embodiments, the acoustic beams with micro-water hammer effects generated by the arrangement of these chips (e.g., position and orientation) can converge to increase the effect on a particular point; for example, the chips are arranged in an array on the same concave surface.

[0096] The overall shape of the array composed of multiple ultrasonic chips or multiple ultrasonic devices 2 can be rectangular, ring-shaped, linear, or other shapes. For example, Figure 13 The example of an array of multiple ultrasound chips shown includes three ultrasound chips.

[0097] In some embodiments, such as Figure 8As shown, the wall of the cavity 1 also has vents 7. Vents 7 facilitate venting during liquid injection into the cavity 1 or venting during liquid injection into the subcutaneous tissue. In some embodiments, the vents 7 are micropores, with the pore size set to achieve air permeability but liquid impermeability, thus ensuring air permeability and reducing the possibility of liquid spillage from the cavity to the outside during use. In other embodiments, when the pore size of the vent 7 is not limited, the vent 7 location can also be addressed by applying a microporous elastic membrane to solve the problems of venting, venting, and preventing spillage. The elastic membrane can be applied to the outer or inner wall of the cavity 1 corresponding to the vent 7. In some embodiments, when it is desired that liquid overflow may occur when the device is in contact with the skin but the contact is not tight, the pore size of the vent 7 can be slightly larger, for example, when the device is used as a beauty and skincare device. In other embodiments, when it is desired that the device of this application does not overflow liquid when in contact with the skin, the size of the pore 7 is such that it can balance the liquid inside the cavity with other external air pressures, or the microporous elastic modulus is used to achieve a micro-balance of air pressure inside and outside the cavity 1, so that even when the contact is not tight, the possibility of liquid leakage is reduced when the ultrasound chip is not activated.

[0098] In some embodiments, the ultrasonic device 2 is further used to generate one or any combination of the following in the liquid environment: eddies, cavitation effects, thermal effects, jets, etc. Different effects of the ultrasonic device 2 can be achieved by adjusting the driving power, such as adjusting the period of the driving signal, the percentage of the driving level within a period, the power level, and the continuous duration of the drive. In some embodiments, when multiple ultrasonic chips are used, as mentioned above, different effects can be achieved under the same power drive when these chips have different parameters. When the ultrasonic device 2 generates eddies, the eddies acting on the skin can enhance the cleansing effect on the skin surface. When the ultrasonic device 2 generates cavitation bubbles, these bubbles enhance the cleansing effect on the skin surface. The cavitation effect removes oil, debris, and dust from the skin, effectively unclogging pores and cleansing the face. Furthermore, the cavitation effect softens the stratum corneum and accelerates its metabolism, restoring skin elasticity and providing a lifting and firming effect. It also opens intercellular spaces, increasing skin permeability and allowing cosmetic substances such as collagen and hyaluronic acid to penetrate the epidermis and reach the dermis, achieving transdermal delivery without causing skin trauma. Some of the ultrasonic energy generated by the ultrasonic device 2 is converted into heat, which accelerates blood circulation, improves metabolism, enhances local tissue nutrition, and strengthens enzyme activity. Because the power applied to the ultrasonic device 2 is low, typically not exceeding 10W, the thermal effect does not damage the skin. Additionally, when the ultrasonic device 2 generates a jet, the jet's intensity is less than that of a sound beam, allowing for effective skin cleansing.

[0099] In some embodiments, such as Figure 10As shown, the cavity 1 has a cover 8 at its open end, which closes the open end. The cover 8 has a hollow needle 81 extending outwards from the position opposite the ultrasonic device 2. The sound beam with micro-water hammer effect generated by the ultrasonic device 2 is directed towards the cavity of the hollow needle 81. In other embodiments, the hollow needle 81 can also be positioned on the cover 8 at a position not directly opposite the ultrasonic device 2. The hollow needle 81 can penetrate the skin, and different lengths of the hollow needle 81 will penetrate to different depths, making it easier to inject the sound beam into the subcutaneous tissue reached by the hollow needle 81. In some embodiments, the cover 8 and the cavity 1 are integrally formed, for example, by pressing the cover 8 and the cavity together to achieve an integral form. This integral form allows for better control of the distance between the ultrasonic device 2 and the hollow needle 81 during assembly. In other embodiments, the cover 8 and the cavity 1 are separately assembled, which facilitates the replacement of the cover 8 with different hollow needles 81. The hollow needle 81 can be a microneedle fabricated using high-precision 3D printing or micro / nano fabrication technology. In some embodiments, multiple hollow needles 81 can be arranged in an array. In some embodiments, the structure of the hollow needle 81 allows the liquid to be held within the cavity 1 by means of liquid tension when the ultrasonic device 2 is not in operation.

[0100] In some embodiments, hollow needles of different shapes can be used. For example, a hollow needle can be like... Figure 10 As shown, its inner diameter is cylindrical, meaning the inner diameter is the same in the extending direction. In other embodiments, the hollow needle can be as follows: Figure 16 or Figure 17 As shown, its inner diameter can be conical. The shape of the hollow needle, such as whether the inner diameter is cylindrical or columnar, its length, and the distance between the hollow needle and the ultrasonic device, will all have different effects on the sound beam.

[0101] In some embodiments, when the inner diameter of the hollow needle is conical, the inner diameter of the hollow needle 81 can gradually decrease along the direction away from the cavity 1. Based on this structure, the sound beam can be further focused and injected subcutaneously from the tip of the hollow needle 81. On the one hand, the hollow needle 81 structure reduces the direct transfer of sound beam energy to the external laminar fluid, which can enhance the local pressure of the sound beam with micro-water hammer effect, increase the effective distance of the micro-water hammer effect, limit the generation of eddies in the sound beam, and reduce power dissipation. However, on the other hand, the inner wall of the hollow needle 81 itself also generates resistance to the sound beam, which leads to some energy loss. Therefore, a comprehensive analysis is required.

[0102] The different apertures of the hollow needle 81 tip, the different lengths of the hollow needle 81, and the different distances between the ultrasonic device 2 and the hollow needle 81 it faces all have different effects on the effect of the sound beam being emitted from the needle tip. The above-mentioned 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 drug solution.

[0103] For example, when the inner diameter of the hollow needle 81 is conical, for different aperture diameters at the tip of the hollow needle 81: with a small aperture, the sound beam attenuates faster due to the smaller aperture at the outlet and the rapid reduction in aperture (one possibility is energy loss due to the resistance of the sound beam by the inner wall of the hollow needle 81), the pressure at the outlet is significantly lower, the effective distance is shorter, but the angle of the effective range (the angle of the jet ejected from the outlet) is larger (when the energy is insufficient to maintain high directivity, the divergence is more pronounced), reaching 45 degrees. As the aperture increases, the pressure at the outlet increases, the effective distance increases, and the angle of the effective range gradually decreases, resulting in better directionality. Figure 16 The outlet orifice diameter of the hollow needle 81 is shown.

[0104] For example, when the inner diameter of the hollow needle 81 is tapered, for different lengths of the hollow needle 81: with the same tip aperture, the longer the hollow needle 81, the more significant the acceleration effect on the sound beam, the better the directionality of the sound beam after passing through the hollow needle 81, and the smaller the diffusion angle. The selection of the length of the hollow needle 81 depends on the transdermal depth and the desired transdermal effect. In some embodiments, the length of the hollow needle 81 can be 50–2000 μm. Figure 17 The acceleration effect of hollow needles with needle lengths of 200µm and 300µm on the acoustic beam is shown. It can be seen that the acoustic beam with a needle length of 300µm has a longer range in the same time period compared to the acoustic beam with a needle length of 200µm. When it is an acoustic beam with a micro water hammer effect, the micro water hammer effect has a longer range.

[0105] For example, when the inner diameter of the hollow needle 81 is conical, for different distances from the hollow needle 81 to the ultrasonic device: the farther the hollow needle 81 is from the ultrasonic device, the less energy the sound beam entering the hollow needle 81 has, and the greater the final ejection angle from the outlet of the hollow needle 81 (when the energy is insufficient to maintain high directivity, the divergence is more pronounced).

[0106] In some embodiments, the effective range, effective area, and effective intensity of the acoustic beam generated when the ultrasonic device 2 operates in the range of 0.1–10 GHz, with a driving power of 0.1–100 W and a total pulse period of 10–2000 ms, have the following relationship: within 100 μm of the device surface, the effective area of ​​the acoustic beam is similar to the shape and area of ​​the device itself, and the point of maximum pressure also appears within this distance. When the distance is greater than 100 μm, the shape of the acoustic beam gradually tends to be circular, and the effective area increases while the effective intensity decreases. Based on this, the distance between the ultrasonic device 2 and the corresponding hollow needle 81 can be designed. In some embodiments, the distance between the ultrasonic device 2 and the corresponding hollow needle 81 is 0–2000 μm.

[0107] In some embodiments, the opening end of the cavity 1 has a cover that closes the opening end. The cover has a mesh surface. The direction of the sound beam of each ultrasonic device 2 in the cavity 1 can be directly aligned with a mesh hole in the mesh surface. The mesh surface structure can keep the liquid in the working cavity by means of liquid tension when the ultrasonic device 2 is not working. The mesh structure can also be used as an isolation to keep the contact part between the ultrasonic device 2 in the cavity 1 and the target object being injected at the required distance.

[0108] In some embodiments, the device provided in this application is fastened to the skin by means of straps or elastic bands, for example... Figure 6 In one example, the bottom of the cavity may have an outwardly extending edge, and the edge may have a hole 5 for mounting a Velcro strap 6. In other embodiments, the device may be pressed firmly against the skin by hand. In some embodiments, the opening end of the cavity 1 of the device may be smoothly designed at the point of contact with the skin to facilitate a tight fit when pressed against the skin. In some embodiments, the opening end of the cavity 1 at the point of contact with the skin may also be fitted or wrapped with a biocompatible elastic material, such as soft silicone or rubber, to further ensure sealing and reduce the possibility of liquid leakage inside the cavity 1.

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

[0110] In some embodiments, the different ratios of the first and second stages in each driving cycle of the ultrasonic device 2 during pulsed driving can achieve different pulse effects. The ratio of the first and second stages and the driving cycle duration can be adjusted accordingly to achieve a more pronounced micro-water hammer effect. The pressure generated by a conventional pulsed water jet is much greater than that generated by a continuous water jet. Furthermore, utilizing the fatigue effect of the target material, the periodic transient impact stress wave, compared to the stagnant pressure of a continuous water jet, allows the target material to reach its fatigue limit faster. This principle of water jets also applies to acoustic beams. Compared to continuous acoustic beams, intermittent acoustic beams generate a micro-water hammer effect with higher energy utilization efficiency, capable of generating high water pressure in a pulsed manner at lower liquid flow rates. As mentioned above, the parameters of the intermittent acoustic beam can be flexibly adjusted, including the pulse frequency (corresponding to the driving cycle), duty cycle (corresponding to the ratio of the first and second stages in the driving cycle), and distance from the material surface. Moreover, the micro-water hammer effect, combined with the focusing properties of the acoustic beam, can reduce the transmission of compressive stress on the target surface, 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 above-described injection devices (i.e., drug delivery devices) of this application can also be combined with low-frequency ultrasound. For example, a low-frequency ultrasound device can be provided in the aforementioned inlet portion, thereby enabling the low-frequency ultrasound and the ultra-high-frequency ultrasound device 2 to work simultaneously or at different times. The low-frequency ultrasound has low energy but a wide range and is responsible for treating large areas, while the ultra-high-frequency ultrasound has high energy and is responsible for treating specific areas. The cavitation effect of low frequency combined with the localized cavitation effect of high frequency increases the transdermal penetration speed.

[0112] In some embodiments, any of the above-described injection devices (i.e. drug delivery devices) of this application may also be used in conjunction with chemical penetration enhancers. For example, chemical penetration enhancers may be injected into the reservoir or applied to the skin. By interacting with lipids in the stratum corneum to change its arrangement structure, the drug's penetration ability is enhanced by weakening the barrier function of the stratum corneum without causing significant damage to cells.

[0113] In some embodiments, any of the above-described injection devices (i.e., drug delivery devices) of this application can also be combined with radio frequency, microcurrent, and / or LED lights, for example, by providing a radio frequency device, a microcurrent needle, and / or an LED light in the aforementioned delivery section. These three can serve as auxiliary methods, with the primary effects being wrinkle reduction and skin condition improvement. For example, utilizing the penetrability of radio frequency and / or microcurrent, the device penetrates the epidermis to act on the dermis, heating the dermal tissue through the LED thermal effect, stimulating fibroblasts to synthesize collagen and elastin. This integrates wrinkle reduction and skin condition improvement with transdermal functionality.

[0114] In some embodiments, any of the above-described injection devices (i.e. drug delivery devices) of this application may also be combined with electroporation, for example, by providing an electroporation electrode in the above-described inlet portion, using electrical pulses to stimulate the skin or subcutaneous tissue, opening the keratin bilayer or the intercellular spaces of skin cells, forming an input channel for the active ingredient, and realizing transdermal delivery of cosmetic substances.

[0115] This application also provides a cosmetic device, including any of the above-described injection devices (i.e. drug delivery devices) and various optional embodiments, which will not be described in detail here.

[0116] The present application will be further described below with reference to specific embodiments. In this embodiment, the characteristics of the ultrasonic device generating intermittent sound beams in liquid to produce micro water hammer effect (also known as the characteristics of sound beams at the solid-liquid interface) are first studied. Then, the characteristics of sound beams combined with microneedle structures are discussed. Finally, an example of its application in an injection device is discussed.

[0117] The characteristics of ultrasonic devices generating acoustic beams with micro-water hammer effect in liquids: The intermittent acoustic beams of pentagonal, circular, and annular ultrasonic devices were simulated and some experiments were conducted. The conclusions are as follows:

[0118] 1) The effective range, area, and intensity of the acoustic beam generated by a supersonic device within a frequency range of 0.1–10 GHz, a power range of 0.1–100 W, and a total pulse period of 1–2000 ms exhibit the following relationship: Within 100 μm of the supersonic device surface, the effective area of ​​the acoustic beam is similar to the shape and area of ​​the device itself, and the point of maximum pressure also appears within this distance. When the distance exceeds 100 μm, the shape of the acoustic beam gradually tends to be circular, the effective area increases, and the intensity decreases. (See also...) Figure 11 The diagram shows simulations of pulsed acoustic beams generated by several special ultrasonic devices, and Figure 12 The image shows an experimental photograph illustrating the increase in the area of ​​the acoustic beam's effect as the distance increases.

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

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

[0121] Here, dynamic pressure refers to the pressure exerted by a fluid due to its velocity, reflecting the fluid's kinetic energy. The characteristic of dynamic pressure is that it changes 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 ultrasonic device accelerates the fluid, forming an acoustic beam. This beam reaches its maximum velocity at a certain point after acceleration by the acoustic pressure field, at which point its kinetic energy is at its maximum. Further upward, it decelerates to some extent due to liquid resistance, and upon impacting the solid wall at the solid-liquid interface, its velocity drops to zero. At this point, all kinetic energy is converted into pressure potential energy upon impact with the wall. By calculating the kinetic energy at the maximum velocity, the pressure potential energy upon impact with the wall can be determined, allowing for the calculation of the pressure and force at that point. The calculations of pressure and force based on the maximum velocity are shown in the table below:

[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 has a water hammer effect and its energy utilization efficiency is higher than that of the continuous acoustic beam.

[0125] The short-pulse, high-speed, discontinuous acoustic beam generated in this application can achieve rapid, multiple, and high-pressure continuous impacts, thus creating a water hammer effect. From another perspective, this application is equivalent to a miniature water hammer generator. The initial pressure of the water hammer effect is much higher than the steady-state pressure; therefore, the pulsed output can significantly increase the pressure and improve transdermal efficiency. The principle behind the water hammer effect, where the initial pressure is much higher than the steady-state pressure (such as a continuous acoustic beam), is explained below:

[0126] The water hammer pressure in the initial stage can be derived based on Bernoulli's equation, which 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), approximately 1000 kg / km². 3 Where c is the wave velocity of the fluid (water), approximately 1400 m / s in the pipe, and v is the velocity of the fluid (water). Since water hammer pressure is composed of a discontinuous sound beam, the formula for water hammer pressure, derived from Bernoulli's equation, is: ΔP = ρ·c·Δv, where Δv is the change in water velocity (which can be understood as the velocity change between two sampling points). For example, if Δv is 0.5 m / s at a certain location in the experiment, then the water hammer pressure at that location in the experiment is ΔP = 1000 kg / m². 3 1400m / s 0.5m / s = 700kPa.

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

[0128] In further experiments, the initial pressure at different distances relative to the interface of the ultrasonic device was calculated. When the ultrasonic device was driven by 16W, the initial pressure within a distance of 1mm was in the MPa range. The initial pressure gradually increased as the distance decreased and was much greater than the pressure during the stagnant phase.

[0129] As shown above, high-pulse (i.e. intermittently generated) acoustic beams exhibit a water hammer effect, have higher energy utilization efficiency than continuously driven acoustic beams, and generate pressures far exceeding those of continuous acoustic beams.

[0130] 5) Based on the distance between the ultrasound device and the skin and the power level, the area of ​​skin that can be treated can range from 0.1 mm^2 to 10 mm^2.

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

[0132] like Figure 13 A simulation of pulsed acoustic beams generated by an array of three ultrasonic devices (corresponding to water hammer effect) is shown. Figure 15 A single ultrasonic device and Figure 13 The diagrams shown depict the interface treatment of three ultrasonic devices. Specifically, they characterize the interface treatment area of ​​a single ultrasonic device and multiple ultrasonic devices at the same power. The size of the treatment area at different heights from the interface is characterized by photographing the shape of red fluorescent particles (5 μm) adhering to the interface after the ultrasonic devices are turned on and then blown away. The results show that, at the same driving power, the treatment area of ​​multiple ultrasonic devices is significantly increased compared to a single device. The diagram shows three ultrasonic devices, with the treatment area increased by approximately three times, thus increasing the effective area. These three ultrasonic devices are driven by a single driving module (i.e., one driving three), meaning that with the same driving module and the same driving power, the treatment area is increased by approximately three times, thereby improving power utilization.

[0133] 7) Microneedle structures, such as hollow needles with tapered inner diameters that increase in the direction directly facing the ultrasonic device, can enhance the local pressure of the acoustic beam, increase its effective distance or diffusion angle, limit eddy current generation, and reduce power dissipation. Simulations verified that different apertures and lengths of the hollow needle tip have different effects on the acoustic beam exiting from the needle tip. (See also...) Figure 16 and Figure 17 As shown.

[0134] 8) By using a microneedle structure—a hollow needle with an inner diameter that increases in the direction directly opposite the ultrasonic device—the effect of the acoustic beam can be adjusted. (See also...) Figure 18 ,in Figure 18 Figure a shows a photograph and schematic diagram of the acoustic beam generated using a 200μm long microneedle, and Figure b shows a photograph and schematic diagram of the acoustic beam generated using a 400μm long microneedle. The outlet diameter of both microneedles is 60μm. The ultrasonic device is located at the top of the figure, generating an acoustic beam downwards. The microneedles are positioned directly below the ultrasonic device for the experiment.

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

[0136]

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

[0138]

[0139] Based on the above usage data, the following preliminary conclusions can be drawn regarding the use of hollow needles with a cylindrical inner diameter:

[0140] a. Comparing the acoustic beam passing through the microneedle with that not passing through the microneedle: the jet velocity is slower, but the effective area of ​​the jet is wider. The main reason is that some of the acoustic beam does not enter the microneedle, resulting in energy loss, and energy loss is also caused by the inner wall of the microneedle.

[0141] b. The jet speed and jet 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, the farther the microneedle is from the ultrasonic device, the less acoustic beam enters the microneedle, and the slower the jet velocity after passing through the microneedle. However, the jet angle is larger, making it more suitable for large-area diffusion drug delivery.

[0142] c. Comparison Figure 18 In the data of a and b above or the experimental results, under the condition that the distance from the 400μm microneedle to the ultrasonic device is the same, the jet angle of the sound beam after it is ejected from the microneedle does not change much, but the jet speed is slower when using the 400μm microneedle compared to the 200μm microneedle.

[0143] Hollow needles with different structures (length, shape) and different distances from ultrasonic devices produce different effects on the sound beams ejected from them. Therefore, based on this, corresponding hollow needle structures or distances from ultrasonic devices can be designed to achieve different speeds and angles of liquid (such as drugs) ejected from the hollow needles, thus enabling different forms of drug delivery.

[0144] Another experiment in this application is as follows: A special ultrasound device was used to perform transdermal treatment on the backs of shaved mice. The solution used was 2 mmol of rhodamine staining solution. In the experimental group, the special ultrasound device was turned on at a power of 8W for 10 minutes, while in the control group, only the solution was used for immersion. This was to test the transdermal effect of the device on small molecules. After treatment, the treated sites in both groups were dissected, 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 perform labeling). Figure 19 As shown in the experimental results, both sections in the experimental group exhibited a certain degree of transdermal penetration, especially the first section, where the rhodamine stain had penetrated the epidermis and reached the dermis and subcutaneous tissue layers. However, the control group only showed fluorescence where the rhodamine reagent was applied to the epidermis, with almost no fluorescent material visible in deeper layers. This demonstrates that rhodamine itself has difficulty penetrating the mouse epidermis, and that the addition of a special ultrasound device can improve its permeability.

[0145] In another set of experiments in this application, a special ultrasound device was used to perform transdermal treatment on the backs of shaved mice, mainly to explore the differences in transdermal absorption of molecules of different sizes, as follows:

[0146] Transdermal Experiment A: Solution used: 1% FITC-dextran solution, molecular weight: 3-6kJ; ultrasonic probe operating intensity: 4W; pulse output cycle: 50ms / 200ms, 15min. Experimental conclusion: Low molecular weight substances exhibit significant transdermal penetration under the action of acoustic fluid. Different transdermal depths and effects can be achieved by controlling the power, distance, and time.

[0147] Transdermal Experiment B: Solution used: 1% FITC-dextran solution, molecular weight: 40kJ; Ultrasonic probe operating power: 8W; Pulse output cycle: 50ms / 200ms, 15min. Experimental conclusion: Medium molecular weight substances can penetrate smoothly, but may cause skin damage. Appropriate control of device power, distance from the skin, and treatment time is necessary.

[0148] Transdermal Experiment C: Solution used: 0.8% FITC-dextran solution, molecular weight: 250kJ; ultrasonic probe operating intensity: 8W; pulse output cycle: 50ms / 200ms, 15min. Experimental conclusion: High molecular weight substances do not show obvious permeation phenomenon in short-term treatment and need to be combined with other methods (such as microneedles) to achieve transdermal transmission of high molecular weight substances.

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

[0150] The drug delivery protocol provided in this application enables non-invasive transdermal delivery of substances without causing skin trauma. When using an array of ultrasonic devices, it can also achieve rapid treatment of large areas of skin. The precise, high-speed acoustic jet or beam and the cavitation of the ultrasonic devices possess excellent directionality and regionality, allowing for precise control of the transdermal treatment area; the treatment is uniform and controllable, gentle and controlled, preventing issues such as the accumulation and clumping of cosmetic substances. When designed as a handheld device, it is convenient to use and does not require a specific location. Furthermore, its high degree of integration allows for integration with other cosmetic products based on different principles (such as radio frequency, microcurrent, LED lights, and ultrasound), offering multiple modes for user convenience.

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

[0152] This application also provides corresponding cosmetic methods, which are implemented using the above-described cosmetic device or the above-described injection device, or any of their optional embodiments, and will not be described in detail here.

[0153] In the several embodiments provided in this application, it should be understood that the disclosed apparatus and methods are not limited to the above embodiments and can be implemented in other ways. For example, the apparatus embodiments described above are merely illustrative. For instance, the division of units is only a logical functional division, and in actual implementation, there may be other division methods. For example, multiple units or components may be combined or integrated into another system, or some features may be ignored or not executed. Furthermore, the coupling or direct coupling or communication connection shown or discussed may be through some interfaces; the indirect coupling or communication connection between apparatuses or units may be electrical, mechanical, or other forms.

[0154] The units described as separate components may or may not be physically separate. 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 the units can be selected to achieve the purpose of this embodiment according to actual needs.

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

[0156] In the above description, the labels of the steps involved, such as S10, S20, etc., do not mean that the steps will necessarily be executed. The order of the steps can be interchanged or executed simultaneously if permitted.

[0157] The term "comprising" as used in the specification and claims should not be construed as limiting itself to what follows; it does not exclude other elements or steps. Therefore, it should be interpreted as specifying the presence of the mentioned feature, integral, step, or component, but does not exclude the presence or addition of one or more other features, integrals, steps, or components, or groups thereof. Thus, the statement "device comprising means A and B" should not be limited to a device consisting solely of components A and B.

[0158] The terms "an embodiment" or "an embodiment" as used in this specification mean that a particular feature, structure, or characteristic described in conjunction with that embodiment is included in at least one embodiment of this application. Therefore, the terms "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 will be apparent to those skilled in the art from this disclosure.

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

Claims

1. A method for realizing micro-water hammer effect based on acoustic beam, characterized in that, include: Liquid environment; Ultrasonic device, which generates 0.5-30 GHz ultrasonic waves when in operation, which 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, the directional fluid motion including a focused columnar sound beam; The ultrasonic device is driven to operate for at least one driving cycle with a first power. Each driving cycle includes a first stage and a second stage. In the first stage, the ultrasonic device is driven to operate and generate ultrasonic waves of 0.5-30 GHz. In the second stage, the driving of the ultrasonic device is stopped. The magnitude of the first power is such that the ultrasonic device generates the acoustic beam during the first stage. The duty cycle of the second stage in at least one drive cycle is adjusted to intermittently generate an acoustic beam, and the duration of the intermittent interval is greater than a threshold, at which the intermittently generated acoustic beam produces a micro water hammer effect.

2. The method according to claim 1, characterized in that, The adjustment of the duty cycle of the second stage in at least one drive cycle to intermittently generate an acoustic beam includes at least one of the following: Adjust the duty cycle of the second stage in each drive cycle; For at least two consecutive drive cycles, adjust the duty cycle of the second stage of at least one of the drive cycles.

3. The method according to claim 1 or 2, characterized in that, The micro water hammer effect can be controlled by at least one of the following methods: The strength of the micro-water hammer effect is controlled by the strength of the first power. The interval 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 1-3, characterized in that, The liquid environment is located in a cavity, the wall of which is provided with hollow needles extending outward, and the sound beam generated by the ultrasonic device is directed towards the hollow needles. The hollow needle extends the effective distance of the micro-water hammer effect and / or maintains the directionality of the micro-water hammer effect.

5. The method according to claim 4, characterized in that, The ultrasonic device and the corresponding hollow needle are arranged in an array of multiple units to generate an array of micro water hammer effects.

6. The method according to any one of claims 1-5, characterized in that, Also includes: The target objects acted upon by the acoustic beam of the micro water hammer effect include at least one of the following: a first particle, epidermis or surface, or tissue located within the range of the micro water hammer effect; The liquid environment includes a second particle, which is carried in the acoustic beam generated by the micro-water hammer effect.

7. A device for realizing micro-water hammer effect based on acoustic beam, characterized in that, include: Liquid environment; Ultrasonic device, which generates 0.5-30 GHz ultrasonic waves when in operation, which 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, the directional fluid motion including a focused columnar sound beam; The ultrasonic device is driven by a first power to operate in at least one driving cycle, each driving cycle including a first stage and a second stage, wherein the ultrasonic device is driven to generate ultrasonic waves of 0.5-30 GHz in the first stage, and the driving of the ultrasonic device is stopped in the second stage; wherein the magnitude of the first power causes the ultrasonic device to generate the acoustic beam in the first stage. The duty cycle of the second stage in at least one drive cycle is adjusted to intermittently generate an acoustic beam, and the duration of the intermittent interval is greater than a threshold, at which the intermittently generated acoustic beam produces a micro water hammer effect.

8. The apparatus according to claim 7, characterized in that, The liquid environment is located in a cavity, the wall of which is provided with hollow needles extending outward, and the sound beam generated by the ultrasonic device is directed towards the hollow needles.

9. A liquid supply device based on the micro-water hammer effect, characterized in that, include: A cavity having an open end; The cavity has injection holes on its walls for injecting liquid into the cavity; The cavity is equipped with a special ultrasound device. After liquid is injected into the cavity, the special ultrasound device is placed in a liquid environment. Based on the method of realizing micro water hammer effect based on acoustic beam as described in any one of claims 1-6, an acoustic beam with micro water hammer effect is generated toward the opening end of the cavity, so as to inject liquid into the skin that closes the opening end through the acoustic beam with micro water hammer effect.

10. The apparatus according to claim 9, characterized in that, The position of the ultrasonic device from the opening of the cavity can be adjusted.

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