Respiratory capacity real-time monitoring method and system for medical vaporizer

Abstract

The invention relates to the field of medical instruments, in particular to a respiratory capacity real-time monitoring method and system of a medical vaporizer. According to the method, the initial atomization airflow flow of the medical atomizer is obtained, the breathing signals of the user in the multiple breathing cycles are collected in the first preset time period, and the initial tidal volume information is obtained. Then, the respiratory signals are converted into a power spectrum density map through fast Fourier transform, inspiration waveforms are extracted to obtain tidal volume characteristic values, and deep analysis of the respiratory signals is achieved. Meanwhile, resistance values and temperature values of the heating wire in a plurality of respiratory cycles are collected, a temperature-resistance change coefficient is generated according to the data, and equipment performance changes are quantified. Based on this, the actual atomized airflow flow is calculated in combination with the initial atomized airflow flow and the coefficient. Finally, the actual atomization airflow flow, the tidal volume characteristic value and the coefficient are synthesized to obtain the actual tidal volume, the medicine dosage is matched according to the actual tidal volume, all the steps are linked with one another, and accurate treatment is achieved through multi-dimensional data integration.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and particularly relates to a method and system for real-time monitoring of respiratory volume of a medical nebulizer. Background Art

[0002] During the treatment process of a medical nebulizer, tidal volume is one of the key parameters determining the drug delivery dose, and there is a close and direct logical connection between it and the drug dose. Existing medical nebulizers use different types of nebulizers for patients with different symptoms. Among them, ultrasonic atomization technology is mostly used for users with respiratory tract injuries, while hot steam nebulizers are mostly used for patients with thick phlegm to improve respiratory tract patency. The design principle of a medical nebulizer is based on accurate monitoring of the patient's tidal volume to precisely control the output dose of the drug, so as to ensure that the patient can inhale an appropriate dose of the drug and thus achieve the best treatment effect.

[0003] However, there are significant defects in the current respiratory volume monitoring technology of medical nebulizers. Taking patients with chronic obstructive pulmonary disease (COPD) as an example, the existing tidal volume monitoring methods cannot accurately capture the complex changes in the inhalation waveform during the patient's breathing process. Due to the unstable breathing of COPD patients and large fluctuations in the inhalation peak value, traditional methods only simply measure the inhalation peak value and do not deeply analyze key features such as the peak frequency and abnormal inhalation peak value, resulting in a large deviation in the tidal volume monitoring result. This makes the drug dose output by the nebulizer not match the actual needs of the patient, and both insufficient or excessive drug dose supply will affect the patient's recovery effect. Therefore, a method and system for real-time monitoring of respiratory volume of a medical nebulizer are needed to solve the above problems. Summary of the Invention

[0004] The main purpose of the present invention is to provide a method and system for real-time monitoring of respiratory volume of a medical nebulizer, aiming to solve the technical problems in the prior art.

[0005] The present invention provides a method and system for real-time monitoring of respiratory volume of a medical nebulizer, including: Obtaining the initial atomization air flow rate of the medical nebulizer; Obtaining the initial tidal volume information of the user in multiple respiratory cycles within a first preset time period, where the initial tidal volume information includes multiple respiratory signals; The multiple respiratory signals generate a power spectral density map through fast Fourier transform, extract multiple inhalation waveforms according to the power spectral density map, and obtain tidal volume characteristic values according to the multiple inhalation waveforms; Obtaining multiple resistance values and multiple temperature values generated by the heating wire corresponding to the medical nebulizer within multiple respiratory cycles of the user; Generating a temperature-resistance change coefficient according to the multiple resistance values and multiple temperature values; Obtain the actual atomization air flow rate based on the initial atomization air flow rate and the temperature-resistance change coefficient; Obtain the actual tidal volume based on the actual atomization air flow rate, the tidal volume characteristic value, and the temperature-resistance change coefficient; Adjust the drug output dose of the atomizer according to the actual tidal volume.

[0006] Preferably, the step of obtaining the tidal volume characteristic value according to multiple inhalation waveforms includes: Extract multiple waveform peaks from multiple inhalation waveforms, obtain multiple time intervals between the multiple waveform peaks according to a preset time series, and obtain the peak frequency according to the multiple time intervals; Obtain multiple inhalation peak values from multiple inhalation waveforms, obtain the inhalation peak average value according to the multiple inhalation peak values, obtain the standard inhalation peak value according to the multiple inhalation peak values and the inhalation peak average value, and compare the multiple inhalation peak values with the standard inhalation peak value in sequence to obtain abnormal inhalation peak values; Obtain the inhalation time period; Obtain the tidal volume characteristic value according to the peak frequency, the standard inhalation peak value, the abnormal inhalation peak value, and the inhalation time period.

[0007] Preferably, the step of generating the temperature-resistance change coefficient according to multiple resistance values and multiple temperature values includes: Obtain multiple reference resistance values when the heating wire initially operates in historical data, and generate a reference line according to the multiple reference resistance values; Obtain the temperature change time period of the heating wire in the respiratory cycle, continuously extract multiple temperature values according to the temperature change time period, and generate the temperature change gradient at adjacent moments according to the extracted temperature values; Obtain the resistance change value at each continuously extracted moment, and associate each resistance change value with the corresponding temperature change gradient to obtain the dynamic association result data; Generate the temperature-resistance change coefficient according to the dynamic association result data.

[0008] Preferably, after the step of generating the temperature-resistance change coefficient according to multiple resistance values and multiple temperature values, it includes: Obtain multiple inhalation curves and multiple exhalation curves according to the respiratory cycle, generate a respiratory spectrum through Fourier transform according to the multiple inhalation curves and multiple exhalation curves, and extract the inhalation phase and exhalation phase of each respiratory cycle from the respiratory spectrum; Obtain the corresponding multiple resistance values during the operation of the heating wire according to the inhalation curve of each respiratory cycle, and obtain the corresponding resistance change curve according to the multiple resistance values; Synchronize the start timestamp of the inhalation phase initial point of each resistance change curve, obtain multiple resistance difference curves according to each resistance change curve, obtain the mean value of the resistance difference curves according to the multiple resistance difference curves, and obtain the resistance difference interval according to the multiple resistance difference curves and the mean value of the resistance difference curves; Judge whether the resistance difference interval is within a preset interval; If it is within the preset interval, it is determined that the user's breathing is stable; If it is outside the preset interval, it is determined that the user's breathing is disordered.

[0009] Preferably, after the step of generating the temperature-resistance change coefficient according to the multiple resistance values and the multiple temperature values, it includes Obtain the inhalation interval time period according to the breathing cycle; Set the target temperature value to the temperature at which the condensed water on the instantaneously evaporable heating wire can be evaporated; Obtain the temperature value of the heating wire under the rated current; Increase the rated current by an increasing multiple to obtain an increased rated current, and heat the heating wire according to the increased rated current to obtain a first temperature value; Judge whether the first temperature value reaches the target temperature value; If the target temperature value is not reached, return to the step of increasing the rated current by an increasing multiple to obtain an increased rated current until the target temperature value is reached and end.

[0010] Preferably, the step of adjusting the drug output dose of the atomizer according to the actual tidal volume includes: Obtain the user's target liquid medicine dose; Obtain the user's ideal tidal volume according to the target liquid medicine dose and the liquid medicine ratio; Obtain the ideal gas supply times according to the ideal tidal volume and the target liquid medicine dose; Start gas supply according to the ideal gas supply times. After the gas supply ends, obtain the actual tidal volume corresponding to the ideal gas supply times; Calculate the inhalation difference amount according to the actual tidal volume and the ideal tidal volume; Judge whether the inhalation difference amount meets the preset value interval; If not, obtain the compensated liquid medicine dose according to the inhalation difference amount, and use the compensated liquid medicine dose as the target liquid medicine dose and return to the step of obtaining the user's ideal tidal volume according to the target liquid medicine dose and the liquid medicine ratio; If it is satisfied, end the gas supply.

[0011] This application also provides a real-time breathing volume monitoring system for a medical atomizer, including: A first acquisition module, which acquires the initial atomization air flow rate of the medical atomizer; The second acquisition module acquires the initial tidal volume information of multiple respiratory cycles of the user within the first preset time period, where the initial tidal volume information includes multiple respiratory signals; The first generation module generates a power spectral density map through fast Fourier transform of the multiple respiratory signals, extracts multiple inhalation waveforms according to the power spectral density map, and obtains tidal volume characteristic values according to the multiple inhalation waveforms; The third acquisition module acquires multiple resistance values and multiple temperature values generated by the heating wire corresponding to the medical nebulizer within multiple respiratory cycles of the user; The second generation module generates a temperature-resistance change coefficient according to the multiple resistance values and the multiple temperature values; The fourth acquisition module acquires the actual atomization air flow rate according to the initial atomization air flow rate and the temperature-resistance change coefficient; The fifth acquisition module acquires the actual tidal volume according to the actual atomization air flow rate, the tidal volume characteristic value, and the temperature-resistance change coefficient; The sixth acquisition module adjusts the drug output dose of the nebulizer according to the actual tidal volume.

[0012] Preferably, the first generation module includes: The first acquisition unit extracts multiple waveform peaks from the multiple inhalation waveforms, obtains multiple time intervals between the multiple waveform peaks according to a preset time sequence, and obtains the peak frequency according to the multiple time intervals; The second acquisition unit obtains multiple inhalation peaks according to the multiple inhalation waveforms, obtains the inhalation peak average value according to the multiple inhalation peaks, obtains the standard inhalation peak value according to the multiple inhalation peaks and the inhalation peak average value, and compares the multiple inhalation peaks with the standard inhalation peak value in sequence to obtain abnormal inhalation peaks; The third acquisition unit obtains the inhalation time period; The fourth acquisition unit obtains the tidal volume characteristic value according to the peak frequency, the standard inhalation peak value, the abnormal inhalation peak value, and the inhalation time period.

[0013] Preferably, the second generation module includes: The fifth acquisition unit acquires multiple reference resistance values when the heating wire initially operates in the historical data, and generates a reference line according to the multiple reference resistance values; The sixth acquisition unit acquires the temperature change time period of the heating wire in the respiratory cycle, continuously extracts multiple temperature values according to the temperature change time period, and generates the temperature change gradient at adjacent moments according to the extracted temperature values; The seventh acquisition unit acquires the resistance change value at each continuously extracted moment, and correlates each resistance change value with the corresponding temperature change gradient to obtain dynamic correlation result data; The first generation unit generates a temperature-resistance change coefficient according to the dynamic correlation result data.

[0014] Preferably, the second acquisition module includes: An eighth acquisition unit, which acquires a plurality of inhalation curves and a plurality of exhalation curves according to the respiratory cycle, generates a respiratory spectrum through Fourier transform according to the plurality of inhalation curves and the plurality of exhalation curves, and extracts the inhalation phase and the exhalation phase of each respiratory cycle according to the respiratory spectrum; A ninth acquisition unit, which acquires a corresponding plurality of resistance values during the operation of the heating wire according to the inhalation curve of each respiratory cycle, and acquires a corresponding resistance change curve according to the plurality of resistance values; A tenth acquisition unit, which synchronizes the start timestamp of the inhalation phase initial stage of each resistance change curve, acquires a plurality of resistance difference curves according to each resistance change curve, acquires the average value of the resistance difference curves according to the plurality of resistance difference curves, and acquires a resistance difference interval according to the plurality of resistance difference curves and the average value of the resistance difference curves; A first judgment unit, which judges whether the resistance difference interval is within a preset interval; If it is within the preset interval, it is determined that the user's breathing is stable; If it is outside the preset interval, it is determined that the user's breathing is disordered.

[0015] The beneficial effects of the present invention are as follows: First, the present invention obtains the initial atomization air flow rate of the medical atomizer, which is the basic data for subsequent calculations. Then, within the first preset time period, the respiratory signals of the user in multiple respiratory cycles are collected to obtain the initial tidal volume information. Then, these respiratory signals are subjected to fast Fourier transform to generate a power spectral density map, and the inhalation waveform is extracted from it to obtain the tidal volume characteristic value, realizing the in-depth analysis of the respiratory signals. At the same time, the resistance values and temperature values of the heating wire of the medical atomizer in multiple respiratory cycles are collected to provide data for analyzing the performance changes of the device. Subsequently, based on these resistance values and temperature values, a temperature-resistance change coefficient is generated to quantify the performance change law of the device. Based on this, the actual atomization air flow rate is calculated by combining the initial atomization air flow rate and the temperature-resistance change coefficient. Finally, the actual tidal volume is obtained by comprehensively considering the actual atomization air flow rate, the tidal volume characteristic value, and the temperature-resistance change coefficient, and then the drug dose output by the medical atomizer is matched according to the actual tidal volume, so as to achieve precise treatment. The whole process is closely linked, from basic data collection to respiratory signal analysis, device performance research, to key parameter calculation and drug dose matching. Each step is closely coordinated. Through the integration and analysis of multi-dimensional data, the problems in traditional methods such as inaccurate tidal volume calculation, ignoring the influence of device performance, and the limitation of single-factor calculation are solved, providing a reliable guarantee for the precise treatment of medical atomizers. Description of the Drawings

[0016] Figure 1 It is a schematic flowchart of the method according to an embodiment of the present invention.

[0017] Figure 2 It is a schematic diagram of the system structure according to an embodiment of the present invention.

[0018] The realization of the object of the present invention, functional characteristics and advantages will be further described with reference to the embodiments and the accompanying drawings. Specific embodiments

[0019] It should be understood that the specific embodiments described herein are only used to explain the present invention and are not used to limit the present invention.

[0020] As Figure 1 - Figure 2 shown, the present application provides a method and system for real-time monitoring of respiratory volume of a medical nebulizer, including: S1. Obtain the initial atomization air flow rate of the medical nebulizer; S2. Obtain the initial tidal volume information of the user in multiple respiratory cycles within a first preset time period, where the initial tidal volume information includes multiple respiratory signals; S3. Generate a power spectral density map through fast Fourier transform of the multiple respiratory signals, extract multiple inhalation waveforms according to the power spectral density map, and obtain tidal volume characteristic values according to the multiple inhalation waveforms; S4. Obtain multiple resistance values and multiple temperature values generated by the heating wire corresponding to the medical nebulizer within multiple respiratory cycles of the user; S5. Generate a temperature-resistance change coefficient according to the multiple resistance values and multiple temperature values; S6. Obtain the actual atomization air flow rate according to the initial atomization air flow rate and the temperature-resistance change coefficient; S7. Obtain the actual tidal volume according to the actual atomization air flow rate, tidal volume characteristic values and temperature-resistance change coefficient; S8. Adjust the drug output dose of the nebulizer according to the actual tidal volume.

[0021] As described in the above steps S1 - S8, in the data collection and basic feature extraction stage of the present invention, first, the built - in flow detection device of the medical nebulizer is used to directly read the initial air flow rate when the device is started. This data is the basic parameter for the operation of the nebulizer, representing the starting flow rate of the gas ejected by the nebulizer. After obtaining the initial air flow rate, the liquid medicine required by the user is added to the nebulizer to generate the initial atomized air flow rate. Different medicine components and drug viscosities will affect the initial atomized air flow rate. For example, when the initial air flow rate is larger, the spraying speed of the atomized drug is faster and the diffusion range may be wider. When the flow rate is smaller, the opposite is true. This data provides the starting reference for the subsequent analysis of the working state of the nebulizer itself. The subsequent calculation and adjustment of parameters such as tidal volume will be carried out based on this. In the first preset time period, after obtaining the signal with the help of the respiratory signal acquisition device, the signal of each respiratory cycle is transmitted to the data processing device. The collected respiratory signal is subjected to inverse Fourier transform to obtain the power spectral density map. The power spectral density map can show the power distribution of the respiratory signal at different frequencies. Each inhalation waveform is an inhalation phase. The start time of the inhalation waveform is defined as the start time point, the end time of the inhalation waveform is defined as the end time point, the wavelength of the inhalation waveform is defined as the inhalation time, and the peak value of the inhalation waveform is defined as the inhalation intensity. The gas flow rate during inhalation is obtained according to the inhalation time and inhalation intensity. The total amount of gas inhaled during inhalation is obtained according to the start time point, end time point and gas flow rate during inhalation. The total amount of gas inhaled during inhalation is used as the tidal volume characteristic value.

[0022] Specifically, the formula for obtaining the tidal volume characteristic value according to multiple said inhalation waveforms is: ; V c represents the tidal volume characteristic value, S lin(t) represents the gas flow rate during inhalation, ta represents the start time point, and tb represents the end time point; Specifically, the formula for obtaining the gas flow rate during inhalation according to the inhalation waveform is: ; S c represents the inhalation time, S q represents the inhalation intensity.

[0023] Meanwhile, during multiple respiratory cycles of the user, a high-precision resistance sensor and a temperature sensor are synchronously utilized to collect multiple resistance values and temperature values corresponding to the heating wire within each respiratory cycle. The resistance sensor converts the change in the resistance of the heating wire into an electrical signal by detecting it; the temperature sensor uses a thermosensitive element to sense the temperature change of the heating wire in real time and outputs corresponding data. After the data is collected, taking the first preset time period as the time axis, multiple resistance values are plotted into a resistance change trend curve graph, which can clearly present the change of the resistance with the respiratory cycle during this period, such as whether there is a trend of gradually increasing or decreasing resistance; similarly, a temperature change graph is constructed based on the preset time period and multiple temperature values to visually display the dynamic fluctuation of the temperature, such as the rise and fall changes of the temperature during the inhalation and exhalation phases. By comparing and observing these two graphs, it is found that there is a close connection between the resistance change and the temperature change, and the two are matched and integrated to generate temperature-resistance change information. This information reflects the performance change law of the heating wire during operation, such as whether the resistance of the heating wire will change abnormally with the increase in temperature. These information are of great significance for accurately evaluating the working state of the atomizer and assisting in calculating the actual tidal volume.

[0024] Specifically, the steps for generating a temperature-resistance change coefficient according to multiple resistance values and multiple temperature values include: Obtain the first resistance value corresponding to multiple temperature moments; Obtain the second resistance value corresponding to the initial temperature; Obtain the material temperature coefficient corresponding to the heating wire; Calculate the resistance change coefficient of the heating wire at different temperatures according to multiple first resistance values, second resistance values and the material temperature coefficient, where the calculation formula is: ; Wherein, R(T) represents the first resistance value, R0 represents the second resistance value, α represents the temperature coefficient corresponding to the material of the heating wire, T represents the current temperature, and T0 represents the initial temperature; R(T) in the above formula represents a variable that changes with temperature and is used to describe the resistance characteristics of the heating wire at different temperatures. Among them, R0 represents a fixed reference value, usually selected to be measured at room temperature or a certain specific reference temperature. α represents the temperature coefficient corresponding to the material of the heating wire, which describes the ratio or sensitivity of the resistance change with temperature. It is a constant and is fixed for a specific material (such as nickel). The value of the temperature coefficient determines the rate of change of the resistance with temperature. T represents the current temperature, which is a variable that may change with time or other conditions. In practical applications, a temperature sensor is required to measure this value. T0 represents the initial temperature, which is usually a fixed value and is used as a reference point for resistance measurement.

[0025] By clearly obtaining the resistance values, initial resistance value, and material temperature coefficient at different temperature moments, and calculating the resistance change coefficient using a formula, the characteristics of the resistance of the heating wire changing with temperature can be accurately quantified. Obtaining the resistance values at multiple temperature moments can cover the states of the heating wire at different operating temperatures. Combining the resistance value at the initial temperature and the temperature coefficient of the material itself, data is obtained from three dimensions: time, initial state, and material properties. The multi-dimensional data collection and application make the calculation results more comprehensively reflect the actual characteristics of the heating wire. It avoids the one-sidedness brought by single data or partial data and can more realistically simulate the resistance change of the heating wire in actual operation. For example, in the respiratory department of a certain hospital, a medical nebulizer is used to treat patients. As the usage time increases, the atomization efficiency of some nebulizers decreases. Using this solution, first, the first resistance value of the heating wire at multiple temperature moments and the second resistance value at the initial temperature are collected, and the material temperature coefficient of the heating wire is obtained. By calculating the resistance change coefficient, it is found that the resistance change coefficient of the heating wire of one nebulizer significantly deviates from the normal range, and the resistance changes too much under the same temperature change. Further inspection reveals that the heating wire is aging, resulting in abnormal resistance change with temperature. Based on the calculation results, the hospital promptly replaces the heating wire, and the atomization efficiency of the nebulizer returns to normal, ensuring the treatment effect of patients.

[0026] Specifically, the steps of obtaining the actual atomization air flow rate according to the initial atomization air flow rate and the temperature-resistance change coefficient include: Obtain the actual atomization air flow rate according to the initial atomization air flow rate, the first resistance value, and the second resistance value, where the calculation formula is: ; Q s represents the actual atomization air flow rate, Q c represents the initial atomization air flow rate, R(T) represents the first resistance value, and R0 represents the second resistance value.

[0027] In the design and use of traditional medical nebulizers, the impact of changes in the performance of the heating wire on the atomization air flow rate is usually not considered. Operators often think that the atomization air flow rate is only determined by the initial set parameters of the device. In fact, when the resistance of the heating wire changes with temperature and usage duration, it will affect its heating efficiency, and then change the aerodynamic characteristics in the atomization chamber, resulting in the actual atomization air flow rate being inconsistent with the initial setting. Due to the lack of consideration of the dynamic changes in the performance of the heating wire, the atomization air flow rate output by traditional nebulizers is unstable during long-term operation or when environmental conditions change. For example, after continuous use for several hours, the temperature of the heating wire rises and the resistance changes. If no corresponding adjustment is made, it may lead to a decrease in the atomization air flow rate, affecting the drug atomization effect and the accuracy of the patient's inhalation dose.

[0028] Obtain the actual atomization air flow rate based on the initial atomization air flow rate, the actual atomization air flow rate, and the tidal characteristics value. The calculation formula is as follows: ; V s represents the actual tidal volume, and V c represents the tidal volume characteristic value, Q s represents the actual atomization air flow rate, and Q c represents the initial atomization air flow rate.

[0029] The initial atomization air flow rate determines the basic speed of the drug sprayed by the atomizer and directly affects the initial conditions of the gas inhaled by the user; the initial tidal volume information reflects the actual breathing needs and inhalation characteristics of the user; the temperature-resistance change information reflects the working state of the heating wire, a key component of the atomizer, and the performance of the heating wire affects the overall working efficiency and stability of the atomizer. These three groups of data are interrelated and interact with each other. By comprehensively and deeply analyzing and integrating them and considering the influence of various factors on the tidal volume, the actual tidal volume is finally obtained. For example, if the initial air flow rate is large, but the resistance of the heating wire increases abnormally, resulting in a decrease in atomization efficiency, combined with the inhalation characteristics of the user, the actual tidal volume is comprehensively judged. The accurate acquisition of the actual tidal volume lays a solid foundation for the subsequent medical atomizer to adjust the operating parameters according to the user's true breathing needs and achieve accurate drug dosage output. The entire process starts from the collection of basic data, obtains information from three dimensions: the state of the atomizer itself, the breathing characteristics of the user, and the performance of the key components of the device, and then through gradual analysis and integration, finally realizes the accurate calculation of the actual tidal volume. This multi-dimensional and step-by-step data processing method avoids the one-sidedness of calculating the tidal volume with a single piece of data and can more comprehensively and truly reflect the actual breathing situation of the user during the use of the medical atomizer, providing a strong guarantee for improving the effectiveness and safety of atomization treatment.

[0030] In one embodiment, the step of obtaining the tidal volume characteristic value according to the plurality of inhalation waveforms includes: S201. Extract a plurality of waveform peaks from the plurality of inhalation waveforms, obtain a plurality of time intervals between the plurality of waveform peaks according to a preset time sequence, and obtain the peak frequency according to the plurality of time intervals; S202. Obtain a plurality of inhalation peak values from the plurality of inhalation waveforms, obtain the average inhalation peak value according to the plurality of inhalation peak values, obtain the standard inhalation peak value according to the plurality of inhalation peak values and the average inhalation peak value, and compare the plurality of inhalation peak values with the standard inhalation peak value in sequence to obtain abnormal inhalation peak values; S203. Obtain the inhalation time period; S204. Obtain the tidal volume characteristic value according to the peak frequency, the standard inhalation peak value, the abnormal inhalation peak value, and the inhalation time period.

[0031] As described in the above steps S201 - S204, the present invention conducts a refined analysis of the inhalation waveform from the time - series dimension by extracting the peak tips of multiple inhalation waveforms and calculating the time intervals between the peak tips to obtain the peak - tip frequency. Compared with the traditional method that only focuses on the amplitude of the inhalation waveform, the introduction of the peak - tip frequency can effectively capture the periodic changes and frequency characteristics during inhalation. Under different breathing states, the peak - tip frequencies of the inhalation waveforms will show obvious differences. This step can sensitively perceive such changes, providing a key basis for judging the regularity and stability of breathing. At the same time, the extraction and analysis of multiple peak tips can avoid the accidental error of a single data, making the obtained peak - tip frequency more representative and reliable, thus laying a solid foundation for the accurate calculation of subsequent tidal volume characteristic values. By obtaining multiple inhalation peaks, calculating the average inhalation peak, the standard inhalation peak, and identifying abnormal inhalation peaks, a comprehensive and in - depth analysis of the amplitude information of the inhalation waveform is carried out. Calculating the average inhalation peak can comprehensively reflect the average intensity during inhalation, and the standard inhalation peak constructs a standard reference for measuring the inhalation intensity based on the average value and each inhalation peak. By comparing each inhalation peak with the standard inhalation peak, abnormal inhalation peaks can be accurately identified. These abnormal values may reflect special situations during the patient's breathing process, such as sudden exertion of respiratory muscles or transient airway obstruction. This refined processing of inhalation peaks can more accurately describe the amplitude characteristics of the inhalation waveform compared with the traditional method of simply using a single inhalation peak for calculation, improving the accuracy and reliability of tidal volume characteristic value calculation, enabling the nebulizer to better adapt to the complex and variable breathing states of patients. By determining the inhalation time period, the duration of inhalation can be intuitively understood. Combining the frequency and amplitude information of the inhalation waveform, the dynamic changes during inhalation can be analyzed more comprehensively. This step provides important time parameters for subsequent tidal volume characteristic value calculation based on the time dimension, making the calculation of tidal volume more in line with the actual respiratory physiological process, enhancing the physical meaning and clinical practicability of tidal volume characteristic values. By integrating these parameters such as peak - tip frequency, standard inhalation peak, abnormal inhalation peak, and inhalation time period, the characteristics of the inhalation process can be comprehensively characterized. The peak - tip frequency affects the inhalation volume per unit time, the standard inhalation peak and abnormal inhalation peak reflect the inhalation intensity, and the inhalation time period determines the duration of inhalation. They interact with each other to accurately reflect the actual volume of the patient's inhalation, that is, the tidal volume characteristic value. For example, for patients with unstable breathing, through the comprehensive calculation of these parameters, their true tidal volume can be more accurately reflected, avoiding errors caused by single - measurement of inhalation peaks. This calculation method of multi - parameter fusion can more accurately and comprehensively reflect the true tidal volume of patients compared with the traditional method of calculating tidal volume with a single or a small number of parameters. Each parameter describes the characteristics of the inhalation process from different angles, complementing and verifying each other, effectively reducing the calculation error caused by the limitations of a single parameter.By synthesizing these parameters, a tidal volume more in line with the actual respiratory physiology of the patient can be established, making the characteristic value of the tidal volume more scientific and reliable, which helps to achieve personalized and precise atomization therapy.

[0032] In one embodiment, the step of generating the temperature-resistance change coefficient according to the resistance change trend curve graph includes: S301. Obtain a plurality of reference resistance values when the heating wire starts to work in the historical data, and generate a reference line according to the plurality of reference resistance values; S302. Obtain the temperature change time period of the heating wire in the respiratory cycle, continuously extract a plurality of temperature values according to the temperature change time period, and generate a temperature change gradient at adjacent moments according to the extracted temperature values; S303. Obtain the resistance change value at each continuously extracted moment, and associate each resistance change value with the corresponding temperature change gradient to obtain dynamic association result data; S304. Generate a temperature-resistance change coefficient according to the dynamic association result data.

[0033] As described in the above steps S301 - S304, the present invention provides an accurate and stable reference standard for subsequent analysis of the resistance change of the heating wire by obtaining multiple reference resistance values when the heating wire initially operates in historical data and using them as a reference line. The reference line is used to calibrate the initial state. The dynamic association data updates the window length = 3 respiratory cycles through a sliding window. By comprehensively analyzing multiple reference resistance values, the accidental error of a single data can be effectively eliminated, and the initial resistance state of the heating wire can be more accurately reflected. With a clear reference line, during the subsequent monitoring process, the resistance change of the heating wire under the respiratory cycle can be clearly compared, and it can be accurately determined whether the resistance change is caused by the temperature change during the normal breathing process. The temperature change time period of the heating wire under the respiratory cycle is obtained, and multiple temperature values are continuously extracted, and then the temperature change gradient at adjacent moments is generated. This method can delicately capture the dynamic change trend of the heating wire temperature during the breathing process. During the breathing process, factors such as the heat exchange between the air flow and the heating wire, and the changes in the patient's breathing frequency and intensity will cause fluctuations in the heating wire temperature. By continuously extracting temperature values and calculating gradients in this step, not only can the temperature data at each moment be obtained, but also the change rate of the temperature in the time dimension can be analyzed, and the temperature characteristics of the heating wire can be deeply understood from the perspective of dynamic changes. Compared with the traditional method of only measuring a single temperature value or measuring the temperature at a long interval, the introduction of the temperature change gradient can more accurately describe the change law of the heating wire temperature, enable the nebulizer to respond more sensitively to the temperature change of the heating wire, improve the accuracy of monitoring the patient's breathing state, and associate the resistance change value at each continuously extracted moment with the corresponding temperature change gradient, establishing a dynamic correspondence relationship between the resistance change and the temperature change of the heating wire, breaking through the simple and static understanding of the relationship between the two in the traditional method. The relationship between the resistance and the temperature of the heating wire is not a simple linear relationship. In different temperature ranges and change rates, the change characteristics of the resistance are different. By precisely associating the resistance change and the temperature change gradient at each moment in this step, the response law of the resistance under different temperature change conditions can be deeply analyzed, and the non-linear characteristics and dynamic change trends of the resistance-temperature relationship can be captured. For example, take a patient receiving nebulization treatment in a cold environment. In this environment, the cold air inhaled by the patient will cause the temperature of the heating wire to drop rapidly, and the temperature drop rate is different in different stages. In S304, when it is monitored that the temperature of the heating wire rapidly drops from 25°C to 20°C, the resistance change value at each moment is recorded simultaneously. Suppose when the temperature drops from 25°C to 24°C, the resistance changes from 10Ω to 10.2Ω; when the temperature drops from 24°C to 23°C, the resistance changes from 10.2Ω to 10.5Ω. Associate these resistance change values with the corresponding temperature change gradients. For example, when the temperature drops from 25°C to 24°C, the temperature change gradient is -10°C / s, and the resistance change corresponds to this temperature change gradient.Through this correlation analysis, it can be found that with different rates of temperature decrease, the variation amplitude and trend of the resistance are also different, and it is not a simple linear relationship. Based on these dynamic correlation result data, a temperature-resistance relationship model can be established more accurately, providing a reliable basis for calculating the temperature-resistance variation coefficient. For example, by appropriately increasing the heating power of the heating wire to compensate for the temperature drop of the heating wire caused by too low ambient temperature, ensuring the normal operation of the atomizer, improving the atomization treatment effect of patients in cold environments, generating a temperature-resistance variation coefficient according to the dynamic correlation result data, which comprehensively reflects the dynamic relationship between the resistance and temperature of the heating wire during the breathing cycle and can accurately quantify the influence degree of temperature change on the resistance. Through the detailed analysis of the reference resistance value, temperature change gradient, and the correlation between resistance and temperature change in the previous steps, a comprehensive and accurate data basis is provided for generating the temperature-resistance variation coefficient. This coefficient is no longer a fixed empirical value but is calculated based on the dynamic change data of the heating wire during the actual breathing process of the patient, with strong pertinence and adaptability. Applying this coefficient to the actual tidal volume calculation and other processes can more accurately consider the influence of temperature factors on resistance measurement, eliminate measurement errors caused by temperature changes, improve the accuracy of the atomizer in monitoring the patient's breathing volume, enable the atomizer to adjust the operating parameters more precisely according to the patient's true breathing state and environmental factors, and provide more effective atomization treatment for the patient.

[0034] In one embodiment, after the step of plotting a plurality of resistance values in the resistance time series into a curve to form a resistance change trend curve graph, it includes: S401. Obtain a plurality of inhalation curves and a plurality of exhalation curves according to the breathing cycle, generate a breathing spectrum through Fourier transform based on the plurality of inhalation curves and the plurality of exhalation curves, and extract the inhalation phase and exhalation phase of each breathing cycle from the breathing spectrum; S402. According to the inhalation curve of each breathing cycle, obtain the corresponding plurality of resistance values during the operation of the heating wire, and obtain the corresponding resistance change curve based on the plurality of resistance values; S403. Synchronize the time stamps of the starting points at the initial stage of the inhalation phase of each resistance change curve, obtain a plurality of resistance difference curves according to each resistance change curve, obtain the average value of the resistance difference curves based on the plurality of resistance difference curves, and obtain a resistance difference interval based on the plurality of resistance difference curves and the average value of the resistance difference curves; S404. Determine whether the resistance difference interval is within a preset interval; If it is within the preset interval, it is determined that the user's breathing is stable; If it is outside the preset interval, it is determined that the user's breathing is disordered.

[0035] As described in the above steps S401 - S404, the present invention deeply analyzes the respiratory signal from the frequency domain by obtaining multiple inhalation curves and exhalation curves, generating a respiratory spectrum using Fourier transform, and then extracting the inhalation phase and exhalation phase of each respiratory cycle. Fourier transform can decompose the complex respiratory curve in the time domain into different frequency components, making the characteristics of the respiratory signal clearer and more intuitive. By extracting the inhalation phase and exhalation phase, not only can the start and end moments of inhalation and exhalation in the respiratory cycle be accurately defined, but also the variation laws and frequency characteristics in different stages of the breathing process can be analyzed. This refined processing of the respiratory signal can capture the subtle changes in the respiratory signal more comprehensively and accurately compared with the traditional method of only observing the respiratory curve in the time domain. According to the inhalation curve of each respiratory cycle, multiple corresponding resistance values during the operation of the heating wire can be accurately obtained, and a resistance change curve can be drawn based on this, realizing the direct correlation between the breathing process and the change of the heating wire resistance. During the breathing process, the heat exchange between the air flow and the heating wire causes the resistance of the heating wire to change. This step can track the dynamic change of the heating wire resistance in each respiratory cycle in real time by closely combining the inhalation curve and the resistance value acquisition. By synchronizing the time stamp of the initial starting point of the inhalation phase of the resistance change curve, calculating the resistance difference curve and its mean and range, and introducing the concept of the standard deviation band, the respiratory stability can be evaluated more scientifically and intuitively. The time stamp synchronization ensures the accurate alignment of the resistance change curves in the time dimension under different respiratory cycles, providing a reliable basis for comparative analysis. The resistance difference curve highlights the uniqueness of the resistance change in each respiratory cycle, and calculating the mean of the resistance difference curve can obtain the average trend of the resistance change. On this basis, by calculating the standard deviation to determine the standard deviation band, the fluctuation range of the resistance change can be quantified. The standard deviation band reflects the degree of dispersion of the resistance data. The narrower its width, the more stable the resistance change, indirectly indicating that the influence of factors such as air flow and temperature on the heating wire during the breathing process is more consistent, and the respiratory stability is higher; on the contrary, the wider the standard deviation band, the greater the fluctuation of the resistance change, meaning that the respiratory state is unstable, and there may be situations such as disordered breathing rhythm and large changes in air flow intensity. This way of combining the resistance change with statistical methods and evaluating the respiratory stability through the standard deviation band can judge the patient's respiratory state more accurately and quantitatively compared with the traditional method of only observing the shape of the resistance change curve, providing a strong basis for the nebulizer to dynamically adjust parameters according to the respiratory stability, improving the accuracy and effectiveness of the aerosol therapy. In S403, after synchronizing the time stamp of the initial starting point of the inhalation phase of the resistance change curve, a series of resistance difference curves are calculated. Through statistical analysis of these curves, the mean of the resistance difference is obtained as 0.12Ω, and the calculated standard deviation is 0.03Ω, thus determining the standard deviation band as [0.09Ω, 0.15Ω]. At this time, the standard deviation band is relatively narrow, indicating that during the patient's breathing process at this stage, the change of the heating wire resistance fluctuates less, reflecting a relatively stable respiratory state.Based on this, the atomizer can maintain a regular atomization rate and parameters, ensuring stable drug delivery and maintaining the therapeutic effect.

[0036] Similarly, after performing step S403 and calculating the resistance difference curve, the mean value of the resistance difference becomes 0.18 Ω, the standard deviation increases to 0.08 Ω, and the standard deviation band becomes [0.1 Ω, 0.26 Ω]. The significant widening of the standard deviation band indicates that the resistance change fluctuation intensifies. This is due to the drastic changes in the intensity and frequency of the patient's respiratory airflow, which have an unstable impact on the heating wire, thereby reflecting the decline in the patient's respiratory stability. According to the respiratory instability situation shown by the standard deviation band, medical staff adjust the atomization rate to make the drug output more suitable for the patient's unstable breathing rhythm, avoiding the problem that the drug is quickly ejected due to rapid breathing and cannot be effectively inhaled. At the same time, the atomization time is increased to ensure that the patient can inhale a sufficient dose of the drug even in the state of unstable breathing, improving the pertinence and effectiveness of the treatment and alleviating the symptoms in the acute attack period of the patient.

[0037] In one embodiment, after the step of generating the temperature-resistance change coefficient according to the resistance change trend curve graph, the following steps are further included: S501. Obtain the inspiratory interval time period according to the respiratory cycle; S502. Set the target temperature value as the temperature at which the condensed water on the heating wire can be instantaneously evaporated; S503. Obtain the temperature value of the heating wire under the rated current; S504. Increase the current of the rated current by an increasing multiple to obtain an up-current rated current, and heat the heating wire according to the up-current rated current to obtain a first temperature value; S505. Determine whether the first temperature value reaches the target temperature value; If the target temperature value is not reached, return to the step of increasing the current of the rated current by an increasing multiple to obtain an up-current rated current until the target temperature value is reached and the process ends.

[0038] As described in the above steps S501 - S505, the present invention provides an ideal time window for the temperature regulation of the heating wire by accurately capturing the inspiratory pause time period in the breathing cycle. During the atomization treatment process, the patient's breathing airflow is relatively gentle during the inspiratory pause. At this time, adjusting the temperature of the heating wire can not only avoid interfering with the patient's normal inspiration but also efficiently handle the problems of condensed water or drug residues on the surface of the heating wire. Clearly setting the target temperature value as the temperature at which the condensed water on the heating wire can be instantaneously evaporated provides a precise quantitative standard for the temperature regulation of the heating wire. By setting this scientific and reasonable target temperature, it can be ensured that each time the temperature of the heating wire is adjusted, the condensed water on the surface can be quickly and effectively evaporated, preventing the formation of an adhesion layer by the mixture of condensed water and drug residues from the source, and thus maintaining the stability of the resistance characteristics of the heating wire. Compared with the traditional fuzzy or fixed temperature setting method, this step makes the temperature regulation more targeted and effective, significantly improving the working performance and reliability of the atomizer. Obtaining the temperature value of the heating wire under the rated current provides important basic data and a reference benchmark for subsequent temperature regulation. The rated current is the standard current for the normal operation of the heating wire, and the temperature value measured under this current truly reflects the initial working state of the heating wire. Compared with the method of blindly increasing the current without obtaining this basic temperature value, this step makes the temperature regulation process more controllable and precise, effectively avoiding the risk of damage to the heating wire due to excessive increase in current resulting in too high a temperature, and at the same time improving the efficiency of temperature regulation, ensuring that the heating wire can reach the target temperature value safely and quickly, maintaining the stable operation of the atomizer. By adopting the method of increasing the current in an increasing multiple according to the rated current, a refined and progressive regulation of the temperature of the heating wire is achieved. This current - increasing strategy avoids sudden jumps in temperature, enables the heating wire to remain stable during the heating process, effectively preventing thermal stress damage to the heating wire caused by rapid temperature changes, and prolonging the service life of the heating wire. At the same time, by gradually increasing the current and real - time monitoring the temperature, the current - increasing amplitude and speed can be flexibly adjusted according to the actual heating situation of the heating wire, ensuring the accuracy and controllability of temperature regulation, and constructing a closed - loop temperature regulation feedback mechanism. By real - time judging whether the temperature of the heating wire reaches the target value, dynamic control and precise optimization of the temperature regulation process are achieved. This feedback mechanism can automatically adjust the current - increasing strategy according to the actual heating situation of the heating wire, ensuring that the temperature of the heating wire always approaches the target temperature, effectively avoiding the problems of insufficient or excessive temperature regulation. Whether it is due to changes in breathing airflow caused by individual differences among different patients or in complex environmental conditions, this mechanism can flexibly respond, enabling the heating wire to quickly and accurately reach the temperature at which the condensed water on the heating wire can be instantaneously evaporated, continuously keeping the surface of the heating wire dry, maintaining the stability of its resistance characteristics, and thus ensuring the long - term stable and efficient operation of the atomizer, providing a reliable treatment guarantee for patients.

[0039] In one embodiment, the step of adjusting the drug output dose of the atomizer according to the actual tidal volume includes: S601. Obtain the target liquid medicine dose of the user; S602. Obtain the ideal tidal volume of the user according to the target liquid medicine dose and the liquid medicine ratio; S603. Obtain the ideal gas supply times according to the ideal tidal volume and the target liquid medicine dose; S604. Start gas supply according to the ideal gas supply times. After the gas supply ends, obtain the actual tidal volume corresponding to the ideal gas supply times; S605. Calculate the inhalation difference amount according to the actual tidal volume and the ideal tidal volume; S606. Determine whether the inhalation difference amount meets the preset interval value; If not, obtain the compensated liquid medicine dose according to the inhalation difference amount, and return the compensated liquid medicine dose as the target liquid medicine dose to the step of obtaining the ideal tidal volume of the user according to the target liquid medicine dose and the liquid medicine ratio; If it meets, end the gas supply.

[0040] As described in the above steps S601 - S606, when the user is atomizing, the liquid medicine may overflow due to the operation steps or exhalation. To prevent the user from having insufficient medication, doctors usually give a dose much larger than the actual medication dose when prescribing medicine to ensure the treatment effect of the user; Obtain the user's target liquid medicine dose, which is the starting point and core basis of the entire medicine supply process. Calculate the ideal tidal volume by combining the target liquid medicine dose and the liquid medicine ratio, fully considering the drug characteristics and the individual needs of the user. Different liquid medicines have different pharmacological properties and therapeutic concentration requirements. Calculating the ideal tidal volume through the liquid medicine ratio can ensure that the drug is inhaled at an appropriate concentration and dose. Calculate the ideal air supply frequency based on the ideal tidal volume and the target liquid medicine dose, providing a clear plan for the air supply process. This helps medical staff reasonably arrange the air supply time and frequency, avoiding the occurrence of over-air supply or insufficient air supply. Obtain the actual tidal volume after the air supply ends, which can timely understand the actual inhalation situation of the patient. The actual tidal volume is affected by various factors, such as the patient's breathing state, mood, equipment performance, etc. By obtaining the actual tidal volume in real time, accurate data support can be provided for subsequent adjustments. For example, if the patient coughs or has shortness of breath during the air supply process, the actual tidal volume will change. By obtaining this data, problems can be discovered and adjusted in a timely manner. Calculate the inhalation difference between the actual tidal volume and the ideal tidal volume, and quantitatively compare the actual inhalation situation with the ideal situation. This enables medical staff to intuitively understand the deviation degree during the treatment process and provide a clear basis for subsequent decisions. Judge whether the inhalation difference meets the preset value, which sets a quality control standard for the treatment process. The preset value is set based on the safety and effectiveness of the treatment. Through this judgment step, it can be ensured that the liquid medicine dose inhaled by the patient is within a reasonable range. For example, if the inhalation difference is too large, it may lead to insufficient or excessive drug dose, affecting the treatment effect or even causing adverse reactions. By judging whether it meets the preset value, such deviations can be discovered and corrected in a timely manner. When the inhalation difference does not meet the preset value, calculate the compensatory liquid medicine dose based on the inhalation difference and restart steps such as calculating the ideal tidal volume, forming a dynamic compensation adjustment mechanism. This enables the treatment process to be adjusted in real time according to the actual situation of the patient, ensuring that the target liquid medicine dose is finally achieved. For example, if the actual amount of liquid medicine inhaled by the patient is insufficient during a certain air supply, by calculating the compensatory liquid medicine dose and re-planning the air supply plan, the missing drug dose can be supplemented to ensure the treatment effect.

[0041] For example, assume that the target liquid medicine dose for the user is 10 milliliters, the liquid medicine ratio is 50 milliliters of tidal volume corresponding to each milliliter of liquid medicine, and the liquid medicine ratio is 1:50. Then the ideal tidal volume is 500 milliliters. According to the ideal tidal volume and the target liquid medicine dose, the ideal air supply frequency is calculated to be 10 times (ideal air supply frequency = ratio of ideal tidal volume to the inhalation volume of each milligram of liquid medicine). Start air supply according to the ideal air supply frequency. After 10 times of ideal air supply are completed, obtain the actual tidal volume corresponding to the ideal air supply frequency, and this actual tidal volume is 480 milliliters. The inhalation difference volume from the ideal tidal volume is 500 - 480 = 20 milliliters. Obtain the compensated liquid medicine dose according to the inhalation difference volume. Then the compensated liquid medicine dose is 0.4 milliliters. Take the compensated liquid medicine dose as the target liquid medicine dose and return to the step of obtaining the user's ideal tidal volume according to the target liquid medicine dose and the liquid medicine ratio. Subsequently, take 0.4 milliliters of the compensated liquid medicine dose as the new target liquid medicine dose and return to the step of calculating the ideal tidal volume. The new ideal tidal volume becomes 0.4 × 50 = 20 milliliters. Recalculate the ideal air supply frequency to be 1 time. Start air supply according to the ideal air supply frequency. After 1 time of ideal air supply is completed, obtain the actual tidal volume corresponding to the ideal air supply frequency, and this actual tidal volume is 48 milliliters. The inhalation difference volume from the ideal tidal volume is 50 - 48 = 2 milliliters. 2 milliliters satisfies the preset interval value, and air supply ends. After multiple adjustments, the target liquid medicine dose of 10 milliliters is finally reached, and medicine supply ends. In this process, by continuously adjusting the compensated liquid medicine dose according to the difference between the actual tidal volume and the ideal tidal volume, it is ensured that the user can accurately inhale the target liquid medicine dose, improving the treatment effect and safety.

[0042] The present application also provides a real-time respiratory volume monitoring system for a medical nebulizer, including: A first acquisition module for acquiring the initial atomization air flow rate of the medical nebulizer; A second acquisition module for acquiring the initial tidal volume information of the user in multiple respiratory cycles within a first preset time period, where the initial tidal volume information includes multiple respiratory signals; A first generation module for generating a power spectral density diagram by performing a fast Fourier transform on the multiple respiratory signals, extracting multiple inhalation waveforms according to the power spectral density diagram, and obtaining a tidal volume characteristic value according to the multiple inhalation waveforms; A third acquisition module for acquiring multiple resistance values and multiple temperature values generated by the heating wire corresponding to the medical nebulizer within multiple respiratory cycles of the user; A second generation module for generating a temperature-resistance change coefficient according to the multiple resistance values and the multiple temperature values; A fourth acquisition module for acquiring the actual atomization air flow rate according to the initial atomization air flow rate and the temperature-resistance change coefficient; A fifth acquisition module for acquiring the actual tidal volume according to the actual atomization air flow rate, the tidal volume characteristic value, and the temperature-resistance change coefficient; The sixth acquisition module adjusts the drug output dose of the nebulizer according to the actual tidal volume.

[0043] Preferably, the first generation module includes: The first acquisition unit extracts multiple waveform peaks from multiple inhalation waveforms, obtains multiple time intervals between the multiple waveform peaks according to a preset time series, and obtains the peak frequency according to the multiple time intervals; The second acquisition unit obtains multiple inhalation peaks according to multiple inhalation waveforms, obtains the average inhalation peak according to the multiple inhalation peaks, obtains the standard inhalation peak according to the multiple inhalation peaks and the average inhalation peak, and compares the multiple inhalation peaks with the standard inhalation peak in sequence to obtain abnormal inhalation peaks; The third acquisition unit obtains the inhalation time period; The fourth acquisition unit obtains the tidal volume characteristic value according to the peak frequency, the standard inhalation peak, the abnormal inhalation peak and the inhalation time period.

[0044] Preferably, the second generation module includes: The fifth acquisition unit obtains multiple reference resistance values when the heating wire starts to work in the historical data, and generates a reference line according to the multiple reference resistance values; The sixth acquisition unit obtains the temperature change time period of the heating wire in the respiratory cycle, continuously extracts multiple temperature values according to the temperature change time period, and generates the temperature change gradient at adjacent moments according to the extracted temperature values; The seventh acquisition unit obtains the resistance change value at each continuously extracted moment, and associates each resistance change value with the corresponding temperature change gradient to obtain the dynamic association result data; The first generation unit generates the temperature-resistance change coefficient according to the dynamic association result data.

[0045] Preferably, the second acquisition module includes: The eighth acquisition unit obtains multiple inhalation curves and multiple exhalation curves according to the respiratory cycle, generates a respiratory spectrum through Fourier transform according to the multiple inhalation curves and the multiple exhalation curves, and extracts the inhalation phase and the exhalation phase of each respiratory cycle from the respiratory spectrum; The ninth acquisition unit obtains the corresponding multiple resistance values during the operation of the heating wire according to the inhalation curve of each respiratory cycle, and obtains the corresponding resistance change curve according to the multiple resistance values; The tenth acquisition unit synchronizes the time stamps of the starting points of the inhalation phases of each resistance change curve, obtains multiple resistance difference curves according to each resistance change curve, obtains the average value of the resistance difference curves according to the multiple resistance difference curves, and obtains the resistance difference interval according to the multiple resistance difference curves and the average value of the resistance difference curves; The first judgment unit judges whether the resistance difference range is within a preset range; If it is within the preset range, it is determined that the user's breathing is stable; If it is outside the preset range, it is determined that the user's breathing is disordered.

[0046] Those of ordinary skill in the art can understand that all or part of the processes in the methods of the above embodiments can be completed by instructing relevant hardware through a computer program. The computer program can be stored in a non-volatile computer-readable storage medium. When the computer program is executed, it can include the processes of the embodiments of the above methods. Among them, any reference to a memory, storage, database or other medium provided in the present application and used in the embodiments can include non-volatile and / or volatile memories. Non-volatile memories can include read-only memory (ROM), programmable ROM (PROM), electrically programmable ROM (EPROM), electrically erasable programmable ROM (EEPROM) or flash memory. Volatile memories can include random access memory (RAM) or external cache memory. By way of illustration and not limitation, RAM is available in many forms, such as static RAM (SRAM), dynamic RAM (DRAM), synchronous DRAM (SDRAM), double data rate SDRAM (SSRSDRAM), enhanced SDRAM (ESDRAM), synchronous link (Synchlink) DRAM (SLDRAM), memory bus (Rambus) direct RAM (RDRAM), direct memory bus dynamic RAM (DRDRAM), and memory bus dynamic RAM (RDRAM), etc.

[0047] It should be noted that in this article, the terms "include", "comprise" or any other variant thereof are intended to cover non-exclusive inclusion, so that a process, apparatus, article or method including a series of elements not only includes those elements, but also includes other elements not expressly listed, or further includes elements inherent to such process, apparatus, article or method. Without further limitation, an element defined by the statement "including one..." does not exclude the existence of additional identical elements in the process, apparatus, article or method including that element.

[0048] The above are only the preferred embodiments of the present invention, and do not limit the patent scope of the present invention accordingly. Any equivalent structure or equivalent process transformation made by using the specification and drawings of the present invention, or directly or indirectly applied in other related technical fields, shall be equally included in the patent protection scope of the present invention.

Claims

1. A real-time monitoring method for the respiratory volume of a medical nebulizer, wherein an electric heating wire is provided inside the medical nebulizer, characterized in that, Including: Obtain the initial atomization air flow rate of the medical nebulizer; Obtain the initial tidal volume information of multiple respiratory cycles of the user within the first preset time period, where the initial tidal volume information includes multiple respiratory signals; The multiple respiratory signals generate a power spectral density map through fast Fourier transform, extract multiple inhalation waveforms according to the power spectral density map, and obtain tidal volume characteristic values according to the multiple inhalation waveforms; Obtain multiple resistance values and multiple temperature values generated by the heating wire corresponding to the medical nebulizer within multiple respiratory cycles of the user; Generate a temperature-resistance change coefficient according to the multiple resistance values and multiple temperature values; Obtain the actual atomization air flow rate according to the initial atomization air flow rate and the temperature-resistance change coefficient; Obtain the actual tidal volume according to the actual atomization air flow rate, the tidal volume characteristic value, and the temperature-resistance change coefficient; Adjust the drug output dose of the nebulizer according to the actual tidal volume.

2. The real-time monitoring method for respiratory volume of the medical nebulizer according to claim 1, wherein The step of obtaining the tidal volume characteristic value according to the multiple inhalation waveforms includes: Extract multiple waveform peak tips according to the multiple inhalation waveforms, obtain multiple time intervals between the multiple waveform peak tips according to a preset time sequence, and obtain the peak tip frequency according to the multiple time intervals; Obtain multiple inhalation peak values according to the multiple inhalation waveforms, obtain the inhalation peak average value according to the multiple inhalation peak values, obtain the standard inhalation peak value according to the multiple inhalation peak values and the inhalation peak average value, and compare the multiple inhalation peak values with the standard inhalation peak value in turn to obtain abnormal inhalation peak values; Obtain the inhalation time period; Obtain the tidal volume characteristic value according to the peak tip frequency, the standard inhalation peak value, the abnormal inhalation peak value, and the inhalation time period.

3. The real-time respiration volume monitoring method of the medical nebulizer according to claim 1, characterized in that The step of generating a temperature-resistance change coefficient according to the multiple resistance values and multiple temperature values includes: Obtain multiple reference resistance values when the heating wire initially operates in the historical data, and generate a reference line according to the multiple reference resistance values; Obtain the temperature change time period of the heating wire during the respiratory cycle, continuously extract multiple temperature values according to the temperature change time period, and generate the temperature change gradient between adjacent moments according to the extracted temperature values; Obtain the resistance change value at each continuously extracted moment, and associate each resistance change value with the corresponding temperature change gradient to obtain dynamic association result data; Generate a temperature-resistance change coefficient according to the dynamic association result data.

4. The real-time monitoring method for respiratory volume of the medical nebulizer according to claim 1, wherein, After the step of generating a temperature-resistance change coefficient according to the multiple resistance values and multiple temperature values, it includes: Obtain multiple inhalation curves and multiple exhalation curves according to the respiratory cycle, generate a respiratory spectrum through Fourier transform according to the multiple inhalation curves and multiple exhalation curves, and extract the inhalation phase and exhalation phase of each respiratory cycle according to the respiratory spectrum; According to the inhalation curve of each respiratory cycle, obtain the corresponding multiple resistance values during the operation of the heating wire, and obtain the corresponding resistance change curve according to the multiple resistance values; Synchronize the time stamps of the starting points of the inhalation phase initial stage of each resistance change curve, obtain multiple resistance difference curves according to each resistance change curve, obtain the average value of the resistance difference curves according to the multiple resistance difference curves, and obtain the resistance difference interval according to the multiple resistance difference curves and the average value of the resistance difference curves; Judge whether the resistance difference interval is within a preset interval; If it is within the preset interval, it is determined that the user's breathing is stable; If it is outside the preset interval, it is determined that the user's breathing is disordered.

5. The real-time monitoring method of respiratory volume of the medical nebulizer according to claim 1, characterized in that After the step of generating the temperature-resistance change coefficient according to multiple resistance values and multiple temperature values, it includes: Obtain the inspiratory interval time period according to the respiratory cycle; Set the target temperature value to the temperature at which the condensate on the instantaneously evaporable heating wire can be evaporated; Obtain the temperature value of the heating wire under the rated current; Increase the rated current by an increasing multiple to obtain an up-current rated current, and heat the heating wire according to the up-current rated current to obtain a first temperature value; Judge whether the first temperature value reaches the target temperature value; If the target temperature value is not reached, return to the step of increasing the rated current by an increasing multiple to obtain the up-current rated current until the target temperature value is reached and end.

6. The real-time monitoring method for respiratory volume of the medical nebulizer according to claim 1, characterized in that The step of adjusting the drug output dose of the atomizer according to the actual tidal volume includes: Obtain the user's target liquid medicine dose; Obtain the user's ideal tidal volume according to the target liquid medicine dose and the liquid medicine ratio; Obtain the ideal gas supply times according to the ideal tidal volume and the target liquid medicine dose; Start gas supply according to the ideal gas supply times. After the gas supply ends, obtain the actual tidal volume corresponding to the ideal gas supply times; Calculate the inhalation difference amount according to the actual tidal volume and the ideal tidal volume; Judge whether the inhalation difference amount meets the preset value interval; If it does not meet, obtain the compensation liquid medicine dose according to the inhalation difference amount, and use the compensation liquid medicine dose as the target liquid medicine dose and return to the step of obtaining the user's ideal tidal volume according to the target liquid medicine dose and the liquid medicine ratio; If it meets, end the gas supply.

7. A real-time respiratory volume monitoring system for a medical nebulizer, characterized in that, It includes: The first acquisition module acquires the initial atomization air flow rate of the medical atomizer; The second acquisition module acquires the initial tidal volume information of the user's multiple respiratory cycles within the first preset time period, wherein the initial tidal volume information includes multiple respiratory signals; The first generation module generates a power spectral density diagram through fast Fourier transform of the multiple respiratory signals, extracts multiple inspiratory waveforms according to the power spectral density diagram, and obtains tidal volume characteristic values according to the multiple inspiratory waveforms; The third acquisition module acquires multiple resistance values and multiple temperature values generated by the heating wire corresponding to the medical atomizer within the user's multiple respiratory cycles; The second generation module generates a temperature-resistance change coefficient according to the multiple resistance values and the multiple temperature values; The fourth acquisition module acquires the actual atomization air flow rate according to the initial atomization air flow rate and the temperature-resistance change coefficient; The fifth acquisition module acquires the actual tidal volume according to the actual atomization air flow rate, the tidal volume characteristic value, and the temperature-resistance change coefficient; The sixth acquisition module adjusts the drug output dose of the atomizer according to the actual tidal volume.

8. The real-time respiratory volume monitoring system of the medical nebulizer according to claim 7, characterized in that, The first generation module includes The first acquisition unit extracts multiple waveform peaks from the multiple inspiratory waveforms, obtains multiple time intervals between the multiple waveform peaks according to the preset time sequence, and obtains the peak frequency according to the multiple time intervals; The second acquisition unit obtains multiple inspiratory peaks according to the multiple inspiratory waveforms, obtains the inspiratory peak mean value according to the multiple inspiratory peaks, obtains the standard inspiratory peak value according to the multiple inspiratory peaks and the inspiratory peak mean value, and compares the multiple inspiratory peaks with the standard inspiratory peak value in turn to obtain abnormal inspiratory peaks; A third acquisition unit configured to acquire an inhalation time period; A fourth acquisition unit configured to acquire a tidal volume characteristic value according to a peak frequency, a standard inhalation peak value, an abnormal inhalation peak value, and an inhalation time period.

9. The real-time respiratory volume monitoring system of the medical nebulizer according to claim 7, wherein The second generation module includes A fifth acquisition unit configured to acquire a plurality of reference resistance values when the heating wire initially operates in historical data, and generate a reference line according to the plurality of reference resistance values; A sixth acquisition unit configured to acquire a temperature change time period of the heating wire in a respiratory cycle, continuously extract a plurality of temperature values according to the temperature change time period, and generate a temperature change gradient at adjacent moments according to the extracted temperature values; A seventh acquisition unit configured to acquire a resistance change value at each continuously extracted moment, and associate each resistance change value with the corresponding temperature change gradient to obtain dynamic association result data; A first generation unit configured to generate a temperature-resistance change coefficient according to the dynamic association result data.

10. The real-time respiratory volume monitoring system of a medical nebulizer according to claim 7, characterized in that, The second acquisition module includes An eighth acquisition unit configured to acquire a plurality of inhalation curves and a plurality of exhalation curves according to a respiratory cycle, generate a respiratory spectrum through Fourier transform according to the plurality of inhalation curves and the plurality of exhalation curves, and extract an inhalation phase and an exhalation phase of each respiratory cycle from the respiratory spectrum; A ninth acquisition unit configured to acquire a corresponding plurality of resistance values during the operation of the heating wire according to the inhalation curve of each respiratory cycle, and acquire a corresponding resistance change curve according to the plurality of resistance values; A tenth acquisition unit configured to synchronize the inhalation phase initial starting timestamp of each resistance change curve, acquire a plurality of resistance difference curves according to each resistance change curve, acquire an average value of the resistance difference curves according to the plurality of resistance difference curves, and acquire a resistance difference interval according to the plurality of resistance difference curves and the average value of the resistance difference curves; A first determination unit configured to determine whether the resistance difference interval is within a preset interval; If it is within the preset interval, it is determined that the user's breathing is stable; If it is outside the preset interval, it is determined that the user's breathing is disordered.

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