CN118649318A - A breath-driven adjustable atomization volume atomizer driving device and method - Google Patents

Abstract

The invention discloses a breath-driven adjustable atomization volume atomizer driving device, comprising an atomizer, a human mouth and throat model, a filtering device and a vacuum pump. The atomizer generates a liquid mist aerosol driven by an excitation signal, and multiple filtrations are performed in sequence through a bubble absorption tube, a slag discharge filter and a membrane filtration unit in the filtering device located between the human mouth and throat model and the vacuum pump. The tail end of the filtering device is connected to the vacuum pump through a flow meter. A method of use is also provided, comprising placing an atomized solution in a medicine cup of the atomizer; collecting the user's inhalation flow at a certain frequency through a flow sensor; and calculating the corresponding required atomization volume according to the real-time flow through a control module; then the control module outputs a corresponding driving signal; the driving circuit amplifies the driving signal to drive the atomizing sheet, so that the atomizer operates at an optimal atomization volume. The invention improves the delivery efficiency of the drug aerosol in the human respiratory tract and improves the user experience during inhalation therapy.

Description

A breath-driven adjustable atomization volume atomizer driving device and method

Technical Field

The invention relates to the technical field of atomizers for inhalation therapy, and in particular to a breathing-driven atomizer driving device and method with adjustable atomization volume.

Background Art

With the development of science and technology, inhalation therapy is increasingly used to treat respiratory diseases such as chronic obstructive pulmonary disease (COPD) and asthma. By inhaling drugs in the form of tiny particles or aerosols, the drugs can directly act on the target organs. The mesh nebulizer is a common inhalation device. Its principle is to connect a perforated metal sheet with an oscillator, and produce resonance under a certain frequency of voltage and current drive, so that the drug solution is squeezed out of the mesh to form a drug aerosol. It is widely popular in my country for its advantages such as low drug residue and portability.

However, the efficacy of nebulized inhalation is affected by the nebulizer atomization volume, atomized droplet size, and real human breathing patterns. How to improve drug delivery efficiency is a research problem that needs to be overcome in this field, especially in terms of the impact of individual differences in breathing patterns on drug delivery. When a single atomized amount of drug aerosol is inhaled by different people, its delivery efficiency may vary greatly. Therefore, the concept of personalized medicine has been proposed, and how to optimize treatment methods for different subjects is a major research direction in this field.

In view of this, it is indeed necessary to design a nebulizer drive system that can adjust the atomization volume in real time according to the respiratory flow rate, so that the nebulizer can adapt to the breathing patterns of different people when delivering drugs and effectively improve the delivery efficiency.

Summary of the invention

The present invention provides a breath-driven adjustable atomization volume nebulizer driving device and method, which solves the problem that the nebulizer cannot maintain the optimal atomization volume according to the change of the patient's respiratory flow rate during actual atomization inhalation treatment.

To achieve the above-mentioned purpose, the present invention provides the following technical solutions: a breath-driven adjustable atomization amount atomizer driving device, characterized in that it includes an atomizer, a human mouth and throat model, a filter device and a vacuum pump, the atomizer is used as a device for holding atomized solution, the atomizer includes a medicine cup, an atomizing sheet, a gasket and an inlet structure, and generates a liquid mist aerosol with a certain atomization amount under the drive of an excitation signal, the human mouth and throat model is located on one side of the atomizer, and the upper end of the human mouth and throat model is connected to one end of the atomizer, the human mouth and throat model is configured to simulate the mouth and throat structure of a real human body, so as to serve as the main part for studying the deposition of droplets in the human body, and the filter device is located between the human mouth and throat model and the vacuum pump; wherein, if it is for a very high-end demand of a specific patient, by scanning the mouth and throat respiratory tract of the patient, the human mouth and throat model shown in Figure 2 is used to perform experiments using the patient's respiratory tract structure 3D printing. If it is for an unknown ordinary person, the average mouth and throat model of the population is used to determine the experimental results.

The filtering device includes a bubble absorption tube, a slag discharge filter and a membrane filtration unit, which are connected to the lower end of a human mouth and throat model through the upper end of the filtering device, and the bubble absorption tube, the slag discharge filter and the membrane filtration unit are sequentially connected between the human mouth and throat model and a vacuum pump. The filtering device is used to capture droplets escaping from the human mouth and throat model. The bubble absorption tube, the slag discharge filter and the membrane filtration unit perform primary filtration, secondary filtration and tertiary filtration respectively. The tail end of the filtering device is connected to the vacuum pump through a flow meter, and the vacuum pump is configured to draw liquid mist aerosol into the experimental device at a constant suction flow rate.

Preferably, the bubble absorption tube, the slag discharge filter and the membrane filter are connected to each other in sequence, and the airflow coming out of the bubble absorption tube is subjected to secondary filtration by the slag discharge filter to capture droplets in the airflow, and at the same time, the airflow is subjected to tertiary filtration by the membrane filtration unit to completely capture residual atomized droplets.

Preferably, a nebulizer driving system is provided in the driving device, and the nebulizer driving system includes a flow sensor, a control module and a driving circuit. The real-time data flow during the user's breathing process is collected by the flow sensor installed on one side of the nebulizer. The control module outputs a corresponding driving signal according to the flow value to change the nebulizer atomization amount. The driving circuit is connected to the signal output end of the control module to amplify the driving signal generated by the control module; the signal output end of the driving circuit is connected to the nebulizer, and the nebulizer generates high-frequency vibration through the driving force provided by the driving circuit, so that the solution in the medicine cup is atomized and sprayed out.

Preferably, the atomizer drive system also includes a power module and a transformer module. The power module is respectively connected to the power ports of the flow sensor, the control module and the drive circuit. The transformer module is located between the power module and the power supply module. After being transformed by the transformer module, the transformer is connected to the flow sensor, the control module and the drive circuit to provide working power therefor.

The present invention also provides a method for using a breath-driven adjustable atomization amount atomizer driving device, comprising the following steps:

Step 100, placing the atomized solution in the atomizer medicine cup;

Step 101: Detect the real-time flow rate of the user during breathing through a flow sensor;

Step 102, the control module calculates the required atomization amount according to the flow value returned by the flow sensor and the optimal atomization amount/inhalation flow ratio determined by the experiment, and generates a corresponding PWM signal waveform according to the relationship between the PWM duty cycle and the atomization amount;

Step 103, the control module then outputs a corresponding driving signal;

Step 104: The driving circuit amplifies the driving signal to drive the atomizing sheet, so that the atomizer operates at an optimal atomization amount; wherein the optimal atomization amount is determined by the lowest point of the deposition ratio.

Preferably, in step 100, the nebulizer medicine cup is a chamber for holding the nebulized solution, the chamber includes any suitable closed or open chamber, the nebulized solution includes a drug portion and a fluorescent substance portion for measuring the deposition amount, and the nebulized solution drops into the human mouth and throat model under the suction of a vacuum pump; after a period of time, the nebulizer and the vacuum pump are turned off; the fluorescent solution deposited in various parts is washed out; the mass of the droplets deposited in various parts is measured; finally, the deposition ratio of the liquid mist aerosol in the human mouth and throat model is calculated by the following relationship:

Where _m0 is the mass of droplets deposited in the human mouth and throat model, and _mtotal is the total mass of droplets captured in each part.

Preferably, in step 101, the flow sensor collects data at a frequency of 10 times/second. In actual use, the user's inhalation flow is 0-30 L/min, and the maximum range of the flow sensor should be greater than or equal to 35 L/min.

Preferably, in step 102 and step 103, the instantaneous inhalation flow of the user is read by the flow sensor. If the flow is less than 0.1 L/min, the system does not work; if the flow is greater than 0.1 L/min, the control module calculates the required atomization amount according to the flow value returned by the flow sensor and the optimal atomization amount/inhalation flow ratio determined by the experiment. The control module is a signal generating device for receiving and generating signals. The control module generates a PWM drive signal corresponding to the current required atomization amount according to the relationship between the PWM duty cycle and the atomization amount.

1) The atomization volume of the atomizer is calculated by the following formula:

Wherein, m ₁ and m ₂ are the total mass of the atomizer and solution before and after atomization, respectively, and t is the atomization time;

2) The relationship between duty cycle and atomization amount is fitted by the following formula:

Duty＝55.17-113.18x+671.36V _n ² (3)

The goodness of fit ^R2 is 0.97.

Preferably, in step 104, the driving circuit includes any suitable power signal amplifying device, and the driving circuit amplifies the driving signal to a certain multiple to drive the atomizing plate to generate liquid mist aerosol.

Compared with the prior art, the present invention has the following beneficial effects: the present invention can measure the optimal atomization mass flow value at each moment in an inhalation waveform, and the atomizer driving system can automatically adjust the atomization amount according to the inhalation flow, making the atomization inhalation treatment more humane, and can adapt to the breathing patterns of patients of different ages, genders, and health conditions, and improve the delivery efficiency of drug aerosols in the human respiratory tract; in addition, the driving system of the present invention uses automated means to adapt to the patient's breathing pattern throughout the operation, without the need for the patient to cooperate, thereby improving the user experience during inhalation treatment. At the same time, the atomization amount in the present invention changes with the inhalation waveform, rather than a switching amount.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings are used to provide further understanding of the present invention and constitute a part of the specification. They are used to explain the present invention together with the embodiments of the present invention and do not constitute a limitation of the present invention.

In the attached picture:

FIG1 is a flow chart of a method for using a breath-driven nebulizer with adjustable atomization volume according to the present invention;

FIG2 is a schematic diagram of the structure of a measuring device according to some embodiments of the present invention;

FIG3 is a schematic diagram of the structure of a measuring device according to some other embodiments of the present invention;

FIG4 is a schematic structural diagram of a breath-driven adjustable atomization amount atomizer driving device of the present invention;

FIG5 is a schematic diagram showing the meaning of the duty cycle of the present invention;

Numbers in the figure: 1. Atomizer; 2. Human mouth and throat model; 3. Bubble absorption tube; 4. Slag discharge filter; 5. Membrane filtration unit; 6. Flow meter; 7. Vacuum pump.

DETAILED DESCRIPTION

The preferred embodiments of the present invention are described below in conjunction with the accompanying drawings. It should be understood that the preferred embodiments described herein are only used to illustrate and explain the present invention, and are not used to limit the present invention.

In this field, the delivery efficiency of drugs in the form of liquid mist aerosol in the human respiratory tract is mainly affected by gravity sedimentation and inertial collision. Among them, gravity sedimentation is related to the size of aerosol particles, and inertial collision can be described by inertial parameters, as shown in the following formula:

IP＝ρ _d ² d _d ² Q

Where ρ _d is the droplet density, d _d is the initial droplet diameter, and Q is the suction flow rate.

For a single nebulizer, the density of the atomized droplets is basically constant with the initial diameter. Therefore, the inhaled air flow rate is the main factor affecting the deposition of liquid mist aerosol through inertial collision.

Ding Ting et al. have published a study on the deposition efficiency of sodium chloride liquid mist aerosol in an idealized mouth-throat model under different inspiratory flow rates (Evaporation Affects the In Vitro Deposition of Nebulized Dropletin an Idealized Mouth-Throat Model). They found that the deposition rate of liquid mist aerosol in the mouth-throat model changes in a "U"-shaped curve pattern with the increase of inspiratory flow rate, which first decreases and then increases. They also analyzed that under low flow rates, the evaporation of droplets is the reason for the increase in deposition rate. This study reveals the variation of the deposition ratio of liquid mist aerosol produced by the nebulizer in the mouth-throat under different inspiratory flow rates under a single nebulization volume. In the actual nebulization inhalation process, although the existing nebulizer can change the nebulization volume by adjusting the nebulizer gear, it still delivers drugs with a single nebulization volume, and the patient's respiratory flow rate changes over time, so it is impossible to keep the drug aerosol delivery efficiency at the optimal level.

In view of the above problems, according to one aspect of the present application, the present application provides a method for using a nebulizer that is driven by breathing and automatically adjusts the amount of atomization according to the inhalation flow rate. The method uses a flow sensor to collect real-time flow during the user's breathing process, and the control module outputs a corresponding drive signal according to the flow value to change the amount of atomization of the nebulizer 1, thereby improving the delivery efficiency of the drug aerosol. Specifically, for a certain inhalation flow collected by the flow sensor, the control module calculates the amount of atomization required for the flow according to the optimal atomization amount/inhalation flow ratio obtained in some embodiments of the present application. Subsequently, the relationship between the pwm duty cycle and the amount of atomization obtained by the control module generates a corresponding pwm signal, which is amplified by the drive circuit and drives the atomizer to atomize the solution with the required amount of atomization. With the change of the inhalation flow rate, the atomization amount of the nebulizer 1 will also change, and the nebulizer 1 always maintains a high delivery efficiency for the delivery of drug aerosols.

As shown in FIG1 , the present application provides a method for using a nebulizer that is driven by breathing and automatically adjusts the amount of nebulization according to the inspiratory flow rate, which includes the following steps:

Step 100, placing the atomized solution in the atomizer medicine cup;

The nebulizer medicine cup is a chamber for holding the nebulized solution, and the chamber can be any suitable closed or open chamber in the art. The nebulized solution can be any suitable drug solution in the art, for example, but not limited to, a 0.9% sodium chloride aqueous solution. In some embodiments, the nebulized liquid in the medicine cup contains a drug portion and a fluorescent substance portion for measuring the deposition amount.

Step 101, a flow sensor collects the user's inhalation flow at a certain frequency;

The flow sensor may be any suitable flow data acquisition device in the art, and the data acquisition frequency may be, but is not limited to, 10 times/second. In actual use, the user's inhalation flow is generally 0-30L/min, and the maximum range of the flow sensor should be greater than or equal to 35L/min to ensure that the flow reading is true and reliable and avoid reading errors due to insufficient range.

Step 102, the control module calculates the required atomization amount according to the real-time flow rate;

Step 103, the control module outputs a corresponding driving signal;

The control module can be any suitable programmable signal generating device in the art that can receive and generate signals, such as, but not limited to, an Arduino development board. In actual use, the control module reads the data collected by the flow sensor, processes the data according to the control program, and then generates a corresponding PWM drive signal.

Step 104, the driving circuit amplifies the signal to drive the atomizer sheet, so that the atomizer 1 operates at an optimal atomization amount;

The driving circuit may be any suitable power signal amplifying device in the art. In actual use, the driving circuit amplifies the driving signal to a certain multiple to drive the atomizing sheet to generate liquid mist aerosol.

As shown in FIG2 , some embodiments of the present application use an experimental device for measuring the deposition ratio of a liquid mist aerosol in a human mouth and throat model 2, which comprises: a nebulizer 1, a human mouth and throat model 2, a filtering device, and a vacuum pump 7. The nebulizer 1 is a device for holding a nebulized solution, which comprises a medicine cup, a nebulizer sheet, a gasket, and an inlet structure, and generates a liquid mist aerosol with a certain atomization amount under the drive of an excitation signal. The human mouth and throat model 2 is configured to simulate the mouth and throat structure of a real human body, so as to serve as the main part for studying the deposition of droplets in the human body. The filtering device comprises a bubble absorption tube 3, a slag discharge filter 4, and a membrane filter unit 5, which are used to capture droplets escaping from the human mouth and throat model 2. The vacuum pump 7 is configured to draw the liquid mist aerosol into the experimental device at a constant inhalation flow rate. The device is a simple and reliable device for measuring the deposition ratio of a liquid mist aerosol in a human mouth and throat model 2.

The atomizer 1 may be any suitable atomizer 1 in the art without being limited thereto.

The atomization amount of the nebulizer 1 is: 0.1g/min, 0.2g/min, 0.3g/min, 0.4g/min or a numerical range consisting of any two of the above values. In some embodiments, the atomization amount of the nebulizer 1 is constant at 0.37g/min. The nebulizer 1 can further set a mouthpiece between the inlet structure and the human mouth and throat model 2, so that the liquid mist aerosol atomized by the nebulizer 1 enters the human mouth and throat model 2 under the suction of the vacuum pump 7. The material of the human mouth and throat model 2 is a highly transparent resin, and the human mouth and throat model 2 is divided into two lobes, so that the droplets deposited on it can be washed out with deionized water after the experiment. At the same time, the left and right models are clamped with pliers during the experiment to ensure the airtightness of the structure and prevent droplets from escaping from the gap.

The filtering device may be any suitable filtering device in the art.

1) The water level in the bubble absorption tube 3 is less than or equal to 10 cm to avoid large splashes of droplets due to excessive flow rate.

2) The slag discharge filter 4 is arranged between the bubble absorption tube 3 and the membrane filtration unit 5 to perform a second-stage filtration on the airflow coming out of the bubble absorption tube 3 and capture droplets in the airflow.

3) The membrane filtration unit 5 is arranged after the slag discharge filter 4 to perform deep filtration on the airflow and completely capture the residual atomized droplets to improve the accuracy of the experiment.

The vacuum pump 7 may be any suitable vacuum pump 7 in the art without being limited thereto.

The vacuum pump 7 can be further provided with a rotor flowmeter 6 in front of the vacuum pump 7 to adjust the experimental flow rate. The experimental flow rate is set to 15 L/min, 22.5 L/min, 30 L/min, 45 L/min, and 60 L/min.

As shown in FIG3 , some other embodiments of the present application use a device for measuring the atomization amount of an atomizer, which comprises: a control module, a drive circuit, an atomizer 1, a weight sensor, and a power module. The control module is configured to generate a PWM signal with different duty cycles. The drive circuit is configured to amplify the PWM signal generated by the control module to provide a driving force to the atomizer 1. The weight sensor is configured to measure the mass of the atomizer 1 before and after atomization. By dividing the mass difference of the atomizer 1 before and after atomization by the atomization time, the device can conveniently calculate the atomization amount of the atomizer 1 under different drives.

The control module may be any suitable signal generating device in the art.

By adjusting the driving parameters, the duty cycle of the pwm signal generated by the control module is: 20%, 30%, 40%, 50% or a range of values formed by any two of the above values. The pwm duty cycle generated by the control module is 20% to 50%, driving the atomizer 1 to change the atomization amount from small to gradually increase.

The driving circuit may select any suitable signal amplifying device in the art.

The driving circuit is configured to be connected to the signal output terminal of the control module and is used to amplify the driving signal generated by the control module.

The weight sensor may be any suitable weight sensor in the art without limitation.

The weight sensor is a high-precision balance and is disposed at the bottom of the atomizer 1 to effectively measure the weight change of the atomizer 1 before and after atomization.

As shown in FIG4 , according to another aspect of the present application, the present application not only provides a new method for using a nebulizer, but also designs a driving device required for the method accordingly. The device has a simple and clear structure and low operating cost, and can flexibly adjust the atomization amount of the nebulizer 1 according to the size of the inhalation flow rate. The present application discloses a nebulizer 1 driving system that utilizes breathing drive and automatically adjusts the atomization amount according to the inhalation flow rate, which includes: a flow sensor, a control module, a drive circuit, a nebulizer 1, and a power module. The flow sensor is configured to collect inhalation flow data at a certain frequency. The power module includes a control switch and a transformer module to provide working power to each electronic device.

The flow sensor may be any suitable flow sensor in the art.

The flow sensor is connected to the user through the mouthpiece to measure the user's inhalation flow. The distance between the flow sensor and the nebulizer 1 is no more than 2 cm, so that the aerosol can be quickly inhaled by the user.

The power module may be any suitable power supply device in the art according to the rated voltage of the selected electronic device, without being limited thereto.

The power supply module is a common power supply, which is connected to the flow sensor, the control module and the drive circuit after being transformed by the transformer module to provide working power for them.

Some embodiments are listed below to illustrate the principle of the present application and the method of using the device.

1. Measurement method

Examples 1-5

The experimental steps for measuring the deposition ratio of liquid mist aerosol in the human mouth and throat model 2 are as follows:

An aqueous solution of 0.9% w/v NaCl and 0.1% w/v fluorescein is used as a test solution, and the test solution is placed in a medicine cup of the nebulizer. The vacuum pump 7 is started, and the inhalation flow rate is adjusted by the rotor flowmeter 6; after the airflow is stabilized, the nebulizer 1 switch is turned on, and the solution is atomized and sprayed out at a certain rate; under the suction of the vacuum pump 7, the liquid mist aerosol enters the real human mouth and throat model and is deposited; then, the aerosol that is not deposited in the mouth and throat is captured by the three-stage filtering device in turn.

After the experiment, each part of the system was ultrasonically cleaned, and the absorbance of the eluate after volume was fixed was measured by an instrument. The mass of the fluorescent droplets deposited in each part of the system was determined according to the solution concentration and volume, and the deposition ratio was determined according to formula (1).

Examples 6-12

The steps for measuring the atomization amount of atomizer 1 driven by different PWM duty cycles are as follows:

An aqueous solution of 0.9% w/v NaCl and 0.1% w/v fluorescein is used as a test solution, and the test solution is placed in the medicine cup of the nebulizer. The total mass m ₁ of the nebulizer 1 and the solution is weighed with an electronic balance; then, a driver is written to the control module, and the control module generates a PWM signal with a certain duty cycle, which is amplified by the drive circuit to drive the nebulizer plate to vibrate and generate liquid mist aerosol; after three minutes of nebulization, the power switch is turned off, and the total mass m ₂ of the nebulizer 1 and the solution is weighed again; finally, the nebulization amount of the nebulizer 1 is calculated by formula (2). Afterwards, the PWM duty cycle generated by the control module is changed, and the above experimental steps are repeated to obtain the nebulization amount of the nebulizer 1 driven by different PWM duty cycles.

2. Measurement results

The measured data of the deposition ratio of the liquid mist aerosol in Examples 1-5 at different inhalation flow rates in the real human mouth and throat model 2 are recorded in the following table.

Referring to the above table, it can be seen that under a single atomization amount, the deposition ratio of the liquid mist aerosol in the human mouth and throat model 2 first decreases and then increases with the increase of the inspiratory flow rate, which is the same as the trend of the experimental results of Ding Ting et al. When the inspiratory flow rate is 30L/min, the aerosol deposition ratio is the smallest, which is 25.1%, indicating that most of the liquid mist aerosol can enter the lower respiratory tract through the human mouth and throat, and has better drug delivery efficiency in clinical practice. In this embodiment, the atomization amount of the aerosol generated by the nebulizer 1 is constant at 0.37g/min, and the optimal atomization amount/inspiratory flow ratio is calculated to be 0.0123; according to this _Qm = 0.37g/min divided by the corresponding flow rate 30L/min, a flow ratio is obtained, which is _qm = 0.0123g/minL; when a patient uses it, the instantaneous flow rate V during its inhalation determines that the optimal atomization mass flow rate of drug delivery for the patient at this moment is _Qoptimal = _qm *V.

The way to achieve Q _optimal for the atomizer device is to measure the PWM signal duty cycle when the device defaults to atomization mass flow rate Q _m = 0.37g/min. The meaning of the duty cycle is shown in the figure. Each T period is very short, milliseconds or microseconds. Assuming that the duty cycle of Q _m = 0.37g/min is 20%, then the atomization mass of 1% duty cycle is 0.37/20 = 0.0185g/min. In this way, it is determined how much duty cycle = Q _optimal / 0.0185 is needed at this moment to achieve Q _optimal .

The measured data of the atomization amount of the atomizer 1 driven by different PWM duty cycles in Examples 6-12 are recorded in the following table.

Referring to the table above, we can see that the larger the duty cycle, the greater the driving power of the atomizer and the higher the atomization volume. The relationship between the duty cycle and the atomization volume can be fitted by the following formula:

Duty＝55.17-113.18x+671.36V _n ²

Among them, the ^R2 value of the formula is 0.97, and the fitting effect is good.

3. Usage

The specific use method of the breath-driven nebulizer drive system with adjustable atomization volume provided by the present application is as follows:

1) Turn on the power supply and press the control switch. The power module starts to supply power to the system. The control module starts to initialize the system and set the PWM frequency and signal output port. If the initialization is successful, the LED indicator integrated on the module will light up. If the initialization fails, the LED will not light up. Users can easily judge whether the drive system can work normally according to the brightness of the indicator.

2) In the working state of 1) above, the control module will read the flow data returned by the flow sensor. When the flow is less than 0.1L/min, or the user is in the exhalation stage, the control module will not generate a PWM signal, and the nebulizer 1 will not produce atomization. According to whether there is an inhalation flow, the drive system automatically switches the atomization/stop working state.

3) In the working state of 2) with inhalation flow, the flow sensor returns flow data to the control module every 0.1 seconds; the control module calculates the required atomization amount according to the flow value and the above-mentioned optimal atomization amount/inhalation flow ratio, and infers the current required PWM duty cycle through the relationship between the atomization amount and the PWM duty cycle of the above-mentioned formula (3), and then inputs the PWM signal into the driving circuit for amplification, thereby driving the atomizer 1 to work with the optimal atomization amount.

Furthermore, in order to prevent the atomization volume from being too small, resulting in too small inhalation volume and too long treatment time, or the atomization volume from being too large, resulting in a poor user experience, the minimum/maximum atomization volume is set to avoid these problems and control the atomization inhalation within the range of efficiency, speed and convenience.

Furthermore, the analog signal input terminal of the control module can be connected to a potentiometer, and the user can actively adjust the knob position and send a corresponding analog signal to the control module. If the knob is rotated clockwise, the larger the output PWM duty cycle, the larger the atomization amount; if the knob is rotated counterclockwise, the smaller the output PWM duty cycle, the smaller the atomization amount, thereby realizing stepless adjustment of the atomization amount. Without violating the spirit of this application, those skilled in the art can set or remove the above components according to actual measurement needs without being limited thereto.

Finally, it should be noted that the above description is only a preferred example of the present invention and is not intended to limit the present invention. Although the present invention has been described in detail with reference to the aforementioned embodiments, those skilled in the art can still modify the technical solutions described in the aforementioned embodiments or replace some of the technical features therein by equivalents. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of the present invention shall be included in the protection scope of the present invention.

Claims (9)

1. A breath-driven atomizer driving device with adjustable atomization amount, which is characterized in that: the device comprises an atomizer, a human mouth-throat model, a filtering device and a vacuum pump, wherein the atomizer is used for containing an atomized solution, the atomizer comprises a medicine cup, an atomizing sheet, a gasket and an inlet structure, liquid aerosol is generated in a certain atomization amount under the drive of an excitation signal, the human mouth-throat model is positioned on one side of the atomizer, the upper end of the human mouth-throat model is connected with one end of the atomizer, the human mouth-throat model is configured to simulate the mouth-throat structure of a real human body so as to serve as a main part for researching the deposition of liquid drops in the human body, and the filtering device is positioned between the human mouth-throat model and the vacuum pump;

The filtering device comprises a bubble absorbing pipe, a slag discharging type filter and a filter membrane filtering unit, the upper end of the filtering device is connected with the lower end of a human mouth-throat model, the bubble absorbing pipe, the slag discharging type filter and the filter membrane filtering unit are sequentially connected between the human mouth-throat model and a vacuum pump, liquid drops escaping from the human mouth-throat model are captured by the filtering device, the bubble absorbing pipe, the slag discharging type filter and the filter membrane filtering unit are respectively subjected to primary filtering, secondary filtering and tertiary filtering, the bubble absorbing pipe, the slag discharging type filter and the filter membrane filtering unit are located at the tail end of the filtering device and are connected with the vacuum pump through a flowmeter, and the vacuum pump is configured to suck liquid mist aerosol into the experimental device at constant air suction flow.

2. A breath actuated adjustable aerosol atomizer actuator as set forth in claim 1, wherein: the bubble absorbing pipe, the deslagging type filter and the filter membrane filter are connected with one another at first in sequence, the air flow coming out of the bubble absorbing pipe is subjected to secondary filtration through the deslagging type filter, liquid drops in the air flow are trapped, and meanwhile, the air flow is subjected to tertiary filtration through the filter membrane filter unit, so that residual atomized liquid drops are completely trapped.

3. A breath actuated adjustable aerosol atomizer actuator as set forth in claim 1, wherein: the driving device is internally provided with an atomizer driving system, the atomizer driving system comprises a flow sensor, a control module and a driving circuit, the flow sensor arranged at one side of the atomizer is used for collecting real-time data flow in the breathing process of a user, the control module outputs corresponding driving signals according to flow values to enable the atomization amount of the atomizer to be changed, and the driving circuit is connected with the signal output end of the control module and is used for amplifying driving signals generated by the control module; the signal output end of the driving circuit is connected with the atomizer, and the atomizer generates high-frequency vibration through the driving force provided by the driving circuit, so that the solution in the medicine cup is atomized and sprayed out.

4. A breath actuated adjustable aerosol atomizer actuator as set forth in claim 3, wherein: the atomizer driving system further comprises a power supply module and a transformation module, wherein the power supply module is respectively connected with the power supply ports of the flow sensor, the control module and the driving circuit, and the transformation module is positioned between the power supply module and the power supply module, is transformed by the transformation module and then is connected with the flow sensor, the control module and the driving circuit so as to provide working power for the flow sensor, the control module and the driving circuit.

5. The application method of the breathing-driven atomizer driving device with the adjustable atomization amount is characterized by comprising the following steps of:

Step 100, placing an atomized solution into an atomizer medicine cup;

step 101, detecting real-time flow in the breathing process of a user through a flow sensor;

102, calculating the required atomization amount by a control module according to the flow value returned by the flow sensor and the optimal atomization amount/inspiration flow ratio determined through experiments, and generating a corresponding pwm signal waveform by the relation between the pwm duty ratio and the atomization amount;

step 103, the control module outputs corresponding driving signals;

step 104, the driving circuit amplifies the driving signal to drive the atomizing sheet so that the atomizer operates under the optimal atomization amount, wherein the optimal atomization amount is determined by the deposition ratio nadir.

6. The method of using a breath actuated adjustable nebulization amount nebulizer drive of claim 5, wherein: in step 100, the nebulizer cup is a chamber for holding a nebulized solution, the chamber including any suitable closed or open chamber, the nebulized solution including a drug portion and a fluorescent portion for measuring a deposition amount, and the nebulized solution droplets entering the model of the human mouth and throat under suction of the vacuum pump; after a period of time, the atomizer and the vacuum pump are turned off; washing out the fluorescent solution deposited on each part; measuring the mass of liquid drops deposited at each part; finally, the deposition ratio of the liquid mist aerosol in the human mouth-throat model is calculated by the following relation:

Where m ₀ is the mass of the droplets deposited in the model of the human mouth and throat, and m _total is the total mass of the droplets trapped at each location.

7. The method of using a breath actuated adjustable nebulization amount nebulizer drive of claim 6, wherein: in step 101, the data collection frequency of the flow sensor includes 10 times/second, and in actual use, the inspiration flow of the user is 0-30L/min, and the maximum range of the flow sensor is greater than or equal to 35L/min.

8. The method of using a breath actuated adjustable nebulization amount nebulizer drive of claim 7, wherein: 102 and 103, reading the instantaneous inspiration flow of the user through a flow sensor, and if the flow is less than 0.1L/min, disabling the system; if the flow is greater than 0.1L/min, the control module calculates the required atomization amount according to the flow value returned by the flow sensor and the optimal atomization amount/inspiration flow ratio determined through experiments, the control module is used for receiving and generating a signal generating device of the signal, and the control module generates a pwm driving signal corresponding to the current required atomization amount according to the relation between the pwm duty ratio and the atomization amount;

1) The atomization amount of the atomizer was calculated from the following formula:

Wherein m ₁ and m ₂ are respectively the total mass of the atomizer and the solution before and after atomization, and t is the atomization time;

2) The relationship between duty cycle and atomization amount is fitted with the following formula:

Duty＝55.17-113.18x+671.36V_n ²

Wherein, the value of the goodness of fit R ² is 0.97.

9. The method of using a breath actuated adjustable nebulization amount nebulizer drive of claim 8, wherein: in step 104, the driving circuit includes any suitable power signal amplifying device, and amplifies the driving signal to a multiple by the driving circuit to drive the atomizing sheet to generate the aerosol.