Atomizer active medicine supply and suction control method, device and equipment and medium

Abstract

The invention discloses an active medicine supply and suction control method, device and equipment for an atomizer and a medium, the atomizer comprises an atomizing sheet, a microphone sensor and a main control chip, and the method comprises the following steps that the capacitance value of the microphone sensor is dynamically changed based on the detected air pressure change when a user inhales; the main control chip is used for collecting the capacitance variable quantity of the microphone sensor, and a signal conversion circuit in the main control chip is used for converting the capacitance variable quantity into an air suction strength grade signal; and driving parameters of the atomization piece are dynamically adjusted on the basis of the obtained inspiration strength grade signal so as to achieve drug supply amount matching. Compared with the prior art, the capacitive sensing technology is combined with a closed-loop feedback control mechanism, output parameters of the atomization piece are monitored in real time and dynamically adjusted, the medicine atomization amount and the user inspiration force are precisely synchronized, and the medicine delivery efficiency is remarkably improved.

Description

Technical Field

[0001] The present application relates to the technical field of medical nebulizers, and in particular to a method, device, equipment and medium for controlling active drug supply and drug inhalation of a nebulizer. Background Art

[0002] Traditional nebulizers often use a constant power drive or manually adjusted drug delivery mode, making it difficult to dynamically adjust drug dosage to the patient's actual inhalation strength, which can easily lead to drug waste or inefficient inhalation. Existing inhalation detection solutions based on pressure sensors suffer from low sensitivity, high noise interference, and a lack of precise linkage between pressure signals and nebulization control. This makes them particularly unsuitable for children, the elderly, and other individuals with weaker respiratory capacity. Summary of the Invention

[0003] The purpose of this application is to provide a method, device, equipment and medium for active drug supply and inhalation control of a nebulizer, aiming to solve the technical problems of low sensitivity, large noise interference, and lack of precise linkage mechanism between pressure signal and atomization control in the existing inhalation detection scheme.

[0004] In order to solve the above technical problems, the purpose of this application is achieved through the following technical solutions:

[0005] A first aspect of the present application provides a method for controlling active drug supply and inhalation of a nebulizer, wherein the nebulizer includes: an atomizer, a microphone sensor, and a main control chip, and the method includes the following steps:

[0006] Dynamically changing the capacitance value of the microphone sensor based on the detected air pressure change when the user inhales;

[0007] The main control chip is used to collect the capacitance change of the microphone sensor, and the signal conversion circuit in the main control chip converts the capacitance change into an inhalation force level signal;

[0008] The driving parameters of the atomizer are dynamically adjusted based on the acquired inhalation force level signal to achieve drug supply matching.

[0009] In a possible implementation, the microphone sensor is a MEMS capacitive air pressure sensor array, and the mapping relationship between the capacitance change ΔC and the inhalation force F satisfies:

[0010] ΔC=C0*(1+α*ln(F / F0)),

[0011] Where C0 is the reference capacitance value, F0 is the minimum detection force threshold, and α is the sensitivity coefficient.

[0012] In one possible implementation, the signal conversion circuit is a charge-to-voltage conversion circuit, which includes a high-frequency carrier generation module, a differential amplifier circuit, and an analog-to-digital converter. The conversion step includes:

[0013] The high-frequency carrier generation module drives the capacitance of the microphone sensor to generate a capacitance change signal;

[0014] Using the differential amplifier circuit to perform noise reduction processing on the capacitance change signal and extract a valid capacitance change signal;

[0015] The analog-to-digital converter quantizes the analog signal after noise reduction processing into a digital inhalation intensity value.

[0016] In a possible implementation, the step of dynamically adjusting the driving parameters of the atomizer plate based on the acquired inhalation force level signal includes:

[0017] When the suction intensity is ≤30% of the full scale, the driving voltage is V=V min +K p *I linear regulation;

[0018] When the inspiratory intensity is greater than 30% of the full scale, the integral compensation item V=V is enabled. min +K p *I+K i ∫Idt, where Kp / Ki is the dynamic adjustment coefficient, I is the inhalation intensity, and Vmin is the minimum driving voltage.

[0019] In a possible implementation, the step of dynamically adjusting the driving parameters of the atomizer plate based on the acquired inhalation force level signal further includes:

[0020] When it is detected that the capacitance change exceeds ±30% of the full scale within 5 consecutive seconds, the driving voltage of the atomizer plate is forced to drop to a safe threshold;

[0021] When it is detected that the capacitance change returns to zero within 2 seconds, it is determined that the user stops inhaling and the power supply of the atomizer is immediately cut off.

[0022] In a possible implementation, the method further includes a dynamic baseline calibration step:

[0023] During the first three inhalation cycles after the atomizer is started, the capacitance value of the microphone sensor is collected and its mean μ and standard deviation σ are calculated;

[0024] The normal fluctuation range is set to [μ-3σ, μ+3σ], and the capacitance change outside the range is regarded as an abnormal signal and automatically filtered.

[0025] In a possible implementation, the method further includes a breathing pattern recognition step:

[0026] Automatically identify shallow breathing, deep breathing or gasping patterns by analyzing the time domain waveform of the capacitance change during n consecutive inspiration-expiration cycles;

[0027] The maximum output limit of the driving parameters is dynamically adjusted according to the identification results.

[0028] A second aspect of the present application provides a device for controlling active drug supply and inhalation of a nebulizer, the device comprising:

[0029] a detection response unit, configured to dynamically change the capacitance value of the microphone sensor based on detected air pressure changes when the user inhales;

[0030] An acquisition and conversion unit, configured to acquire a capacitance change of the microphone sensor using the main control chip, and convert the capacitance change into an inhalation force level signal through a signal conversion circuit in the main control chip;

[0031] A dynamic adjustment unit is used to dynamically adjust the driving parameters of the atomizer based on the acquired inhalation force level signal to achieve drug supply matching.

[0032] A third aspect of the present application provides a computer device, characterized in that the computer device includes a memory and a processor, the memory stores a computer program, and the processor implements the method described in the first aspect when executing the computer program.

[0033] A fourth aspect of the present application provides a computer-readable storage medium, wherein the storage medium stores a computer program, wherein the computer program includes program instructions, and when the program instructions are executed by a processor, the method described in the first aspect can be implemented.

[0034] The beneficial effects of the present application compared to the prior art are as follows: the present application provides a method, device, equipment and medium for active drug supply and inhalation control of a nebulizer, the nebulizer comprising: a nebulizer sheet, a microphone sensor and a main control chip, comprising the following steps: dynamically changing the capacitance value of the microphone sensor based on the detected air pressure change when the user inhales; using the main control chip to collect the capacitance change of the microphone sensor, and converting the capacitance change into an inhalation force level signal through the signal conversion circuit in the main control chip; dynamically adjusting the driving parameters of the nebulizer sheet based on the acquired inhalation force level signal to achieve drug supply quantity matching. Compared to the prior art, the present application adopts capacitive sensing technology combined with a closed-loop feedback control mechanism to monitor and dynamically adjust the output parameters of the nebulizer sheet in real time, so that the drug atomization amount is accurately synchronized with the user's inhalation force, significantly improving the drug delivery efficiency. BRIEF DESCRIPTION OF THE DRAWINGS

[0035] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the following is a brief introduction to the drawings required for use in the description of the embodiments. Obviously, the drawings described below are some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without any creative work.

[0036] Figure 1 A schematic diagram of a method for controlling active drug supply and drug inhalation of a nebulizer provided in an embodiment of the present application Figure 1 ;

[0037] Figure 2 A schematic diagram of a method for controlling active drug supply and drug inhalation of a nebulizer provided in an embodiment of the present application Figure 2 ;

[0038] Figure 3 A schematic diagram of a method for controlling active drug supply and drug inhalation of a nebulizer provided in an embodiment of the present application Figure 3 ;

[0039] Figure 4 A schematic diagram of a method for controlling active drug supply and drug inhalation of a nebulizer provided in an embodiment of the present application Figure 4 ;

[0040] Figure 5 A schematic diagram of a method for controlling active drug supply and drug inhalation of a nebulizer provided in an embodiment of the present application Figure 5 ;

[0041] Figure 6 A schematic diagram of a method for controlling active drug supply and drug inhalation of a nebulizer provided in an embodiment of the present application Figure 6 ;

[0042] Figure 7 A schematic block diagram of a nebulizer active drug supply and inhalation control device provided in an embodiment of the present application;

[0043] Figure 8 A schematic block diagram of a computer device provided in an embodiment of the present application. DETAILED DESCRIPTION

[0044] The following will be combined with the drawings in the embodiments of this application to clearly and completely describe the technical solutions in the embodiments of this application. Obviously, the embodiments described are part of the embodiments of this application, not all of them. Based on the embodiments in this application, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of this application.

[0045] It will be understood that when used in this specification and the appended claims, the terms “comprises” and “comprising” indicate the presence of described features, integers, steps, operations, elements and / or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components and / or groups thereof.

[0046] It should also be understood that the terms used in this specification are for the purpose of describing specific embodiments only and are not intended to limit the present application. As used in this specification and the appended claims, the singular forms "a," "an," and "the" are intended to include the plural forms unless the context clearly indicates otherwise.

[0047] It should be further understood that the term "and / or" used in this specification and the appended claims refers to and includes any and all possible combinations of one or more of the associated listed items.

[0048] In order to solve the technical problems of low sensitivity, large noise interference, and lack of precise linkage mechanism between pressure signal and atomization control in the existing inhalation detection scheme, the present application provides a method for active drug supply and inhalation control of a nebulizer, which can achieve precise synchronization between the drug atomization amount and the user's inhalation force, significantly improving the drug delivery efficiency.

[0049] See also Figures 1 to 6 , an embodiment of the present application provides a method for actively supplying and inhaling drugs through a nebulizer.

[0050] The hardware architecture and sensor layout are as follows: The main structure of the atomizer adopts a modular design, and the core components include a piezoelectric ceramic atomizer, a capacitive microphone sensor, and a main control chip (such as the STM32 series). The atomizer and the microphone sensor are connected through a flexible circuit board to ensure signal transmission stability. The sensor is embedded inside the atomizer nozzle, and the surface is covered with a breathable microporous filter membrane to avoid direct contact with the liquid medicine. The sensor and the main control chip communicate through the IC bus to ensure low-latency data transmission. The main control chip integrates the ADC module, signal processing unit, and PWM drive circuit. The built-in algorithm realizes the detection of inhalation force, dynamic adjustment of the atomizer drive parameters, and safety protection mechanism.

[0051] Figure 1 This is a schematic diagram of a method for controlling active drug supply and drug inhalation of a nebulizer provided in an embodiment of the present application. Figure 1 .like Figure 1 As shown, the method includes the following steps S110-S130.

[0052] S110, dynamically changing the capacitance value of the microphone sensor based on the detected air pressure change when the user inhales;

[0053] Specifically, when the user inhales, the diaphragm inside the microphone sensor will deform with the negative pressure generated by the user's inhalation, causing a slight change in its capacitance value; this embodiment optimizes the mechanical structure of the microphone sensor (such as the diaphragm material and cavity design) to enhance its sensitivity to low-frequency and weak air pressure changes, so that it can accurately capture inhalation movements of different intensities.

[0054] S120: Utilize the main control chip to collect capacitance variation of the microphone sensor, and convert the capacitance variation into an inhalation force level signal through a signal conversion circuit in the main control chip;

[0055] Specifically, the main control chip uses a high-precision analog front-end circuit (i.e., a signal conversion circuit or ADC module) to collect capacitance changes from the microphone sensor. It also uses adaptive algorithms (such as sliding window filtering or threshold comparison) to analyze the signal in real time, discretizing the continuous capacitance changes into multi-level inhalation force signals (e.g., light, medium, and heavy), thereby achieving a quantitative representation of the user's breathing behavior.

[0056] S130 , dynamically adjusting the driving parameters of the atomizer based on the acquired inhalation force level signal to achieve drug supply matching.

[0057] Specifically, the main control chip controls the atomization rate of the drug solution by adjusting the driving voltage, pulse frequency or duty cycle of the atomizer according to the inhalation force level signal. For example: when inhaling with high force, the driving parameters are increased to increase the atomization volume to match the user's rapid inhalation needs; when inhaling with low force, the driving parameters are reduced to avoid waste of drug solution or the risk of choking. Combined with the closed-loop feedback mechanism, the working status of the atomizer (such as current fluctuations) is monitored in real time to ensure a dynamic balance between the drug supply and the inhalation demand.

[0058] In summary, this application can adapt to the differences in breathing intensity of different users (such as children and adults) or different stages of disease (such as acute stage and recovery stage) through dynamic detection and classification, avoiding drug waste or insufficient inhalation caused by the "fixed flow" of traditional nebulizers. At the same time, the on-demand drug supply mechanism synchronizes the output of atomized particles with the user's inhalation, reduces the escape of drugs in the air, and increases the lung deposition rate, which is especially suitable for high-cost or dose-sensitive drugs. In addition, it also greatly enhances the user experience, avoids choking or breath holding caused by the mismatch between the atomization rate and the inhalation, and is especially suitable for patients with weak respiratory muscles.

[0059] Furthermore, in a more specific embodiment, the microphone sensor is a MEMS capacitive air pressure sensor array, and the mapping relationship between its capacitance change ΔC and the inhalation force F satisfies: ΔC = C0*(1+α*ln(F / F0)), where C0 is the reference capacitance value, F0 is the minimum detection force threshold, and α is the sensitivity coefficient.

[0060] Specifically, the microphone sensor in this embodiment adopts a MEMS interdigital capacitor structure, which includes 12 pairs of interleaved interdigital electrodes. The interdigital spacing is 50 μm, the interdigital length is 1 mm, the thickness is 10 μm, and the material is doped polysilicon. When the user inhales, the air pressure change causes the movable electrode of the interdigital structure to have a lateral displacement of 0.1 - 2 μm, resulting in a change in the capacitance between the interdigital electrodes. Its reference capacitance value C0 = 2 pF, and the maximum capacitance change ΔC = ±1.2 pF (corresponding to the inhalation force range of 0.1 - 5 N).

[0061] Among them, the process of realizing the capacitance-force mapping relationship is as follows: Set the minimum detection force threshold F0 = 0.1 N, the sensitivity coefficient α = 0.3. The capacitance change ΔC and the inhalation force F satisfy the relationship: ΔC = C0*(1 + α*ln(F / F0)); The main control chip collects ΔC through the ADC module, with a sampling rate of 1 kHz, and combines the temperature compensation algorithm to eliminate the influence of environmental temperature drift. When F < F0, it is determined as an invalid signal, and the atomizing sheet does not start; when F ≥ F0, the atomizing output is dynamically adjusted according to the real-time calculated F value.

[0062] Finally, the driving parameters of the atomizing sheet are adjusted in two segments according to the F value:

[0063] When 0.1 N ≤ F < 2 N, the driving frequency is 80 - 120 kHz, and the duty cycle is 20% - 75%; when F ≥ 2 N, the driving frequency is 200 kHz, the duty cycle is 100%, and at the same time, overload protection is triggered (current limit 1 A). By adjusting the duty cycle of the pulse width modulation (PWM) signal for driving the atomizing sheet, the average working power of the atomizing sheet can be directly controlled. When the atomizing sheet is in a high duty cycle state, the atomizing sheet is powered on for a long time, the atomizing rate is high, and the liquid medicine output is large; while in a low duty cycle state, the atomizing sheet works intermittently, the atomizing rate is low, and the liquid medicine output is small. This method dynamically adjusts the duty cycle to avoid the atomizing sheet working at high temperature for a long time, slow down aging, and improve the reliability of the device.

[0064] As Figure 2 shown, in a more specific embodiment, the signal conversion circuit is a charge-voltage conversion circuit. The charge-voltage conversion circuit includes a high-frequency carrier generation module, a differential amplifier circuit, and an analog-to-digital converter. The conversion steps include S121 - S123:

[0065] S121. The high-frequency carrier generation module drives the capacitance of the microphone sensor to generate a capacitance change signal;

[0066] Specifically, the high-frequency carrier generation module generates an AC carrier signal with a fixed frequency and directly loads it onto the capacitance plate of the microphone sensor, and the sensor is excited through capacitive coupling. When the user inhales and causes the capacitance value of the sensor to change, the amplitude or phase of the carrier signal is modulated accordingly, generating an AC modulation signal proportional to the capacitance change amount.

[0067] S122, using the differential amplifier circuit to perform noise reduction processing on the capacitance change signal, and extracting a valid capacitance change signal;

[0068] Specifically, the differential amplifier circuit uses a dual-channel input structure to receive the sensor output signal and a reference signal, respectively, eliminating environmental interference (such as power supply noise and temperature drift) through common-mode rejection. The amplifier circuit demodulates and filters the modulated signal, stripping off the high-frequency carrier component and extracting the low-frequency effective capacitance change signal, while also suppressing crosstalk noise in the signal transmission path.

[0069] S123. The analog-to-digital converter quantizes the analog signal after the noise reduction process into a digital inhalation intensity value.

[0070] Specifically, the analog-to-digital converter receives the amplified analog signal and, using successive approximation or integral conversion, discretizes the continuous capacitance change signal into a digital inhalation intensity value. A baseline calibration is performed simultaneously during the conversion process, dynamically compensating for sensor zero-point drift to ensure that the digital output reflects only valid inhalation activity.

[0071] like Figure 3 As shown, in a more specific embodiment, executing step S130 further specifically includes executing steps S131-S132:

[0072] S131, when the suction intensity is ≤30% of the full scale, the driving voltage is V=V min +K p *I linear regulation;

[0073] Specifically, the proportionality coefficient K p Ensure that the inhalation intensity is linearly related to the driving voltage, achieve fast response at low intensity, and avoid lag or fluctuation in atomization volume. min To maintain the minimum driving voltage for the basic operation of the atomizer and prevent atomization interruption due to signal noise.

[0074] S132: When the inhalation intensity is greater than 30% of the full scale, the integral compensation item V=V is enabled. min +K p *I+K i ∫Idt.

[0075] Specifically, the integral term gradually corrects the steady-state error (such as output attenuation caused by aging of the atomizer) by accumulating the time integral value of the inhalation intensity, thereby improving the long-term control accuracy. At the same time, K is adaptively adjusted according to the real-time inhalation intensity change rate. p With K i For example, when the inhalation intensity rises rapidly, K is increased first. p To speed up the response, increase K in the stable stage iTo suppress the cumulative deviation.

[0076] In this embodiment, when the inhalation intensity exceeds 30% of full scale for a preset time threshold (e.g., 0.5 seconds), the device automatically switches to integral compensation mode. If the inhalation intensity drops below 30%, it immediately switches back to pure proportional control mode, ensuring sensitivity in the low-intensity range. In the low-intensity range, linear proportional control enables rapid fine-tuning to accommodate the low-dose requirements of children or patients with weak breathing. In the medium- and high-intensity ranges, integral compensation eliminates long-term deviations, ensuring that the atomized volume accurately matches the user's continuous inhalation action.

[0077] like Figure 4 As shown, in a more specific embodiment, after executing step S130, the process further includes executing steps S140-S150.

[0078] S140, when it is detected that the capacitance change exceeds ±30% of the full scale for 5 consecutive seconds, forcibly reducing the driving voltage of the atomizer plate to a safety threshold;

[0079] Specifically, this embodiment monitors the capacitance change of the microphone sensor in real time. When it detects that the capacitance value continuously exceeds ±30% of the full scale and the duration reaches a preset threshold, the forced protection logic is triggered. The main control chip immediately linearly reduces the driving voltage of the atomizer from the current value to the safety threshold and locks this state until the capacitance signal returns to the normal range. After the abnormality is resolved, the sensor calibration process (such as zero point reset) is automatically executed, and the dynamic adjustment function is restored after confirmation.

[0080] S150: When it is detected that the capacitance change returns to zero within 2 seconds, it is determined that the user stops inhaling, and the power supply of the atomizer plate is immediately cut off.

[0081] Specifically, the dynamic trend of capacitance change is continuously tracked. If the capacitance value is detected to return to zero within a preset time window (such as no fluctuation or maintaining a baseline value), it is determined that the user has actively stopped inhaling. The main control chip immediately cuts off the power supply to the atomizer, stops atomizing the liquid medicine, and starts standby mode to reduce system power consumption. After re-detecting a valid capacitance change signal, the device automatically wakes up and resumes drug supply control.

[0082] like Figure 5 As shown, in a more specific embodiment, dynamic baseline calibration steps S210-S220 are further included.

[0083] S210, collecting capacitance values of the microphone sensor during the first three inhalation cycles after the atomizer is started and calculating the mean μ and standard deviation σ thereof;

[0084] S220, set the normal fluctuation range to [μ-3σ, μ+3σ], and the capacitance change outside the range is regarded as an abnormal signal and automatically filtered.

[0085] Specifically, the dynamic baseline calibration process includes:

[0086] Initial data collection: After the atomizer is started, the original capacitance value of the microphone sensor is continuously collected during the first several inhalation cycles to eliminate transient interference signals.

[0087] Statistical calculation: Perform statistical analysis on the capacitance values within the effective inhalation cycle, calculate their mean and dispersion indicators, and establish a dynamic baseline range.

[0088] Abnormal signal filtering: Capacitance changes that exceed the baseline range are identified as abnormal (such as sensor failure or environmental interference) and are prohibited from participating in the inhalation force calculation to ensure signal purity.

[0089] Furthermore, the quick judgment logic of inhalation interruption is:

[0090] Zero detection: Continuously monitor the absolute value of the capacitance change. If it remains below the noise threshold and remains stable, it is determined that there is no effective inhalation action.

[0091] Power cut-off response: After determining that inhalation has stopped, the atomizer drive circuit is immediately disconnected and the system enters low power consumption mode until a new valid signal is detected.

[0092] like Figure 6 As shown, in a more specific embodiment, it further includes breathing pattern recognition steps S310-S320.

[0093] S310, automatically identifying shallow breathing, deep breathing, or gasping patterns by analyzing the time domain waveform of the capacitance change during n consecutive inspiration-expiration cycles;

[0094] Specifically, this embodiment continuously collects capacitance change waveforms for 10 complete respiratory cycles (inhalation-exhalation) and extracts time-domain features (such as waveform rising slope, peak amplitude, duration, etc.). A pattern classification algorithm is then used to identify respiratory patterns. Shallow breathing is characterized by low waveform peaks, short durations, and gentle slopes; deep breathing is characterized by high waveform peaks, long durations, and steep slopes; and wheezing is characterized by violent peak fluctuations and irregular respiratory cycles.

[0095] S320. Dynamically adjust the maximum output limit of the driving parameter according to the recognition result.

[0096] Specifically, the upper limit of the atomizer drive parameters is constrained in real time based on the recognition results. If the recognition result is a shallow breathing pattern, the maximum output limit is lowered to prevent the atomization rate from exceeding the user's inhalation capacity. If the recognition result is a deep breathing pattern, the limit constraint is lifted, allowing the atomizer to output full power to match the high flow rate requirement. If the recognition result is a gasping pattern, the limit is dynamically adjusted based on real-time waveform fluctuations to prevent sudden changes in atomization volume due to drastic changes in breathing.

[0097] In summary, this embodiment achieves deep coordination between atomization therapy and the user's physiological state through the combination of breathing pattern recognition and dynamic limit control, achieving a precise balance between safety, effectiveness and comfort.

[0098] Figure 7 This is a schematic block diagram of a nebulizer active drug supply and drug inhalation control device provided in an embodiment of the present application. Figure 7 As shown, corresponding to the above-mentioned nebulizer active drug supply and inhalation control method, the present application also provides a nebulizer active drug supply and inhalation control device 400. The nebulizer active drug supply and inhalation control device 400 includes a unit for executing the above-mentioned nebulizer active drug supply and inhalation control method, and the device can be configured in a terminal such as a desktop computer, tablet computer, or laptop computer.

[0099] Specifically, see Figure 7 The nebulizer active drug supply and drug inhalation control device 400 includes:

[0100] The detection response unit 410 is configured to dynamically change the capacitance value of the microphone sensor based on the detected air pressure change when the user inhales.

[0101] The acquisition and conversion unit 420 is used to use the main control chip to acquire the capacitance change of the microphone sensor, and convert the capacitance change into an inhalation force level signal through the signal conversion circuit in the main control chip.

[0102] The acquisition and conversion unit 420 is further specifically configured to: cause the high-frequency carrier generation module to drive the capacitor of the microphone sensor to generate a capacitance change signal; utilize the differential amplifier circuit to perform noise reduction processing on the capacitance change signal and extract a valid capacitance change signal; and cause the analog-to-digital converter to quantize the noise-reduced analog signal into a digital inhalation intensity value.

[0103] The dynamic adjustment unit 430 is used to dynamically adjust the driving parameters of the atomizer based on the acquired inhalation force level signal to achieve drug supply matching.

[0104] The dynamic adjustment unit 430 is further configured to: when the inhalation intensity is ≤30% of the full scale, the driving voltage is V=V min +K p*I linear adjustment; when the inhalation intensity is greater than 30% of the full scale, the integral compensation item V=V is enabled min +K p *I+K i ∫Idt, where Kp / Ki is the dynamic adjustment coefficient, I is the inhalation intensity, and Vmin is the minimum driving voltage.

[0105] It should be noted that those skilled in the art can clearly understand that the specific implementation process of the above-mentioned nebulizer active drug supply and inhalation control device and each unit can refer to the corresponding description in the aforementioned method embodiment. For the convenience and brevity of description, it will not be repeated here.

[0106] The above-mentioned nebulizer active drug supply and drug inhalation control device 400 can be implemented in the form of a computer program. The computer program can be used in the following ways: Figure 8 Runs on the computer equipment shown.

[0107] See also Figure 8 , Figure 8 This is a schematic block diagram of a computer device provided in an embodiment of the present application. The computer device 500 can be a terminal or a server. The terminal can be a smart phone, tablet computer, laptop computer, desktop computer, personal digital assistant, wearable device, or other electronic device with communication capabilities. The server can be a standalone server or a server cluster consisting of multiple servers.

[0108] See Figure 8 The computer device 500 includes a processor 502 , a memory, and a network interface 505 connected via a system bus 501 , wherein the memory may include a non-volatile storage medium 503 and an internal memory 504 .

[0109] The non-volatile storage medium 503 can store an operating system 5031 and a computer program 5032. The computer program 5032 includes program instructions, which, when executed, can enable the processor 502 to execute a method for controlling active drug supply and inhalation of a nebulizer.

[0110] The processor 502 is used to provide computing and control capabilities to support the operation of the entire computer device 500.

[0111] The internal memory 504 provides an environment for the operation of the computer program 5032 in the non-volatile storage medium 503. When the computer program 5032 is executed by the processor 502, the processor 502 can execute a method for actively supplying and inhaling drugs for a nebulizer.

[0112] The network interface 505 is used to communicate with other devices through the network. Figure 8The structure shown in the figure is merely a block diagram of a portion of the structure related to the solution of the present application, and does not constitute a limitation on the computer device 500 to which the solution of the present application is applied. The specific computer device 500 may include more or fewer components than shown in the figure, or combine certain components, or have a different component arrangement.

[0113] It should be understood that in the embodiment of the present application, the processor 502 may be a central processing unit (CPU), and the processor 502 may also be other general-purpose processors, digital signal processors (DSP), application-specific integrated circuits (ASIC), field-programmable gate arrays (FPGA), or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc. The general-purpose processor may be a microprocessor or any conventional processor, etc.

[0114] Those skilled in the art will appreciate that all or part of the steps in the method of the above-described embodiment can be implemented by instructing the relevant hardware through a computer program. The computer program includes program instructions, which can be stored in a storage medium that is computer-readable. The program instructions are executed by at least one processor in the computer system to implement the steps in the method of the above-described embodiment.

[0115] Therefore, the present application also provides a storage medium. The storage medium may be a computer-readable storage medium. The storage medium stores a computer program, wherein the computer program includes program instructions. When the program instructions are executed by a processor, the processor performs the following steps:

[0116] S110, dynamically changing the capacitance value of the microphone sensor based on the detected air pressure change when the user inhales;

[0117] S120: Utilize the main control chip to collect capacitance variation of the microphone sensor, and convert the capacitance variation into an inhalation force level signal through a signal conversion circuit in the main control chip;

[0118] S130 , dynamically adjusting the driving parameters of the atomizer based on the acquired inhalation force level signal to achieve drug supply matching.

[0119] The storage medium may be any computer-readable storage medium that can store program codes, such as a USB flash drive, a mobile hard disk, a read-only memory (ROM), a magnetic disk, or an optical disk.

[0120] Those skilled in the art will appreciate that the units and algorithm steps of each example described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, computer software, or a combination of the two. In order to clearly illustrate the interchangeability of hardware and software, the composition and steps of each example have been generally described in terms of function in the above description. Whether these functions are performed in hardware or software depends on the specific application and design constraints of the technical solution. Professional and technical personnel can use different methods to implement the described functions for each specific application, but such implementation should not be considered to be beyond the scope of this application.

[0121] The non-Company software tools or components appearing in the embodiments of this application are merely examples and do not represent actual use.

[0122] In the several embodiments provided in this application, it should be understood that the disclosed devices and methods can be implemented in other ways. For example, the device embodiments described above are merely illustrative. For example, the division of each unit is merely a logical functional division, and other division methods may be used in actual implementation. For example, multiple units or components can be combined or integrated into another system, or some features can be ignored or not implemented.

[0123] The steps in the method of the embodiment of the present application can be adjusted in order, combined, and deleted according to actual needs. The units in the device of the embodiment of the present application can be combined, divided, and deleted according to actual needs. In addition, the functional units in the various embodiments of the present application can be integrated into a processing unit, or each unit can exist physically separately, or two or more units can be integrated into a single unit.

[0124] If the integrated unit is implemented in the form of a software functional unit and sold or used as an independent product, it can be stored in a storage medium. Based on this understanding, the technical solution of the present application is essentially or the part that contributes to the prior art, or all or part of the technical solution can be embodied in the form of a software product. The computer software product is stored in a storage medium and includes a number of instructions for enabling a computer device (which can be a personal computer, terminal, or network device, etc.) to execute all or part of the steps of the various embodiments of the present application.

[0125] The above are only specific embodiments of the present application, but the scope of protection of the present application is not limited thereto. Any person skilled in the art can easily conceive of various equivalent modifications or substitutions within the technical scope disclosed in this application, and such modifications or substitutions should be included in the scope of protection of this application. Therefore, the scope of protection of this application should be based on the scope of protection of the claims.

Claims

1. A method for controlling active drug supply and inhalation of a nebulizer, the nebulizer comprising: The atomizer, microphone sensor and main control chip are characterized by including the following steps: Dynamically changing the capacitance value of the microphone sensor based on the detected air pressure change when the user inhales; The main control chip is used to collect the capacitance change of the microphone sensor, and the signal conversion circuit in the main control chip converts the capacitance change into an inhalation force level signal; The driving parameters of the atomizer are dynamically adjusted based on the acquired inhalation force level signal to achieve drug supply matching.

2. A method for controlling active drug supply and drug inhalation of a nebulizer according to claim 1, characterized in that: The microphone sensor is a MEMS capacitive air pressure sensor array, and the mapping relationship between its capacitance change ΔC and the inhalation force F satisfies: ΔC=C0*(1+α*ln(F / F0)), Where C0 is the reference capacitance value, F0 is the minimum detection force threshold, and α is the sensitivity coefficient.

3. A method for controlling active drug supply and inhalation of a nebulizer according to claim 1, characterized in that: The signal conversion circuit is a charge-voltage conversion circuit, which includes a high-frequency carrier generation module, a differential amplifier circuit, and an analog-to-digital converter. The conversion step includes: The high-frequency carrier generation module drives the capacitance of the microphone sensor to generate a capacitance change signal; Using the differential amplifier circuit to perform noise reduction processing on the capacitance change signal and extract a valid capacitance change signal; The analog-to-digital converter quantizes the analog signal after noise reduction processing into a digital inhalation intensity value.

4. A method for controlling active drug supply and inhalation of a nebulizer according to claim 2, characterized in that: The step of dynamically adjusting the driving parameters of the atomizer plate based on the acquired inhalation force level signal includes: When the suction intensity is ≤30% of the full scale, the driving voltage is V=V min +K p *I linear regulation; When the inspiratory intensity is greater than 30% of the full scale, the integral compensation item V=V is enabled. min +K p *I+K i ∫Idt, where K p / K i is the dynamic adjustment coefficient, I is the inhalation intensity, V min is the minimum driving voltage.

5. The method for controlling active drug supply and drug inhalation of a nebulizer according to claim 1, characterized in that: The step after dynamically adjusting the driving parameters of the atomizer plate based on the acquired inhalation force level signal further includes: When it is detected that the capacitance change exceeds ±30% of the full scale within 5 consecutive seconds, the driving voltage of the atomizer plate is forced to drop to a safe threshold; When it is detected that the capacitance change returns to zero within 2 seconds, it is determined that the user stops inhaling and the power supply of the atomizer is immediately cut off.

6. A method for controlling active drug supply and inhalation of a nebulizer according to claim 1, characterized in that: The method further comprises a dynamic baseline calibration step: During the first three inhalation cycles after the atomizer is started, the capacitance value of the microphone sensor is collected and its mean μ and standard deviation σ are calculated; The normal fluctuation range is set to [μ-3σ, μ+3σ], and the capacitance change outside the range is regarded as an abnormal signal and automatically filtered.

7. A method for controlling active drug supply and inhalation of a nebulizer according to claim 1, characterized in that: The method further comprises a breathing pattern recognition step: Automatically identify shallow breathing, deep breathing or gasping patterns by analyzing the time domain waveform of the capacitance change during n consecutive inspiration-expiration cycles; The maximum output limit of the driving parameters is dynamically adjusted according to the identification results.

8. A device for controlling active drug supply and drug inhalation of a nebulizer, characterized in that: The device comprises: a detection response unit, configured to dynamically change the capacitance value of the microphone sensor based on detected air pressure changes when the user inhales; An acquisition and conversion unit, configured to acquire a capacitance change of the microphone sensor using the main control chip, and convert the capacitance change into an inhalation force level signal through a signal conversion circuit in the main control chip; A dynamic adjustment unit is used to dynamically adjust the driving parameters of the atomizer based on the acquired inhalation force level signal to achieve drug supply matching.

9. A computer device, characterized in that: The computer device includes a memory and a processor, the memory stores a computer program, and the processor implements the method according to any one of claims 1 to 7 when executing the computer program.

10. A computer-readable storage medium, characterized in that The storage medium stores a computer program, wherein the computer program includes program instructions, and when the program instructions are executed by a processor, the method according to any one of claims 1 to 7 can be implemented.

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