Atomizer system based on inspiration airflow perception adjustment and adjustment method

Abstract

The invention provides an atomizer system based on inspiration airflow sensing adjustment and an adjustment method, and relates to the technical field of medical instruments, and the atomizer system comprises an atomizer body, an airflow sensing module, a control module, an atomization output adjustment module and a voice broadcast module. The airflow sensing module is used for sensing inspiration airflow and converting the inspiration airflow into electric signals. The control module and the airflow sensing module are used for receiving the electric signals and sending control instructions. When the inspiration airflow intensity corresponding to the electric signal is lower than a preset threshold value, a reminding instruction is sent, the atomization output adjusting module is used for adjusting the atomization output quantity of the atomizer body according to a control instruction, and the voice broadcast module is used for receiving the reminding instruction and outputting electronic voice prompt information. Atomization output is matched with the inspiration state in real time, medicine loss is effectively reduced, and the medicine utilization rate is increased; by establishing mathematical models for different nebulizer types and combining breathing parameter correction, individualized accurate adjustment is achieved, and the treatment effect is improved.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, specifically to a nebulizer system and adjustment method based on inhalation airflow sensing and adjustment. Background Technology

[0002] In the field of medical devices, nebulizers are commonly used devices for treating respiratory diseases. They achieve therapeutic effects by converting drug solutions into tiny particles for patients to inhale. Currently, the most widely used nebulizers in clinical practice mainly include two types: jet nebulizers and screen nebulizers. The former uses compressed air to disperse water-based drugs into atomized form, while the latter uses piezoelectric elements to drive the screen to vibrate at high frequency, causing the drug solution to be sprayed from the mesh to form atomized particles.

[0003] Existing nebulizers suffer from a significant technical drawback in practical applications: the nebulization output rate is typically fixed and cannot be dynamically adjusted based on the patient's real-time inspiratory airflow. When the patient is not inhaling or the inspiratory airflow is weak, the nebulizer continues to output nebulized particles at a fixed rate, resulting in a large amount of medication being lost to the environment without being effectively inhaled, leading to severe drug waste. Conversely, when the patient's inspiratory airflow is strong, the fixed output nebulization volume is insufficient to match the inspiratory demand, affecting the efficiency of drug deposition in the lungs. This mismatch between the fixed output mode and the patient's dynamic inspiratory state has become a key issue restricting the improvement of drug utilization in nebulized therapy.

[0004] Furthermore, most existing nebulizers use static adjustment models, failing to fully consider the attenuation characteristics of airflow intensity over time, the periodic changes in respiratory rhythm, and individual differences in the proportion of inspiratory airflow during patient inhalation. This makes it difficult to adapt to airflow fluctuations in the same patient during treatment, hindering precise individualized adjustments. For children, elderly patients, and other groups with weaker respiratory function or lower cooperation levels, existing nebulizers lack an active guidance mechanism for the patient's inspiratory strength. Patients often struggle to determine if their inspiratory state is within the optimal treatment range, frequently resulting in low drug deposition efficiency due to insufficient inspiratory strength.

[0005] Chinese patent document CN110049795A discloses an intelligent nebulizer, which discloses a technical solution that monitors the patient's inhalation and exhalation flow by integrating multimodal sensors and provides visual or tactile feedback to guide the patient to adjust their breathing through wireless communication connection to a smart terminal. This achieves digital management and compliance tracking of the respiratory therapy process. However, this solution belongs to a passive feedback guidance mode, which requires the patient to actively adjust their breathing behavior based on the feedback. It does not involve the technology of automatically adjusting the nebulization output according to the inhalation airflow intensity, and there is still a problem that the nebulization output and the inhalation state cannot be dynamically matched in real time.

[0006] Chinese patent document CN101730560B discloses a ventilator nebulizer delivery system, which discloses a technical solution that monitors the physiological response of passively ventilated patients to breathing movements and automatically optimizes the working parameters of the ventilator and nebulizer by a controller, thereby optimizing drug delivery for mechanically ventilated patients. However, this solution is specifically designed for passively ventilated patients receiving mechanical ventilation and requires the use of a ventilator. Moreover, the control is based on physiological parameters such as lung compliance and airway resistance rather than inspiratory airflow intensity. The quantitative mathematical relationship between nebulization output and airflow parameters is not disclosed, making it unsuitable for standalone nebulizer scenarios used by spontaneously breathing patients. Summary of the Invention

[0007] The purpose of this invention is to provide a nebulizer system and adjustment method based on inspiratory airflow sensing and adjustment. This system can dynamically adjust the nebulization output in real time according to the patient's inspiratory airflow, reduce drug waste and achieve individualized and precise treatment. At the same time, when the patient's inspiratory airflow does not reach the preset threshold, the system reminds the patient to increase the inspiratory force through electronic voice broadcast, thereby improving the efficiency of drug deposition in the lungs and the clinical treatment effect.

[0008] To achieve the above objectives, the present invention provides the following technical solution: Atomizer system based on inhalation airflow sensing and adjustment includes: an atomizer body, an airflow sensing module, a control module, an atomization output adjustment module, and a voice broadcast module. The airflow sensing module is disposed on the inhalation channel of the atomizer body and is used to sense the inhalation airflow and convert it into an electrical signal. The control module is connected to the airflow sensing module, the atomization output adjustment module, and the voice broadcast module, respectively, and is used to receive the electrical signal, send control commands to the atomization output adjustment module based on an airflow-atomization output relationship model, and send a reminder command to the voice broadcast module when the inhalation airflow intensity corresponding to the electrical signal is lower than a preset threshold. The atomization output adjustment module is connected to the atomizer body and is used to adjust the atomization output of the atomizer body according to the control commands. The voice broadcast module is used to receive the reminder command and output electronic voice prompts.

[0009] Preferably, the airflow sensing module uses a thermal airflow sensor or a differential pressure airflow sensor. The thermal airflow sensor detects the airflow velocity by measuring the cooling effect of the airflow on the heating element, while the differential pressure airflow sensor determines the airflow velocity by measuring the pressure difference generated by the airflow at different locations.

[0010] Further preferred: the response time of the airflow sensing module is less than or equal to 50ms, and the measurement accuracy error range is ±3%.

[0011] Further preferred embodiment: the atomizer body is a jet atomizer, and the atomization output adjustment module includes a gas source adjustment valve. The gas source adjustment valve is used to adjust the pressure and flow rate of the compressed gas to control the atomized particle generation rate. The pressure adjustment range is 0.1MPa-0.5MPa, and the flow rate adjustment range is 3L / min-10L / min.

[0012] Further preferred: In the airflow-atomization output relationship model, the atomization output amount With inhalation airflow intensity The relationship satisfies the formula: ;in, The gas source characteristic coefficient has a value range of 0.02 ml / (L·s) to 0.08 ml / (L·s). This is the airflow attenuation coefficient, with a value ranging from 0.01s. - ¹-0.05s - ¹; This refers to the duration of inhalation; The base atomization rate is 0.01 ml / s to 0.03 ml / s.

[0013] Further preferred embodiment: the atomizer body is a screen atomizer, and the atomization output adjustment module includes a vibration controller. The vibration controller is used to adjust the vibration frequency and amplitude of the screen to control the atomized particle generation rate. The vibration frequency adjustment range is 5000Hz-15000Hz, and the amplitude adjustment range is 5μm-20μm.

[0014] Further preferred: In the airflow-atomization output relationship model, the atomization output amount With inhalation airflow intensity The relationship satisfies the formula: ;in, The sieve characteristic coefficient has a value range of 0.015 ml / (L·s) to 0.06 ml / (L·s). The airflow sensitivity index has a value range of 1.1-1.5. This is the amplitude correction function. ,in, Amplitude; The base atomization rate is 0.008 ml / s to 0.025 ml / s.

[0015] A further preferred embodiment: the preset threshold is the inhalation airflow threshold. The value range is 0.5L / s-2.0L / s; the condition for the control module to trigger voice broadcast is: the actual inhalation airflow intensity detected by the airflow sensing module. And the duration is ≥200ms; when If the system detects that inhalation has stopped, the control module controls the voice broadcasting module to stop outputting voice prompts.

[0016] Further preferred: the response delay of the voice broadcast module is ≤100ms; when the control module triggers the voice broadcast, the atomization output adjustment module still adjusts the atomization output according to the airflow-atomization output relationship model.

[0017] A method for adjusting an atomizer based on inhalation airflow sensing, characterized in that it is applied to any of the atomizer systems described above based on inhalation airflow sensing, and includes the following steps: S1: The airflow sensing module senses the intensity and changes of the inhaled airflow and converts the airflow signal into an electrical signal, which is then transmitted to the control module. S2: After receiving the electrical signal, the control module calculates the actual inhalation airflow intensity. Actual inhalation airflow intensity If the actual inhalation airflow intensity is less than the preset threshold and the duration is ≥200ms, the voice broadcast module will be activated and output electronic voice prompts; if the actual inhalation airflow intensity is greater than the preset threshold, the voice broadcast will not be triggered. S3: The control module processes the electrical signal and calculates the atomization output corresponding to the current inhalation airflow intensity based on the airflow-atomization output relationship model. S4: The control module sends a control command to the atomization output adjustment module; S5: The atomization output adjustment module adjusts the atomization output of the atomizer body according to the control command; when the stop of inhalation is detected, the control module controls the atomization output adjustment module to reduce the atomization output to 10%-20% of the basic atomization output, and at the same time controls the voice broadcast module to stop outputting voice prompt information.

[0018] Compared with the prior art, the present invention has the following advantages: I. This invention uses an airflow sensing module to sense the intensity and changes of the patient's inhalation airflow in real time. The control module dynamically adjusts the nebulization output based on the airflow-nebulization output relationship model, so that the nebulization output matches the patient's inhalation state in real time. It accurately delivers the drug when the patient inhales and automatically reduces the output when the patient stops inhaling or the airflow weakens, effectively reducing the waste caused by drug loss to the environment and significantly improving drug utilization.

[0019] Second, this invention establishes mathematical models for jet nebulizers and screen nebulizers, including parameters such as gas source characteristic coefficient, airflow attenuation coefficient, airflow sensitivity index, and amplitude correction function. These models are then combined with respiratory rate and inspiratory ratio for real-time correction. This allows the invention to adapt to the inspiratory habits of different patients and the airflow fluctuations during the inspiratory process of the same patient, achieving individualized and precise adjustment and improving the deposition efficiency and therapeutic effect of drugs in the lungs.

[0020] Third, the nebulization output adjustment process of the present invention is automatically completed by the control module, without the need for manual intervention or active cooperation from the patient to adjust breathing, which lowers the threshold for use and is especially suitable for children, elderly patients and other groups with weak respiratory function or low cooperation, thus improving the convenience and applicability of nebulization therapy. Attached Figure Description

[0021] Figure 1 A schematic diagram of the structure of an atomizer system based on inhalation airflow sensing and adjustment provided by the present invention; Figure 2 The flowchart illustrates an atomizer adjustment method based on inhalation airflow sensing, as provided by this invention. Detailed Implementation

[0022] The technical solution of the present invention will now be clearly and completely described with reference to the accompanying drawings. Obviously, the described embodiments are only some, not all, of the embodiments of the present invention. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0023] Example 1 like Figure 1 As shown, this invention provides an atomizer system based on inhalation airflow sensing and adjustment, including an atomizer body, an airflow sensing module, a control module, an atomization output adjustment module, and a voice broadcast module.

[0024] The airflow sensing module is located on the intake channel of the atomizer body to sense the intake airflow and convert it into an electrical signal. The control module is connected to the airflow sensing module, the atomization output adjustment module, and the voice broadcast module, respectively. It receives the electrical signals and sends control commands to the atomization output adjustment module based on the airflow-atomization output relationship model. At the same time, it can determine whether to trigger the voice broadcast based on the airflow intensity signal transmitted by the airflow sensing module. When the airflow intensity is lower than a preset threshold, it sends a start command to the voice broadcast module.

[0025] The atomization output adjustment module is connected to the atomizer body and is used to adjust the atomization output of the atomizer body according to control commands.

[0026] The voice broadcast module is integrated into the handheld end of the nebulizer body and connects to the control module. It receives reminder commands from the control module and outputs preset electronic voice prompts. The operation panel has "Volume +", "Volume -", and "Voice On / Off" buttons, which patients can adjust as needed. The preset threshold V0 can be set via the "Threshold Adjustment" knob on the panel, and the screen displays the comparison between the current airflow intensity and the threshold in real time (e.g., "Normal" or "Insufficient"). The voice broadcast module uses a high-fidelity speaker with an adjustable output volume range of 30dB-80dB. It supports preset voice content (e.g., "Insufficient inhalation, please increase your inhalation" or "Please take a deep breath to improve the treatment effect"), and the response latency is ≤100ms to ensure real-time reminders.

[0027] Specifically, the airflow sensing module captures the dynamic changes in the patient's inhalation airflow in real time. The control module analyzes and processes the airflow-nebulization output relationship model established based on clinical data to generate control commands. The nebulization output adjustment module adjusts the nebulization output accordingly, so that the nebulization output dynamically matches the patient's inhalation state, solving the problem of drug waste caused by the fixed output of traditional nebulizers. At the same time, the control module triggers or stops voice broadcast by comparing the actual airflow intensity with the preset threshold, guiding the patient to adjust the inhalation intensity.

[0028] In one specific embodiment of this example, the airflow sensing module employs either a thermal airflow sensor or a differential pressure airflow sensor. The thermal airflow sensor detects airflow velocity by measuring the cooling effect of the airflow on the heating element, while the differential pressure airflow sensor determines airflow velocity by measuring the pressure difference generated by the airflow at different locations. The two types of sensors can be flexibly selected based on the nebulizer type and clinical needs to ensure accurate acquisition of airflow signals.

[0029] In one specific embodiment of this example, the response time of the airflow sensing module is less than or equal to 50ms, and the measurement accuracy error range is ±3%. The fast response time ensures that airflow changes can be captured in real time, avoiding adjustment lag; the strict accuracy requirements ensure the accuracy of the airflow signal, providing reliable data for the analysis and processing of the control module.

[0030] In one specific embodiment of this example, the airflow sensing module is also associated with a preset inspiratory airflow threshold V0 to determine whether the patient's inhalation strength meets the treatment requirements. V0 can be dynamically adjusted according to the patient's age, condition, and nebulizer type, with a value range of 0.5L / s-2.0L / s (V0=0.5L / s-1.0L / s is recommended for pediatric patients, and V0=1.0L / s-2.0L / s is recommended for adult patients). The threshold can be manually set through the nebulizer operation panel or automatically adapted by the control module based on historical treatment data.

[0031] In one specific embodiment of this example, the nebulizer body is a jet nebulizer, and the nebulization output adjustment module includes a gas source regulating valve. The gas source regulating valve is used to adjust the pressure and flow rate of the compressed gas to control the atomized particle generation rate. The pressure adjustment range is 0.1MPa-0.5MPa, and the flow rate adjustment range is 3L / min-10L / min. By precisely controlling the pressure and flow rate through the gas source regulating valve, the nebulization requirements of different drugs can be adapted, ensuring uniform atomized particle size.

[0032] In one specific embodiment of this example, for a jet atomizer, the relationship between the atomization output Q1 and the inhalation airflow intensity V in the airflow-atomization output relationship model satisfies the following formula: Where k1 is the gas source characteristic coefficient, ranging from 0.02 ml / (L·s) to 0.08 ml / (L·s); α is the airflow attenuation coefficient, ranging from 0.01 s. - ¹-0.05s - ¹; t is the inhalation duration; b1 is the basic nebulization volume, ranging from 0.01 ml / s to 0.03 ml / s. The item reflects the attenuation characteristics of airflow over time during inhalation, enabling the nebulization output to adapt to the attenuation of airflow during the patient's inhalation. b1 ensures that there is still a basic nebulization volume to maintain the drug nebulization state even when the airflow is weak.

[0033] It should be noted that this implementation introduces a dynamic formula that includes gas source characteristics, airflow attenuation, and inhalation time. The value of k1 reflects the difference in atomization efficiency between different gas sources (compressed air or oxygen), ensuring that the model is adapted to different gas source conditions; The formula reflects the attenuation characteristics of airflow over time during inhalation. For example, if the airflow is strong at the beginning of the patient's inhalation and gradually weakens later, the formula can automatically reduce the nebulization output to avoid drug waste. b1 ensures that even with weak airflow, there is still a basic nebulization volume to maintain drug nebulization. This solves the problem that static models cannot adapt to dynamic changes during inhalation, enabling the output of the jet nebulizer to intelligently adjust with the duration of inhalation, improving the matching degree between drug and airflow. The introduction of the gas source characteristic coefficient enhances the model's adaptability to different gas sources, ensuring efficient nebulization under various clinical gas source conditions, thereby improving the efficiency and utilization of drug deposition in the lungs.

[0034] In one specific embodiment of this example, the atomizer body is a screen atomizer, and the atomization output adjustment module includes a vibration controller. The vibration controller is used to adjust the vibration frequency and amplitude of the screen to control the atomized particle generation rate. The vibration frequency adjustment range is 5000Hz-15000Hz, and the amplitude adjustment range is 5μm-20μm. By adjusting the frequency and amplitude, tiny particles that meet the requirements for lung deposition can be generated.

[0035] In one specific embodiment of this example, for a screen atomizer, the relationship between the atomization output Q2 and the inhalation airflow intensity V in the airflow-atomization output relationship model satisfies the following formula: .

[0036] Where k2 is the screen characteristic coefficient, ranging from 0.015 ml / (L·s) to 0.06 ml / (L·s); β is the airflow sensitivity index, ranging from 1.1 to 1.5; f(A) is the amplitude correction function, f(A) = 0.5 + 0.02 × A, where A is the amplitude; and b2 is the basic nebulization volume, ranging from 0.008 ml / s to 0.025 ml / s. The amplitude correction function f(A) addresses the nonlinearity between amplitude and airflow response, while the airflow sensitivity index β enables individualized adjustment of inspiratory characteristics for different patients. Specifically, this formula is used to calculate the relationship between the atomization output of the screen atomizer and the intensity of the inhalation airflow.

[0037] in, This represents the nebulization output of the sieve nebulizer, measured in ml / s. It is the target value calculated by the model and reflects the drug nebulization efficiency of the sieve nebulizer under specific conditions.

[0038] This is the sieve characteristic coefficient, ranging from 0.015 to 0.06 ml / (L·s), which is related to the physical properties of the sieve, such as material, pore size, and pore density. Different sieves exhibit variations in vibration transmission efficiency and drug solution throughput. For example, metal sieves and plastic sieves have different vibration responses, and small-pore sieves and large-pore sieves have different droplet formation rates. This coefficient can be experimentally calibrated to suit different types of sieves, ensuring the model's versatility.

[0039] V represents the inhalation airflow intensity, measured in L / s. Similar to V in the jet atomizer mentioned above, it is a core variable monitored in real time by the inhalation airflow sensing module, directly affecting the basis for calculating the atomization output.

[0040] β is the airflow sensitivity index, ranging from 1.1 to 1.5, used to reflect the sensitivity of nebulizer output to changes in inspiratory airflow intensity. Different patients have different fluctuation ranges in inspiratory intensity; for example, the amplitude of inspiratory airflow intensity variation differs between children and adults. The larger the β value, the more significant the change in nebulizer output with airflow intensity. By adjusting this index, the model can be adapted to the inspiratory characteristics of different populations, achieving individualized adjustment.

[0041] f(A) is the amplitude correction function, and f(A) = 0.5 + 0.02 × A (A is the amplitude, in μm). It is used to correct the nonlinear effect of the screen amplitude on the atomization output. The screen amplitude directly determines the speed at which the drug solution passes through the screen, and the relationship between amplitude and atomization volume is not a simple linear one. When the amplitude increases, the droplet formation efficiency will show a nonlinear increase. This function introduces the amplitude variable A, so that the model can accurately reflect the atomization capability under different amplitudes. For example, when the amplitude is 50 μm, f(A) = 0.5 + 0.02 × 50 = 1.5, that is, it produces a 1.5-fold correction to the basic calculation result, ensuring that the atomization output volume is accurately matched with the amplitude change.

[0042] The base atomization rate, ranging from 0.008 to 0.025 ml / s, acts as a function in the formula above. Similarly, it maintains the minimum atomization output under low airflow conditions to ensure that the drug solution on the screen surface is always ready for atomization, avoiding drug residue and response delay caused by atomization interruption.

[0043] This formula takes into account the characteristics of the screen itself, airflow intensity, amplitude nonlinearity, and basic nebulization requirements, making the output adjustment of the screen nebulizer more in line with its working principle and improving the matching accuracy between nebulization output and the patient's inhalation state.

[0044] It should be noted that by introducing an amplitude correction function f(A), the nonlinearity between amplitude and airflow response is resolved. For example, as the amplitude increases, the value of f(A) increases accordingly, allowing the nebulization output to more accurately follow amplitude changes. The airflow sensitivity index β is set to consider the differences in sensitivity to changes in airflow intensity among different patients. The higher the β value, the more significant the response of the nebulization output to changes in airflow intensity, achieving individualized adjustment. k2, as the screen characteristic coefficient, can be flexibly adjusted according to parameters such as screen material and pore size to ensure that the model is compatible with different types of screens.

[0045] This implementation scheme significantly improves the matching accuracy between nebulization output and inspiratory airflow under different amplitudes, avoiding drug waste or insufficient output caused by amplitude changes; the introduction of the airflow sensitivity index enables the model to adapt to the inspiratory characteristics of different patients, improving the effect of individualized treatment; the flexible setting of the screen characteristic coefficient enhances the versatility of the model, can be adapted to various screen types, and provides reliable mathematical support for the precise adjustment of the screen nebulizer.

[0046] In one specific embodiment of this example, the control module further corrects the nebulization output based on the breathing rate f and the inspiratory ratio r, using the following correction formula: Where Q0 is the initial nebulization output, t is the time point within the respiratory cycle, and r is the ratio of inspiratory time to respiratory cycle. The sine function term makes the nebulization output fluctuate regularly with the respiratory cycle, increasing the output during the inspiratory phase and appropriately decreasing it during the expiratory phase; the inspiratory proportion correction term adjusts the output amplitude according to the proportion of the patient's inspiratory time, making the nebulization output more closely match the patient's physiological breathing pattern.

[0047] Specifically, this formula is used to correct the initial nebulization output in real time, so that the nebulization output is more in line with the patient's breathing pattern.

[0048] Q is the corrected final nebulization output, in ml / s. It is the actual nebulization output value after comprehensively considering the breathing rhythm and inspiratory ratio, and is directly used to control the operation of the nebulization output adjustment module.

[0049] Q0 is the initial atomization output, which is a basic value calculated according to the above formula. It includes the influence of factors such as airflow intensity, air source or screen characteristics, and is the starting point for correction calculations.

[0050] This is a respiratory rhythm correction term, used to make the nebulized output volume vary periodically with the respiratory cycle. 0.1 is the fluctuation coefficient, controlling the amplitude of fluctuation in nebulized output volume with the respiratory cycle. It is a sine function that reflects the periodicity of respiration. `f` is the patient's respiratory rate, measured in Hz (respiratory rate per minute, converted to per second), which determines the period of the sine function and matches the patient's actual breathing rhythm. `t` is the time point within the respiratory cycle, measured in seconds (s), representing the duration from the start of the current respiratory cycle to the current moment. When the patient is in the inspiratory phase, the sine function value is positive, making the correction term greater than 1, thus increasing the nebulized output. During the expiratory phase, the sine function value is negative, the correction term is less than 1, and the nebulized output decreases, thereby achieving synchronization between nebulized output and respiratory rhythm.

[0051] This is the inspiratory ratio correction term, used to adjust the nebulizer output amplitude based on the proportion of inspiratory time within the respiratory cycle. Here, 'r' represents the inspiratory ratio, i.e., the ratio of inspiratory time to respiratory cycle, ranging from 0 to 1. When 'r' is larger, it indicates a longer inspiratory time, and the correction term value increases, resulting in a corresponding increase in nebulizer output to ensure sufficient drug supply during a longer inspiratory period. When 'r' is smaller, the correction term value is smaller, avoiding excessive drug delivery during a short inspiratory period, thus preventing waste. 0.8 is the base coefficient, and 0.4 is the adjustment coefficient; both work together to keep the correction term within a reasonable range, ensuring that the nebulizer output matches the inspiratory time characteristics.

[0052] This formula dynamically adjusts the initial nebulization output by integrating the periodicity of the respiratory rhythm and individual differences in the proportion of inspiratory air, making the output of the nebulizer more consistent with the patient's physiological breathing pattern, thereby further improving drug utilization and treatment efficacy.

[0053] In one specific embodiment of this example, the control module includes a microprocessor, an A / D converter, and a signal processing unit. The A / D converter has a sampling frequency greater than or equal to 1kHz, and the signal processing unit uses an adaptive filtering algorithm to process the electrical signal. The high sampling frequency captures subtle changes in airflow, and the adaptive filtering algorithm intelligently identifies and eliminates interference signals such as exhalation and ambient airflow, ensuring the accuracy of airflow intensity detection. Simultaneously, the control module compares the actual airflow intensity V detected by the airflow sensing module with a preset threshold V0 in real time: when V < V0 and the duration is ≥200ms (to avoid false triggering due to airflow fluctuations), a voice broadcast reminder is triggered; when V ≥ V0, or when inhalation stops, the voice broadcast module stops the reminder. While the voice broadcast is triggered, the control module still adjusts the nebulization output according to the original airflow-nebulization output relationship model, i.e., the basic nebulization volume remains unchanged, avoiding treatment interruption due to the reminder; if the voice broadcast is triggered multiple times (e.g., three consecutive inhalations fail to reach the threshold), the control module can record this state for subsequent treatment parameter optimization.

[0054] Example 2 like Figure 2 As shown, the present invention also provides an atomizer method based on inhalation airflow sensing and adjustment, applied to the above-mentioned atomizer system, comprising the following steps: S1: The airflow sensing module senses the intensity and changes of the inhaled airflow and converts the airflow signal into an electrical signal, which is then transmitted to the control module. S2: After receiving the electrical signal, the control module calculates the actual inspiratory airflow intensity V and compares V with the preset threshold V0. If V < V0 and the duration is ≥ 200ms, the control module starts the voice broadcast module and outputs electronic voice prompts. If V ≥ V0, the voice broadcast is not triggered. If the patient's inspiratory strength is still not up to standard after the voice broadcast is started (V < V0 duration ≥ 5s), the control module can repeat the broadcast 1-2 times to avoid excessive reminders that may cause discomfort to the patient. If the threshold is not reached for 5 consecutive inhalations, the panel can display a prompt "Inspiratory strength was insufficient for some periods of this treatment. It is recommended to adjust the breathing method" after the nebulization treatment is completed, for reference by medical staff or patients. S3: The control module processes the electrical signal and calculates the atomization output corresponding to the current inhalation airflow intensity based on the airflow-atomization output relationship model. S4: The control module sends a control command to the atomization output adjustment module; S5: The atomization output adjustment module adjusts the atomization output of the atomizer body according to the control command; when the stop of inhalation is detected, the control module controls the atomization output adjustment module to reduce the atomization output to 10%-20% of the basic atomization output, and at the same time controls the voice broadcast module to stop reminding.

[0055] Specifically, signal processing ensures the accuracy of the airflow signal, providing reliable data for subsequent calculations and threshold judgments; step S2 achieves precise triggering and stopping of voice broadcasts through threshold comparison, balancing the reminder effect and patient comfort with a fault-tolerance mechanism; combining the airflow-nebulization output relationship model and correction formula, the calculation of the optimal nebulization output is more in line with the patient's physiological characteristics; when inhalation stops, the nebulization output is reduced to 10%-20% of the basic nebulization volume, and the voice broadcast stops simultaneously, which avoids drug waste and keeps the nebulization system in standby mode for quick response to the next inhalation.

[0056] This invention ensures real-time dynamic matching between nebulization output and inhalation airflow through a complete adjustment process, reducing drug waste when inhalation stops; the signal processing improves data accuracy, providing a guarantee for precise adjustment and threshold judgment; the voice broadcast function guides patients to standardize inhalation, and the automated adjustment process requires no manual intervention, improving treatment efficiency, stability and applicability.

[0057] The above embodiments are only for illustrating the technical concept and features of the present invention, and are intended to enable those skilled in the art to understand the content of the present invention and implement it accordingly. They should not be construed as limiting the scope of protection of the present invention. All equivalent transformations or modifications made in accordance with the spirit and essence of the present invention should be covered within the scope of protection of the present invention.

Claims

1. A nebulizer system based on inhalation airflow sensing and adjustment, characterized in that, include: The atomizer body, airflow sensing module, control module, atomization output adjustment module, and voice broadcast module; The airflow sensing module is located on the air intake channel of the atomizer body and is used to sense the airflow and convert it into an electrical signal. The control module is connected to the airflow sensing module, the atomization output adjustment module and the voice broadcasting module respectively. It is used to receive the electrical signal, send control commands to the atomization output adjustment module based on the airflow-atomization output relationship model, and send a reminder command to the voice broadcasting module when the inhalation airflow intensity corresponding to the electrical signal is lower than a preset threshold. The atomization output adjustment module is connected to the atomizer body and is used to adjust the atomization output of the atomizer body according to the control command. The voice broadcast module is used to receive the reminder command and output electronic voice prompt information.

2. The atomizer system based on inhalation airflow sensing and adjustment according to claim 1, characterized in that: The airflow sensing module employs either a thermal airflow sensor or a differential pressure airflow sensor. The thermal airflow sensor detects the airflow velocity by measuring the cooling effect of the airflow on the heating element, while the differential pressure airflow sensor determines the airflow velocity by measuring the pressure difference generated by the airflow at different locations.

3. The atomizer system based on inhalation airflow sensing and adjustment according to claim 2, characterized in that: The airflow sensing module has a response time of less than or equal to 50ms and a measurement accuracy error range of ±3%.

4. The atomizer system based on inhalation airflow sensing and adjustment according to claim 1, characterized in that: The atomizer body is a jet atomizer, and the atomization output adjustment module includes a gas source adjustment valve. The gas source adjustment valve is used to adjust the pressure and flow rate of the compressed gas to control the atomized particle generation rate. The pressure adjustment range is 0.1MPa-0.5MPa, and the flow rate adjustment range is 3L / min-10L / min.

5. The atomizer system based on inhalation airflow sensing and adjustment according to claim 4, characterized in that: In the airflow-atomization output relationship model, the atomization output quantity With inhalation airflow intensity The relationship satisfies the formula: ;in, The gas source characteristic coefficient has a value range of 0.02 ml / (L·s) to 0.08 ml / (L·s). This is the airflow attenuation coefficient, with a value ranging from 0.01s. - ¹-0.05s - ¹; This refers to the duration of inhalation; The base atomization rate is 0.01 ml / s to 0.03 ml / s.

6. The atomizer system based on inhalation airflow sensing and adjustment according to claim 1, characterized in that: The atomizer body is a screen atomizer, and the atomization output adjustment module includes a vibration controller. The vibration controller is used to adjust the vibration frequency and amplitude of the screen to control the atomized particle generation rate. The vibration frequency adjustment range is 5000Hz-15000Hz, and the amplitude adjustment range is 5μm-20μm.

7. The atomizer system based on inhalation airflow sensing and adjustment according to claim 6, characterized in that: In the airflow-atomization output relationship model, the atomization output quantity With inhalation airflow intensity The relationship satisfies the formula: ;in, The sieve characteristic coefficient has a value range of 0.015 ml / (L·s) to 0.06 ml / (L·s). The airflow sensitivity index has a value range of 1.1-1.

5. This is the amplitude correction function. ,in, The amplitude; The base atomization rate is 0.008 ml / s to 0.025 ml / s.

8. The atomizer system based on inhalation airflow sensing and adjustment according to claim 1, characterized in that: The preset threshold is the inhalation airflow threshold. The value range is 0.5L / s-2.0L / s; the condition for the control module to trigger voice broadcast is: the actual inhalation airflow intensity detected by the airflow sensing module. And the duration is ≥200ms; when If the system detects that inhalation has stopped, the control module controls the voice broadcasting module to stop outputting voice prompts.

9. The atomizer system based on inhalation airflow sensing and adjustment according to claim 1, characterized in that: The response delay of the voice broadcast module is ≤100ms; when the control module triggers the voice broadcast, the atomization output adjustment module still adjusts the atomization output according to the airflow-atomization output relationship model.

10. A method for adjusting an atomizer based on inhalation airflow sensing, characterized in that, Applied to the atomizer system based on inhalation airflow sensing and adjustment as described in any one of claims 1-9, Includes the following steps: S1: The airflow sensing module senses the intensity and changes of the inhaled airflow and converts the airflow signal into an electrical signal, which is then transmitted to the control module. S2: After receiving the electrical signal, the control module calculates the actual inhalation airflow intensity and compares the actual inhalation airflow intensity with a preset threshold. If the actual inhalation airflow intensity is less than the preset threshold and the duration is ≥200ms, the voice broadcast module is activated and outputs electronic voice prompt information. If the actual inhalation airflow intensity is greater than the preset threshold, the voice broadcast is not triggered. S3: The control module processes the electrical signal and calculates the atomization output corresponding to the current inhalation airflow intensity based on the airflow-atomization output relationship model. S4: The control module sends a control command to the atomization output adjustment module; S5: The atomization output adjustment module adjusts the atomization output of the atomizer body according to the control command; when the stop of inhalation is detected, the control module controls the atomization output adjustment module to reduce the atomization output to 10%-20% of the basic atomization output, and at the same time controls the voice broadcast module to stop outputting voice prompt information.

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