A method and system for oxygen flow control of a pediatric respiratory nebulization administration device

Abstract

The application provides an oxygen flow control method and system for a pediatric respiratory atomization drug delivery device, wherein a coefficient matrix of scattering light energy distribution under different light shielding degrees is constructed in advance based on the re-scattering effect of particles in an atomization airflow and a calibration experiment; a measurement area is arranged on the inner side of an atomization cup outlet of the pediatric respiratory atomization device, and scattering light energy distribution data of the atomized particles and light shielding degree data of the measurement area are synchronously collected; the particle size distribution of the particles in the atomization airflow is determined through the coefficient matrix, the scattering light energy distribution data and the light shielding degree data; the flow characteristic parameters of the medicine are collected, and the atomization efficiency of the medicine is determined according to the flow characteristic parameters; when the particle size distribution deviates from a preset pediatric applicable particle size range, the oxygen flow of the pediatric respiratory atomization device is adjusted within the child tolerance range according to the atomization efficiency. By adopting the scheme of the application, the oxygen flow in the atomization drug delivery process can be adjusted in real time according to the flow characteristics of the medicine.

Description

Technical Field

[0001] This application relates to the field of medical drug delivery technology, and more specifically, to a method and system for controlling oxygen flow in a pediatric respiratory nebulizer drug delivery device. Background Technology

[0002] Pediatric respiratory nebulization is an important means of treating respiratory diseases in children. By nebulizing drugs into tiny particles, they can act directly on the respiratory mucosa, which has the advantages of rapid onset of action and few side effects. Due to the narrow airways and sensitive mucosa of children, oxygen-driven nebulization has become the preferred method in pediatric clinical practice because of its high nebulization efficiency and ability to provide oxygen support at the same time. It is especially suitable for infants and young children with respiratory difficulties.

[0003] Existing oxygen-driven nebulization technologies mostly rely on fixed flow parameters, making it difficult to dynamically adapt to treatment needs. On the one hand, the particle size of nebulized particles directly affects the drug deposition site. The particle size suitable for pediatric use (1~5μm) needs to be strictly controlled, but existing technologies cannot monitor particle size distribution in real time. Often, the particle size is too large, resulting in insufficient drug deposition, or too small, causing the risk of choking. On the other hand, differences in drug flow characteristics (such as viscosity and surface tension) can significantly affect nebulization efficiency. Traditional devices lack targeted adjustment mechanisms, and oxygen flow rate adjustment is mostly based on experience, making it difficult to achieve precise optimization within the range that children can tolerate (0.5~2L / min), thus affecting the treatment effect. Therefore, how to adjust the oxygen flow rate in the nebulization drug delivery process in real time according to the drug flow characteristics has become a challenge for the industry. Summary of the Invention

[0004] This application provides a method and system for controlling oxygen flow in a pediatric respiratory nebulizer drug delivery device, which can adjust the oxygen flow in real time during the nebulizer drug delivery process according to the drug flow characteristics.

[0005] In a first aspect, this application provides a method for controlling the oxygen flow rate of a pediatric respiratory nebulizer, comprising: A coefficient matrix of scattered light energy distribution under different shading levels was constructed in advance based on the complex scattering effect of particles in the atomized airflow and in conjunction with calibration experiments. A measurement area is set inside the outlet of the nebulizer cup of the pediatric respiratory nebulizer. A laser beam is emitted into the measurement area, and the scattered light energy distribution data of the nebulized particles and the shading data of the measurement area are collected simultaneously. The particle size distribution in the atomized airflow is obtained by inverting the particle size using the coefficient matrix, the scattered light energy distribution data, and the shading data. The flow characteristics parameters of the drug are collected in the connection channel between the drug cup and the core nebulization component of the pediatric respiratory nebulizer, and the nebulization efficiency of the drug is determined based on the flow characteristics parameters. When the particle size distribution deviates from the preset pediatric applicable particle size range, the oxygen flow rate of the pediatric respiratory nebulizer is adjusted within the tolerance range of the child's inhaled oxygen concentration based on the degree and nature of the particle size distribution deviation and in conjunction with the nebulization efficiency.

[0006] In some embodiments, the coefficient matrix for the distribution of scattered light energy under different shading levels is constructed in advance based on the complex scattering effect of particles in the atomized airflow and in conjunction with calibration experiments, specifically including: Simulation of scattered light energy distribution data under different shading levels based on the complex scattering effect of particles in atomized airflow; Calibration experiments were conducted using standard particles of known size to obtain actual scattered light energy distribution data under different shading levels. The scattered light energy distribution data and the actual scattered light energy distribution data are reconstructed into a coefficient matrix of scattered light energy distribution under different shading levels.

[0007] In some embodiments, the particle size distribution in the atomized airflow is obtained by inverting the particle size using the coefficient matrix, scattered light energy distribution data, and shading data, specifically including: The scattering fluctuation domain is determined based on the shading data and the coefficient matrix; The scattered light energy distribution data is substituted into the scattering wave domain to invert the particle size in the atomized gas flow, thereby obtaining the particle size distribution in the atomized gas flow.

[0008] In some embodiments, determining the atomization efficiency of the drug based on the flow characteristic parameters specifically includes: Based on the aforementioned flow characteristic parameters and the diameter of the nozzle in the atomizing chamber of the atomizing device, a shear force model of the drug under different oxygen flow rates is established. The critical conditions for the breakup of atomized drug droplets are determined based on fluid mechanics and the aforementioned flow characteristic parameters. The atomization efficiency of the drug is determined by the critical conditions and the shear force model.

[0009] In some embodiments, adjusting the oxygen flow rate of the pediatric respiratory nebulizer within the tolerance range of the child's inhaled oxygen concentration, based on the degree and nature of the particle size distribution deviation and in conjunction with the nebulization efficiency, specifically includes: Determine the degree and nature of the deviation in particle size distribution; The oxygen adjustment amount is determined based on the degree of deviation of the particle size distribution and the atomization efficiency; The oxygen flow rate of the pediatric respiratory nebulizer is adjusted within the tolerance range of the oxygen concentration inhaled by children, based on the oxygen adjustment amount and the properties of the particle size distribution deviation.

[0010] In some embodiments, the scattered light energy distribution data of the atomized particles and the shading data of the measurement area are acquired simultaneously by a Fourier lens and a charge-coupled device camera.

[0011] In some embodiments, the flow characteristic parameters include the dynamic viscosity, density, flow rate, and surface tension of the drug during flow.

[0012] In some embodiments, the pediatric respiratory nebulizer is an oxygen-driven nebulizer.

[0013] In some embodiments, emitting a laser beam toward the measurement area specifically includes: forming a parallel collimated beam by using a laser emitter in conjunction with an attenuator, a beam expander, and an aperture, and emitting the parallel collimated beam toward the measurement area.

[0014] Secondly, this application provides an oxygen flow control system for a pediatric respiratory nebulizer, comprising: The preprocessing module is used to pre-construct the coefficient matrix of scattered light energy distribution under different shading levels based on the complex scattering effect of particles in the atomized airflow and in conjunction with calibration experiments. The acquisition module is used to set a measurement area inside the nebulizer cup outlet of the pediatric respiratory nebulizer, emit a laser beam into the measurement area, and simultaneously acquire the scattered light energy distribution data of the atomized particles and the shading data of the measurement area. The processing module is used to invert the particle size in the atomized airflow using the coefficient matrix, the scattered light energy distribution data, and the shading data, to obtain the particle size distribution in the atomized airflow. The processing module is also used to collect the flow characteristic parameters of the drug in the connection channel between the drug cup and the nebulization core component of the pediatric respiratory nebulizer, and to determine the nebulization efficiency of the drug based on the flow characteristic parameters. The execution module is used to adjust the oxygen flow rate of the pediatric respiratory nebulizer within the tolerance range of the child's inhaled oxygen concentration when the particle size distribution deviates from the preset pediatric applicable particle size range, based on the degree and nature of the deviation and in combination with the nebulization efficiency.

[0015] The technical solutions provided by the embodiments disclosed in this application have the following beneficial effects: The oxygen flow control system and method for the pediatric respiratory nebulizer provided in this application firstly constructs a coefficient matrix of scattered light energy distribution under different shading levels based on the complex scattering effect of particles in the nebulized airflow and calibration experiments. A measurement area is set inside the nebulizer cup outlet of the pediatric respiratory nebulizer, and a laser beam is emitted into the measurement area while simultaneously collecting scattered light energy distribution data of the nebulized particles and shading level data of the measurement area. The particle size distribution in the nebulized airflow is obtained by inverting the particle size using the coefficient matrix, scattered light energy distribution data, and shading level data. The flow characteristic parameters of the medicine are collected in the connection channel between the medicine cup and the nebulizer core component of the pediatric respiratory nebulizer, and the nebulization efficiency of the medicine is determined based on these flow characteristic parameters. When the particle size distribution deviates from the preset pediatric applicable particle size range, the oxygen flow rate of the pediatric respiratory nebulizer is adjusted within the tolerance range of the child's inhaled oxygen concentration based on the degree and nature of the deviation and the nebulization efficiency.

[0016] Therefore, this application pre-constructs a coefficient matrix of scattered light energy distribution under different shading levels based on the complex scattering effect of particles in the atomized airflow and calibration experiments, providing a reliable foundation for the subsequent accurate inversion of particle size. A measurement area is integrated inside the nebulizer cup outlet, and a miniaturized laser emitter is used to emit laser light, simultaneously collecting scattered light energy distribution data and shading level data, enabling real-time monitoring of the atomized particle state. The particle size distribution is obtained by inverting the coefficient matrix, scattered light energy distribution data, and shading level data, allowing for accurate understanding of the atomized particle size. A miniature rheometer is integrated in the connection channel between the medicine cup and the core nebulizer component to collect drug flow characteristic parameters and determine nebulization efficiency, allowing for targeted understanding of drug nebulization performance. When the particle size distribution deviates from the pediatric applicable range, the oxygen flow rate is adjusted within the child's tolerance range based on the degree and nature of the deviation and the nebulization efficiency. Ultimately, this achieves precise control of particle size and dynamic optimization of nebulization effect during pediatric respiratory nebulization, improving the safety and effectiveness of treatment. In summary, the scheme of this application can adjust the oxygen flow rate in real time during nebulized drug administration based on the drug flow characteristics. Attached Figure Description

[0017] Figure 1 This is an exemplary flowchart of an oxygen flow control method for a pediatric respiratory nebulizer according to some embodiments of this application; Figure 2 This is an exemplary flowchart illustrating the determination of the coefficient matrix according to some embodiments of this application; Figure 3 This is an exemplary flowchart illustrating the adjustment of oxygen flow rate according to some embodiments of this application; Figure 4This is a schematic diagram of the structure of the oxygen flow control system of a pediatric respiratory nebulizer according to some embodiments of this application; Figure 5 This is a schematic diagram of the structure of a computer device for implementing an oxygen flow control method for a pediatric respiratory nebulizer according to some embodiments of this application. Detailed Implementation

[0018] To better understand the technical solution of this application, the technical solution of this application will be described in detail below with reference to the accompanying drawings and specific embodiments.

[0019] refer to Figure 1 The figure is an exemplary flowchart of an oxygen flow control method for a pediatric respiratory nebulizer according to some embodiments of this application. The oxygen flow control method for the pediatric respiratory nebulizer mainly includes the following steps: In step 101, a coefficient matrix of scattered light energy distribution under different shading levels is constructed in advance based on the complex scattering effect of particles in the atomized airflow and in conjunction with calibration experiments.

[0020] In some embodiments, reference Figure 2 The figure is an exemplary flowchart of determining the coefficient matrix according to some embodiments of this application. The coefficient matrix of scattered light energy distribution under different shading degrees, which is constructed in advance based on the complex scattering effect of particles in the atomized airflow and combined with calibration experiments, can be achieved by the following steps: In step 1011, the scattered light energy distribution data under different shading levels are simulated based on the complex scattering effect of particles in the atomized airflow. In step 1012, a calibration experiment is conducted using standard particles of known size to obtain actual scattered light energy distribution data under different shading levels; In step 1013, the scattered light energy distribution data and the actual scattered light energy distribution data are reconstructed into a coefficient matrix of scattered light energy distribution under different shading degrees.

[0021] In practical implementation, the simulation of scattered light energy distribution data under different shading levels based on the complex scattering effect of particles in the atomized airflow can be achieved in the following way: A laser scattering model can be constructed using the Monte Carlo method in existing technologies. This involves abstracting the incident laser as discrete photons and simulating their propagation path in the atomized airflow. When constructing the laser scattering model, key parameters need to be set. These key parameters include, but are not limited to: particle size range, relative refractive index, medium thickness, laser wavelength, particle shape (spherical or non-spherical; in the medical atomization field, spherical is usually used), and scattering angle detection range. The destinations of photons under single scattering and complex scattering are statistically analyzed. These destinations include: transmission, absorption, escape, or capture by the receiver. Specifically, the statistical analysis of photon destinations under single scattering and complex scattering can be achieved in the following way: Each photon is assigned an initial weight (…). When photons collide with particles, the scattering direction is randomly determined according to the probability distribution of the scattering angle, and the number of scatterings is recorded (distinguishing between single scattering and complex scattering). If a photon is absorbed, escapes from the measurement area (escapes), or reaches the detector (is captured), the tracking is terminated. Finally, the number of photons in each direction is counted, and the scattered light energy distribution is calculated based on the number of scattered photons received by each ring of the detector. In specific implementation, for example, the number of scattered photons received by each ring can be divided by the sum of the number of scattered photons received by all rings as the proportion of scattered light energy of each ring, and the set of all the scattered light energy proportions is taken as the scattered light energy distribution. Subsequently, the shading degree is adjusted by changing the concentration of particles in the atomized airflow. The shading degree can be quantified by the number of transmitted photons. Finally, the above simulation process is repeated, and the set of all the obtained scattered light energy distributions is taken as the scattered light energy distribution data under different shading degrees.

[0022] It should be noted that the scattered light energy distribution data in this application is a collection of the proportions of scattered light energy received by each ring of the detector obtained by simulating the complex scattering process of particles in the atomized airflow under different shading levels.

[0023] In practice, calibration experiments are conducted using standard particles of known diameters. The actual scattered light energy distribution data under different shading levels can be obtained in the following way: First, a synchronous measurement system is built, including a laser, attenuator, beam expander, aperture, sample cell, Fourier lens, CCD (charge-coupled device) camera, and spectrometer. The standard particles are prepared into suspensions of different concentrations and injected into the sample cell. The laser emits a laser of a specific wavelength (e.g., 650 nm), which, after attenuation and beam expansion, forms a parallel beam that illuminates the sample cell. The scattered light energy distribution is collected by the CCD camera, and the transmitted light intensity is analyzed by the spectrometer to calculate the number of transmitted photons. The ratio of the number of transmitted photons to the intensity of the laser emitted by the laser is taken as the shading level. Finally, the above measurement process is repeated for standard particle suspensions of different concentrations, and the set of all obtained scattered light energy distributions is taken as the actual scattered light energy distribution data under different shading levels.

[0024] It should be noted that the actual scattered light energy distribution data in this application is a collection of the proportion of scattered light energy of each ring of the detector actually collected under different shading levels using standard particles of known size for calibration experiments.

[0025] In specific implementation, the reconstruction of the scattered light energy distribution data and the actual scattered light energy distribution data into a coefficient matrix of scattered light energy distribution under different shading degrees can be achieved in the following way: First, the scattered light energy distribution data and the actual scattered light energy distribution data are grouped according to the shading degree, so that each group of data corresponds to the same shading degree interval. Then, for each shading degree interval, the simulated scattered light energy distribution and the actual scattered light energy distribution within the interval are arranged in order according to the light energy ratio of each ring of the detector. The rows of the matrix correspond to different detector ring numbers, and the columns correspond to different particle size levels. The resulting matrix is ​​used as the coefficient matrix of scattered light energy distribution under different shading degrees.

[0026] It should be noted that the coefficient matrix in this application is a matrix composed of correlation coefficients used to correlate the scattered light energy distribution and the particle size.

[0027] It should be noted that in constructing the coefficient matrix in this application, by keeping parameters such as drug concentration and gas flow rate stable (e.g., fixing the flow rate at 1 L / min and the concentration at 0.5 g / mL), only the particle size is changed, thereby establishing the correlation between particle size and scattered light energy distribution.

[0028] In step 102, a measurement area is set inside the nebulizer cup outlet of the pediatric respiratory nebulizer. A laser beam is emitted into the measurement area, and the scattered light energy distribution data of the nebulized particles and the shading data of the measurement area are collected simultaneously.

[0029] It should be noted that the pediatric respiratory nebulizer in this application is an oxygen-driven nebulizer. In practice, the measurement area can be set inside the nebulizer cup outlet of the pediatric respiratory nebulizer in the following way: a transparent sample cell can be set as the measurement area along the direction of the nebulized airflow at the outlet end.

[0030] In a specific implementation, the laser beam emitted toward the measurement area can be achieved in the following way: First, a parallel collimated beam is generated and then emitted toward the measurement area. The parallel collimated beam can be generated by existing optical hardware. For example, a miniaturized laser emitter can be arranged on the left side of the measurement area. The laser emitter uses a laser of a specific wavelength (650nm in this application), and is combined with an attenuator, beam expander and aperture to form a parallel collimated beam, which is then emitted toward the measurement area.

[0031] Furthermore, in a specific implementation, the simultaneous acquisition of scattered light energy distribution data of atomized particles and shading data of the measurement area can be achieved in the following manner: a receiving component is arranged on the right side of the measurement area, wherein the receiving component includes a Fourier lens and a CCD camera. The Fourier lens is used to focus the scattered light onto the focal plane, and the CCD camera is placed at the focal plane to receive scattered light signals at different angles. At the same time, a halogen lamp is set between the transmitter and the sample cell, and a spectrometer is set between the sample cell and the receiving component respectively. The shading in the measurement space is measured simultaneously by the halogen lamp and the spectrometer.

[0032] As a preferred embodiment, miniaturized components can be used, namely, a miniaturized laser emitter (5mm in diameter), a Fourier lens (8mm in diameter), and a miniature CCD (10×10mm) integrated into an annular groove inside the outlet of the atomizing cup (annular space diameter 15mm, depth 5mm). The halogen lamp and the spectrometer optical path are perpendicular to the laser optical path (to avoid direct interference), and the signal is transmitted through an optical fiber. Furthermore, an airflow buffer chamber (5mL in volume) can be set upstream of the measurement area to reduce airflow fluctuations caused by breathing. During data acquisition, only the stable inspiratory segment of the respiratory cycle (identified by a pressure sensor) is selected to eliminate exhalation interference data and ensure measurement stability.

[0033] In step 103, the particle size distribution in the atomized airflow is obtained by inverting the particle size using the coefficient matrix, the scattered light energy distribution data, and the shading data.

[0034] In some embodiments, the particle size distribution in the atomized gas stream can be obtained by inverting the particle size using the coefficient matrix, scattered light energy distribution data, and shading data through the following steps: The scattering fluctuation domain is determined based on the shading data and the coefficient matrix; The scattered light energy distribution data is substituted into the scattering wave domain to invert the particle size in the atomized gas flow, thereby obtaining the particle size distribution in the atomized gas flow.

[0035] In specific implementation, the scattering fluctuation domain determined based on the shading data and the coefficient matrix can be achieved in the following way: First, a shading interval is preset, for example, divided into intervals of 0-0.1, 0.1-0.2, ..., 0.9-1.0 with an interval of 0.1. Second, the currently collected shading data is compared with these preset intervals to determine its specific interval range. Then, based on the correlation information of scattered light energy distribution and particle size corresponding to each shading interval constructed in the coefficient matrix, data consistent with the current shading interval is selected from the coefficient matrix. The selected data covers the scattered light energy distribution characteristics corresponding to particles of different sizes under the shading degree, including the proportion of scattered light energy received by each ring of the detector, light energy data at different scattering angles, and other key information. The selected data is used as the scattering fluctuation domain matching the current shading degree.

[0036] It should be noted that the scattering fluctuation domain in this application is a matrix that corresponds to the current shading level range and contains the distribution characteristics of scattered light energy from particles of different sizes.

[0037] In specific implementation, the scattered light energy distribution data is substituted into the scattering wave domain to invert the particle size in the atomized airflow. The particle size distribution in the atomized airflow can be obtained in the following way: First, the collected scattered light energy distribution data is mapped to the row vector of the scattering wave domain according to the light energy proportion of each ring of the detector, ensuring that the data format is consistent with the arrangement rules of scattered light energy in the scattering wave domain. Then, the particle size is divided into 100 ranges from 0.5 to 20 µm. Using the differential evolution algorithm in non-independent mode, based on the correlation between the scattered light energy distribution and particle size in the scattering wave domain, iterative calculations are performed to make the scattered light energy distribution corresponding to the inverted particle size distribution match the actual collected data. To minimize data deviation, the output result with the smallest deviation is taken as the particle size distribution in the atomized airflow. In specific implementation, for example, to ensure that the deviation between the scattered light energy distribution corresponding to the particle size distribution and the actual collected data is minimized, the objective function is set as f=Σ|SD-SC|² (where SD is the predicted scattered light energy distribution and SC is the actual collected data). Multiple sets of particle size distribution parameters (such as the proportion of 100 particle size ranges) are initialized, and new parameter sets are generated through mutation and crossover operations. The parameter set with the smaller objective function value is retained until the objective function value converges (i.e., the relative deviation between the two calculations of the objective function value is less than 1%), and the objective function value when the objective function value converges is taken as the minimum deviation.

[0038] It should be noted that the particle size distribution in this application is a probability distribution function that quantifies the particle distribution in the atomized airflow.

[0039] In step 104, the flow characteristics parameters of the drug are collected in the connection channel between the drug cup and the core nebulization component of the pediatric respiratory nebulizer, and the nebulization efficiency of the drug is determined based on the flow characteristics parameters.

[0040] In specific implementation, the flow characteristic parameters of the drug can be collected in the connection channel between the drug cup and the core nebulization component of the pediatric respiratory nebulizer in the following way: the flow characteristic parameters of the drug are collected in real time in the straight section of the connection channel. The flow characteristic parameters include the dynamic viscosity, density, flow rate and surface tension of the drug. Furthermore, the collection of flow characteristic parameters can be achieved through existing fluid measurement hardware. For example, an installation position matching the size of the micro rheometer probe can be selected in the straight section of the connection channel, and the measuring probe of the micro rotational rheometer can be integrated into the inner wall of the channel through an embedded sealed interface. The measuring end of the probe is in direct contact with the drug flow path in the channel. The micro rheometer collects the flow characteristic parameters of the drug in real time through the probe. It should be noted that the flow characteristic parameters in this application are parameters that describe the flow characteristics of the drug, including the dynamic viscosity, density, flow rate and surface tension of the drug during flow.

[0041] In some embodiments, determining the atomization efficiency of the drug based on the flow characteristic parameters can be achieved through the following steps: Based on the aforementioned flow characteristic parameters and the diameter of the nozzle in the atomizing chamber of the atomizing device, a shear force model of the drug under different oxygen flow rates is established. The critical conditions for the breakup of atomized drug droplets are determined based on fluid mechanics and the aforementioned flow characteristic parameters. The atomization efficiency of the drug is determined by the critical conditions and the shear force model.

[0042] In specific implementation, the shear force model of the drug under different oxygen flow rates can be established based on the flow characteristic parameters and the diameter of the nozzle of the atomizing chamber in the atomizing device in the following way: First, obtain the diameter of the nozzle of the atomizing chamber in the atomizing device and calculate the corresponding flow area A. Then, convert the oxygen flow rate Q into the airflow velocity v (v=Q / A). Then, based on the Euler model in fluid mechanics, combined with the dynamic viscosity μ and density ρ in the drug flow characteristic parameters, use the shear stress formula τ=0.5Pv²C (where C is the drag coefficient, calculated by the Reynolds number, and P is the oxygen density, which is a parameter manually input on the atomizing device and can be directly obtained) to calculate the shear stress τ of the airflow on the droplet. The functional relationship τ=f(Q) of τ changing with the flow rate Q is obtained, and this functional relationship is used as the shear force model of the drug under different oxygen flow rates.

[0043] It should be noted that the shear force model in this application is a functional model that reflects the relationship between oxygen flow rate and droplet interaction force.

[0044] In specific implementation, the critical condition for the breakup of atomized drug droplets based on fluid mechanics and the aforementioned flow characteristic parameters can be achieved in the following way: First, extract the dynamic viscosity, density, flow velocity, and surface tension of the drug from the flow characteristic parameters. Combine this with the current airflow velocity of the atomizing device and the initial droplet diameter. Based on the Euler-Lagrange model in fluid mechanics, calculate the Weber number, which characterizes the gas-liquid interaction, and the Reynolds number, which reflects the influence of viscous forces. Then, determine the critical threshold for droplet breakup of the drug under the current flow characteristics through the correlation between the critical Weber number and the Reynolds number. That is, when the calculated Weber number exceeds this threshold, the droplet breaks up. This critical threshold is used as the critical condition for the breakup of atomized drug droplets.

[0045] It should be noted that the critical condition in this application is used to quantify the mechanical boundary at which a droplet begins to break up under specific flow characteristics.

[0046] In specific implementation, the determination of drug atomization efficiency through the critical conditions and the shear force model can be achieved in the following way: First, substitute the Weber number formula into the critical conditions to obtain the droplet diameter under the critical state. Then, combine the correlation between shear stress τ and airflow velocity v in the shear force model to derive the mapping relationship between droplet diameter and shear stress under the critical state. Subsequently, use the shear force model τ=f(Q) to obtain the shear stress τ corresponding to different oxygen flow rates Q. Substitute it into the above mapping relationship to calculate the critical droplet diameter d(Q) under each flow rate, which is the theoretical particle size after droplet breakage under this flow rate. Finally, select two adjacent oxygen flow rate values ​​Q1 and Q2 (e.g., Q2=Q1+1L / min) and obtain the corresponding theoretical particle sizes d1 and d2 respectively. By calculating the ratio of the difference between the two to the flow rate difference k=(d2-d1) / (Q2-Q1), the change in atomized particle size when the oxygen flow rate changes by 1L / min is obtained. This ratio k is taken as the drug atomization efficiency.

[0047] It should be noted that in this application, atomization efficiency is a parameter value used to quantify the degree of influence of gas flow rate on atomized particle size.

[0048] In step 105, when the particle size distribution deviates from the preset pediatric applicable particle size range, the oxygen flow rate of the pediatric respiratory nebulizer is adjusted within the tolerance range of the child's inhaled oxygen concentration based on the degree and nature of the particle size distribution deviation and in conjunction with the nebulization efficiency.

[0049] It should be noted that the pediatric applicable particle size range in this application can be set as the commonly used 1-5 micrometer range in pediatrics, according to industry common knowledge.

[0050] In some embodiments, reference Figure 3 The figure is an exemplary flowchart illustrating the adjustment of oxygen flow rate according to some embodiments of this application. The adjustment of the oxygen flow rate of the pediatric respiratory nebulizer within the tolerance range of oxygen concentration for children, based on the degree and nature of particle size distribution deviation and in conjunction with the nebulization efficiency, can be achieved using the following steps: In step 1051, the degree and nature of the particle size distribution deviation are determined; In step 1052, the oxygen adjustment amount is determined based on the degree of deviation of the particle size distribution and the atomization efficiency; In step 1053, the oxygen flow rate of the pediatric respiratory nebulizer is adjusted within the tolerance range of the oxygen concentration inhaled by the child, based on the oxygen adjustment amount and the nature of the particle size distribution deviation.

[0051] In practice, the degree and nature of the particle size distribution deviation can be determined as follows: First, the average value of the particle size distribution is determined. Then, the average value is compared with a preset target particle size range. If the average value is lower than the minimum value of the target particle size range, the particle size distribution deviation is recorded as too small. If the average value is higher than the maximum value of the target particle size range, the deviation is recorded as too large. Then, the difference between the average value and the median value of the target particle size range is taken as the degree of particle size distribution deviation.

[0052] In practice, the oxygen adjustment amount can be determined based on the degree of deviation of the particle size distribution and the atomization efficiency in the following way: the value obtained by dividing the degree of deviation of the particle size distribution by the atomization efficiency is used as the oxygen adjustment amount.

[0053] In practice, adjusting the oxygen flow rate of the pediatric respiratory nebulizer within the tolerance range of the child's inhaled oxygen concentration, based on the oxygen adjustment amount and the nature of the particle size distribution deviation, can be achieved in the following way: if the particle size distribution deviation is too small, the oxygen flow rate of the pediatric respiratory nebulizer is reduced by L; if the particle size distribution deviation is too large, the oxygen flow rate of the pediatric respiratory nebulizer is increased by L, where L is the oxygen adjustment amount. The adjusted oxygen flow rate is limited to the tolerance range of the child's inhaled oxygen concentration, which is set by industry professionals based on common knowledge as 0.5~2L / min.

[0054] In another aspect, in some embodiments, this application provides an oxygen flow control system for a pediatric respiratory nebulizer, with reference to... Figure 4The figure is a schematic diagram of the structure of the oxygen flow control system of a pediatric respiratory nebulizer according to some embodiments of this application. The oxygen flow control system 400 of the pediatric respiratory nebulizer includes: a preprocessing module 401, a data acquisition module 402, a processing module 403, and an execution module 404, which are described below: Preprocessing module 401, in this application, is mainly used to pre-construct the coefficient matrix of scattered light energy distribution under different shading degrees based on the complex scattering effect of particles in the atomized airflow and in conjunction with calibration experiments. The acquisition module 402 in this application is mainly used to set up a measurement area inside the outlet of the nebulizer cup of the pediatric respiratory nebulizer, emit a laser beam to the measurement area, and simultaneously acquire the scattered light energy distribution data of the nebulized particles and the shading data of the measurement area. Processing module 403, in this application, is mainly used to invert the particle size in the atomized airflow through the coefficient matrix, the scattered light energy distribution data and the shading data, so as to obtain the particle size distribution in the atomized airflow. It should be noted that the processing module 403 in this application is also used to collect the flow characteristic parameters of the drug in the connection channel between the drug cup and the nebulization core component of the pediatric respiratory nebulizer, and to determine the nebulization efficiency of the drug based on the flow characteristic parameters. The execution module 404 in this application is mainly used to adjust the oxygen flow rate of the pediatric respiratory nebulizer according to the degree and nature of the deviation of the particle size distribution and in combination with the nebulization efficiency within the tolerance range of the oxygen concentration inhaled by children when the particle size distribution deviates from the preset pediatric applicable particle size range.

[0055] In addition, this application also provides a computer device, the computer device including a memory and a processor, the memory storing code, the processor being configured to acquire the code and execute the oxygen flow control method of the pediatric respiratory nebulizer described above.

[0056] In some embodiments, reference Figure 5 The figure is a schematic diagram of the structure of a computer device for implementing an oxygen flow control method for a pediatric respiratory nebulizer according to some embodiments of this application. The oxygen flow control method for the pediatric respiratory nebulizer in the above embodiments can be achieved through… Figure 5 The computer device shown is used to implement this, and the computer device 500 includes at least one processor 501, a communication bus 502, a memory 503, and at least one communication interface 504.

[0057] Processor 501 can be a general-purpose central processing unit (CPU) or an application-specific integrated circuit (ASIC).

[0058] The communication bus 502 can be used to transmit information between the aforementioned components.

[0059] Memory 503 may be a read-only memory (ROM) or other type of static storage device capable of storing static information and instructions, random access memory (RAM) or other type of dynamic storage device capable of storing information and instructions, or electrically erasable programmable read-only memory (EEPROM), compact disc read-only memory (CD-ROM) or other optical disc storage, optical disc storage (including compressed optical discs, laser discs, optical discs, digital versatile optical discs, Blu-ray discs, etc.), magnetic disks or other magnetic storage devices, or any other medium capable of carrying or storing desired program code in the form of instructions or data structures and accessible by a computer, but not limited thereto. Memory 503 may exist independently and be connected to processor 501 via communication bus 502. Memory 503 may also be integrated with processor 501.

[0060] The memory 503 stores program code for executing the scheme of this application, and its execution is controlled by the processor 501. The processor 501 executes the program code stored in the memory 503. The program code may include one or more software modules. The oxygen flow control method of the pediatric respiratory nebulizer in the above embodiments can be implemented by the processor 501 and one or more software modules in the program code in the memory 503.

[0061] Communication interface 504 uses any transceiver-like device to communicate with other devices or communication networks, such as Ethernet, radio access network (RAN), wireless local area networks (WLAN), etc.

[0062] In a specific implementation, as one example, a computer device may include multiple processors, each of which may be a single-core (single-CPU) processor or a multi-core (multi-CPU) processor. Here, a processor may refer to one or more devices, circuits, and / or processing cores used to process data (e.g., computer program instructions).

[0063] The aforementioned computer device can be a general-purpose computer device or a special-purpose computer device. In specific implementations, the computer device can be a desktop computer, a portable computer, a network server, a handheld digital assistant (PDA), a mobile phone, a tablet computer, a wireless terminal device, a communication device, or an embedded device. This application does not limit the type of computer device.

[0064] In addition, this application also provides a computer-readable storage medium storing a computer program that, when executed by a processor, implements the oxygen flow control method of the pediatric respiratory nebulizer described above.

[0065] In summary, the oxygen flow control system and method for the pediatric respiratory nebulizer disclosed in this application firstly constructs a coefficient matrix of scattered light energy distribution under different shading levels based on the complex scattering effect of particles in the nebulized airflow and calibration experiments; a measurement area is set inside the outlet of the nebulizer cup of the pediatric respiratory nebulizer, a laser beam is emitted into the measurement area, and the scattered light energy distribution data of the nebulized particles and the shading level data of the measurement area are collected simultaneously; the particle size distribution of the particles in the nebulized airflow is obtained by inverting the particle size using the coefficient matrix, the scattered light energy distribution data, and the shading level data; the flow characteristic parameters of the medicine are collected in the connection channel between the medicine cup and the nebulization core component of the pediatric respiratory nebulizer, and the nebulization efficiency of the medicine is determined based on the flow characteristic parameters; when the particle size distribution deviates from the preset pediatric applicable particle size range, the oxygen flow rate of the pediatric respiratory nebulizer is adjusted within the tolerance range of the child's inhaled oxygen concentration based on the degree and nature of the deviation in particle size distribution and in conjunction with the nebulization efficiency.

[0066] Therefore, this application pre-constructs a coefficient matrix of scattered light energy distribution under different shading levels based on the complex scattering effect of particles in the atomized airflow and calibration experiments, providing a reliable foundation for the subsequent accurate inversion of particle size. A measurement area is integrated inside the nebulizer cup outlet, and a miniaturized laser emitter is used to emit laser light, simultaneously collecting scattered light energy distribution data and shading level data, enabling real-time monitoring of the atomized particle state. The particle size distribution is obtained by inverting the coefficient matrix, scattered light energy distribution data, and shading level data, allowing for accurate understanding of the atomized particle size. A miniature rheometer is integrated in the connection channel between the medicine cup and the core nebulizer component to collect drug flow characteristic parameters and determine nebulization efficiency, allowing for targeted understanding of drug nebulization performance. When the particle size distribution deviates from the pediatric applicable range, the oxygen flow rate is adjusted within the child's tolerance range based on the degree and nature of the deviation and the nebulization efficiency. Ultimately, this achieves precise control of particle size and dynamic optimization of nebulization effect during pediatric respiratory nebulization, improving the safety and effectiveness of treatment. In summary, the scheme of this application can adjust the oxygen flow rate in real time during nebulized drug administration based on the drug flow characteristics.

[0067] Although preferred embodiments of this application have been described, those skilled in the art, upon learning the basic inventive concept, can make other changes and modifications to these embodiments. Therefore, the appended claims are intended to be interpreted as including the preferred embodiments as well as all changes and modifications falling within the scope of this application.

[0068] Obviously, those skilled in the art can make various modifications and variations to this application without departing from the spirit and scope of this application. Therefore, if such modifications and variations fall within the scope of the claims of this application and their equivalents, this application also intends to include such modifications and variations.

Claims

1. A method for controlling the oxygen flow rate of a pediatric respiratory nebulizer, characterized in that, include: A coefficient matrix of scattered light energy distribution under different shading levels was constructed in advance based on the complex scattering effect of particles in the atomized airflow and in conjunction with calibration experiments. A measurement area is set inside the outlet of the nebulizer cup of the pediatric respiratory nebulizer. A laser beam is emitted into the measurement area, and the scattered light energy distribution data of the nebulized particles and the shading data of the measurement area are collected simultaneously. The particle size distribution in the atomized airflow is obtained by inverting the particle size using the coefficient matrix, the scattered light energy distribution data, and the shading data. The flow characteristics parameters of the drug are collected in the connection channel between the drug cup and the core nebulization component of the pediatric respiratory nebulizer, and the nebulization efficiency of the drug is determined based on the flow characteristics parameters. When the particle size distribution deviates from the preset pediatric applicable particle size range, the oxygen flow rate of the pediatric respiratory nebulizer is adjusted within the tolerance range of the child's inhaled oxygen concentration based on the degree and nature of the particle size distribution deviation and in conjunction with the nebulization efficiency.

2. The method as described in claim 1, characterized in that, The coefficient matrix of scattered light energy distribution under different shading levels was pre-constructed based on the complex scattering effect of particles in the atomized airflow and in conjunction with calibration experiments. Specifically, it includes: Simulation of scattered light energy distribution data under different shading levels based on the complex scattering effect of particles in atomized airflow; Calibration experiments were conducted using standard particles of known size to obtain actual scattered light energy distribution data under different shading levels. The scattered light energy distribution data and the actual scattered light energy distribution data are reconstructed into a coefficient matrix of scattered light energy distribution under different shading levels.

3. The method as described in claim 1, characterized in that, The particle size distribution in the atomized airflow is obtained by inverting the particle size using the coefficient matrix, scattered light energy distribution data, and shading data, specifically including: The scattering fluctuation domain is determined based on the shading data and the coefficient matrix; The scattered light energy distribution data is substituted into the scattering wave domain to invert the particle size in the atomized gas flow, thereby obtaining the particle size distribution in the atomized gas flow.

4. The method as described in claim 1, characterized in that, Determining the atomization efficiency of the drug based on the aforementioned flow characteristic parameters specifically includes: Based on the flow characteristic parameters and the diameter of the nozzle in the atomizing chamber of the atomizing device, a shear force model of the drug under different oxygen flow rates is established. The critical conditions for the breakup of atomized drug droplets are determined based on fluid mechanics and the aforementioned flow characteristic parameters. The atomization efficiency of the drug is determined by the critical conditions and the shear force model.

5. The method as described in claim 1, characterized in that, Adjusting the oxygen flow rate of the pediatric respiratory nebulizer within the tolerance range of the child's inhaled oxygen concentration, based on the degree and nature of the particle size distribution deviation and in conjunction with the nebulization efficiency, specifically includes: Determine the degree and nature of the deviation in particle size distribution; The oxygen adjustment amount is determined based on the degree of deviation of the particle size distribution and the atomization efficiency; The oxygen flow rate of the pediatric respiratory nebulizer is adjusted within the tolerance range of the oxygen concentration inhaled by children, based on the oxygen adjustment amount and the properties of the particle size distribution deviation.

6. The method as described in claim 1, characterized in that, The scattered light energy distribution data of the atomized particles and the shading data of the measurement area are simultaneously acquired using a Fourier lens and a charge-coupled device camera.

7. The method as described in claim 1, characterized in that, The flow characteristic parameters include the dynamic viscosity, density, flow rate, and surface tension of the drug during flow.

8. The method as described in claim 1, characterized in that, The pediatric respiratory nebulizer is an oxygen-driven nebulizer.

9. The method as described in claim 1, characterized in that, The process of emitting a laser beam toward the measurement area specifically includes: using a laser emitter in conjunction with an attenuator, a beam expander, and an aperture to form a parallel collimated beam, and then emitting the parallel collimated beam toward the measurement area.

10. An oxygen flow control system for a pediatric respiratory nebulizer, characterized in that, include: The preprocessing module is used to pre-construct the coefficient matrix of scattered light energy distribution under different shading levels based on the complex scattering effect of particles in the atomized airflow and in conjunction with calibration experiments. The acquisition module is used to set a measurement area inside the nebulizer cup outlet of the pediatric respiratory nebulizer, emit a laser beam into the measurement area, and simultaneously acquire the scattered light energy distribution data of the atomized particles and the shading data of the measurement area. The processing module is used to invert the particle size in the atomized airflow using the coefficient matrix, the scattered light energy distribution data, and the shading data, to obtain the particle size distribution in the atomized airflow. The processing module is also used to collect the flow characteristic parameters of the drug in the connection channel between the drug cup and the nebulization core component of the pediatric respiratory nebulizer, and to determine the nebulization efficiency of the drug based on the flow characteristic parameters. The execution module is used to adjust the oxygen flow rate of the pediatric respiratory nebulizer within the tolerance range of the child's inhaled oxygen concentration when the particle size distribution deviates from the preset pediatric applicable particle size range, based on the degree and nature of the deviation and in combination with the nebulization efficiency.

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