Controllable breathing machine atomization processing circuit
By integrating the main control module, detection module, and oscillation drive module into a circuit design, the size of the atomized particles can be adjusted in real time, solving the problems of low precision and poor feedback in atomization equipment, and achieving personalized atomization treatment effects.
Patent Information
- Authority / Receiving Office
- CN · China
- Patent Type
- Utility models(China)
- Current Assignee / Owner
- ANHUI PROVINCIAL HOSPITAL
- Filing Date
- 2024-12-30
- Publication Date
- 2026-06-23
Smart Images
Figure CN224387877U_ABST
Abstract
Description
Technical Field
[0001] This application relates to the field of medical nebulizers, specifically a controllable nebulization processing circuit for a ventilator. Background Technology
[0002] Currently, with the development of medicine, medical departments are increasingly discouraging outpatient intravenous infusion therapy. Nebulization drug therapy (IDT), an effective treatment for respiratory diseases, is gaining increasing recognition from clinical experts, and nebulization technology is constantly being updated and iterated. From the jet nebulizer that emerged in the 1970s, to the portable upgraded ultrasonic nebulizer, and now to the most widely used vibrating sieve nebulizer, technological advancements have gradually achieved improvements in cost control and ease of use.
[0003] Nebulized inhalers are primarily used to treat respiratory diseases. The lungs, with their vast alveolar surface area, thin alveolar cell membranes, and rich capillary network, offer the highest utilization rate for nebulized medications. In the micron-level aerodynamics of nebulization, droplets larger than 10 micrometers tend to adhere to the inner walls of the upper airways, such as the nasal cavity and oral cavity. Aerosol particles of 5-10 micrometers deposit on the inner walls of the first six bronchial segments. Only 1-5 micrometer aerosol particles ultimately reach the terminal bronchioles and alveoli. These 1-5 micrometer aerosol particles are considered effective, high-quality aerosols, characterized by their fine particle size, low flow rate, and uniform particle size, allowing them to reach deep into the lungs. Particles smaller than 1 micrometer cannot deposit effectively and are exhaled back into the atmosphere. Therefore, particles that are too large cannot reach deep into the lungs, while particles that are too small are exhaled and cannot deposit effectively. Thus, for nebulized therapy, the ideal particle diameter is 1-5 micrometers.
[0004] For mechanical ventilation, the absence of additional airflow interference effectively prevents ventilator mis-triggering. Furthermore, the uniform particle size produced by nebulization minimizes loop deposition, preventing clogging of the exhaled filter and interference with the flow sensor. No noticeable drug residue is visible after nebulization, and no heat is generated during the process, avoiding the potential impact of temperature increases on certain medications.
[0005] However, existing vibrating nebulizer devices often lack effective control over the vibration frequency of the nebulizing screen. Generally, increasing the vibration frequency accelerates the liquid atomization process, thus increasing the atomization volume. However, excessively high vibration frequencies can also make it difficult to control the size of aerosol particles to achieve appropriate standards. Higher vibration frequencies typically produce smaller aerosol particles; the higher the frequency, the stronger the segmentation effect of the screen pores on the liquid, dispersing it into finer particles, while lower frequencies may produce larger aerosol particles. Clinical studies have found that different frequencies and patterns of breathing significantly affect the absorption of drug gases by the lungs. During exhalation, a significant convection effect occurs, causing the volume of aerosol particles inhaled to increase, preventing them from effectively reaching the lungs for absorption. This can also cause coughing in patients with weak respiratory rates or those unable to breathe independently. In summary, existing nebulizer devices generally suffer from low precision and poor feedback, failing to effectively control the vibration frequency of the nebulizing screen according to the patient's respiratory rate, which greatly hinders the effectiveness of nebulization therapy.
[0006] Existing methods for detecting respiratory rate generally rely on raw ventilator waveform data to directly determine the expiratory and inspiratory phases. However, this approach is rarely applicable to nebulized therapy in clinical practice and suffers from poor accuracy. Carbon dioxide concentration detection primarily utilizes infrared spectroscopy. CO2 molecules exhibit strong absorption characteristics to specific wavelengths of infrared light. Different gas molecules absorb infrared light in specific bands, and CO2 shows a significant absorption peak around 4.26 μm. This peak can be used to determine carbon dioxide concentration, and further, indirectly, whether the breath is inhaled or exhaled (during inhalation, carbon dioxide concentration is lower than atmospheric concentration; exhaled concentration is typically around 5%). However, current technologies lack a method to effectively combine ventilator waveform data and carbon dioxide concentration detection to determine the respiratory rate range and achieve high-precision detection.
[0007] Therefore, how to effectively adjust the vibration frequency of the nebulizer screen according to the patient's respiratory rate, realize personalized diagnosis and treatment, and improve the accuracy of respiratory detection and the effectiveness of nebulization therapy is an urgent problem to be solved in the field of medical nebulization devices. Utility Model Content
[0008] In order to solve, or at least solve, the problems mentioned in the background art, this application provides a controllable ventilator nebulization processing circuit.
[0009] To achieve the above objectives, this application provides the following technical solution:
[0010] A controllable ventilator nebulization processing circuit includes: a main control module, a display module, a carbon dioxide concentration detection module, a pressure detection module, a judgment module, a nebulization output control module, and an oscillation drive module;
[0011] The main control module is used to control and process the signal input and output the processing result. The main control module is connected to the display module, the judgment module, the carbon dioxide concentration detection module, and the pressure detection module respectively. The display module, the carbon dioxide concentration detection module, and the pressure detection module are respectively connected to the judgment module. The judgment module is connected to the atomization output control module. The atomization output control module is connected to the oscillation drive module.
[0012] The display module is used to display and process the digital signals received from the main control module, and to collect respiratory curve data and process it into a ventilator respiratory rate signal. The carbon dioxide concentration detection module is used to detect the concentration of carbon dioxide exhaled by the patient and convert the concentration electrical signal into a digital signal for output. The pressure detection module is used to detect the pressure value of the patient's exhaled airflow and convert the pressure electrical signal into a digital signal for output. The judgment module is used to judge and process the collected concentration electrical signal, pressure electrical signal and ventilator respiratory rate signal output by the display module, and output the judgment result to the nebulization output control module. The nebulization output control module is used to regulate the nebulization output signal and control the power of the oscillation drive module. The oscillation drive module is used to control the size of the nebulized aerosol particles.
[0013] As a further embodiment of this application, the main control module includes a main control chip U1, and the carbon dioxide concentration detection module includes a digital-to-analog converter chip U2 and a variable resistor R3 connected at one end to the power supply module. The other end of the variable resistor R3 is connected to pin 2 of the digital-to-analog converter chip U2 and grounded. The variable resistor R3 is used to adjust its resistance value according to the change in carbon dioxide concentration.
[0014] Pin 1 of the digital-to-analog converter chip U2 is connected to pin 5 of the main control chip U1, pin 7 is connected to pin 3 of the main control chip U1, and pins 5 and 6, which are connected in parallel, are both connected to pin 4 of the main control chip U1. Pin 4 of the digital-to-analog converter chip U2 is grounded. The digital-to-analog converter chip U2 is used to output a signal to the main control chip U1 and change the strength of the converter output signal according to the resistance change of the variable resistor R3.
[0015] As a further embodiment of this application, the pressure detection module includes a digital-to-analog converter chip U4, a pressure sensor U5, a capacitor C4, and a resistor R2. Pin 3 of the pressure sensor U5 is connected to the power supply module, pin 1 of the pressure sensor U5 is connected to pin 2 of the digital-to-analog converter chip U4, and is also connected to one end of the capacitor C4 and one end of the resistor R2. Pin 2 of the pressure sensor U5 is grounded and connected to the other end of the capacitor C4 and the other end of the resistor R2, forming a low-pass filter circuit to effectively transmit the pressure sensing signal to the digital-to-analog converter chip U4.
[0016] Pin 1 of the digital-to-analog converter chip U4 is connected to pin 21 of the main control chip U1, pin 7 is connected to pin 16 of the main control chip U1, and pins 5 and 6, which are connected in parallel, are both connected to pin 17 of the main control chip U1. Pin 4 of the digital-to-analog converter chip U4 is grounded, and pin 8 of the digital-to-analog converter chip U4 is connected to the power supply module. The digital-to-analog converter chip U4 is used to convert the electrical signal changes of the pressure sensor U5 into digital signals and output them to the main control chip U1.
[0017] As a further embodiment of this application, the main control module also includes a reset circuit, wherein the reset circuit includes a capacitor C3 and a resistor R1. One end of the capacitor C3 is connected to the power supply module, and the other end is connected to one end of the resistor R1 and pin 9 of the main control chip U1. The other end of the resistor R2 is grounded, together forming a reset circuit, which is used to initialize the main control chip U1 when the system is powered on to ensure that it starts running.
[0018] As a further embodiment of this application, the main control module further includes a crystal oscillator circuit, which includes capacitors C1 and C2 and a crystal oscillator Y1. Pin 1 of the crystal oscillator Y1 is connected to one end of capacitor C2 and pin 18 of the main control chip U1. Pin 2 of the crystal oscillator Y1 is connected to one end of capacitor C1 and pin 19 of the main control chip U1. The other ends of capacitors C1 and C2 are connected to each other and grounded to generate a stable clock signal and provide a timing reference for the main processing chip U1.
[0019] As a further embodiment of this application, the display module includes a display processing chip U3 and a variable resistor R3. Pin 3 of the display processing chip U3 is connected to one end of the variable resistor R3 and grounded. The other end of the variable resistor R3 is connected to a power supply module, which is used to obtain tidal volume and respiratory ratio data according to the change of its resistance value, and to regulate the change of the respiratory curve of the display processing chip U3.
[0020] Pins 1 and 5 of the display processing chip U3 are grounded, and pin 2 is connected to the power supply module. Pin 4 of the display processing chip U3 is connected to pin 24 of the main control chip U1, pin 6 is connected to pin 25 of the main control chip U1, pin 7 is connected to pin 39 of the main control chip U1, pin 8 is connected to pin 38 of the main control chip U1, pin 9 is connected to pin 37 of the main control chip U1, pin 10 is connected to pin 36 of the main control chip U1, pin 11 is connected to pin 35 of the main control chip U1, pin 12 is connected to pin 34 of the main control chip U1, pin 13 is connected to pin 33 of the main control chip U1, and pin 14 is connected to pin 32 of the main control chip U1. The display processing chip U3 is used to display the changes in the patient's respiratory curve and convert them into digital signals for output to the main control chip U1, while also receiving feedback signals from the main control module.
[0021] As a further embodiment of this application, pin 51 of the judgment module is connected to the carbon dioxide concentration detection module to receive carbon dioxide concentration change signals; pin 53 of the judgment module is connected to the pressure detection module to receive pressure change signals; and pin 52 of the judgment module is connected to the display module to receive ventilator breathing curve change signals.
[0022] Pin 49 of the judgment module is grounded, and pin 50 of the judgment module is connected to the atomization output control module. It is used to output the digital signal after receiving and judging each detection signal to the atomization output control module, and release a high-level electrical signal when judging inhalation and a low-level electrical signal when judging exhalation.
[0023] As a further embodiment of this application, the atomization output control module includes an atomization control chip U6, a resistor R7, a light-emitting diode D1, a switch S1, and variable resistors R7 and R8 connected in parallel. Pin 1 of the atomization control chip U6 is connected to the power supply module, pin 8 of the atomization control chip U6 is grounded, pin 2 of the atomization control chip U6 is connected to one end of the resistor R5, the other end of the resistor R5 is connected to the positive terminal of the light-emitting diode D1, and the negative terminal of the light-emitting diode D1 is grounded. Pin 4 of the atomization control chip U6 is simultaneously connected to one end of the switch S1 and the +5V power supply, and the other end of the switch S1 is grounded. The atomization control chip U6 is simultaneously connected to one end of the variable resistor R6, one end of the variable resistor R7, and the oscillation drive module. The other ends of the variable resistors R6 and R7 are interconnected and grounded. The variable resistors R6 and R7 are used to control the atomization output based on the change in their resistance values.
[0024] As a further embodiment of this application, the oscillation drive module includes an atomizing plate P1, an inductor L1, a capacitor C5, resistors R8, R9, R10, R11, and R12. One end of resistor R12 is connected to pin 6 of the atomization control chip U6. Resistor R12 and resistor R8 are connected in series. The end of resistor R8 away from resistor R12 is connected to pin 2 of the atomizing plate P1 and one end of the inductor L1. The other end of inductor L1 is connected to pin 1 of the atomizing plate P1 and one end of capacitor C5. The other end of capacitor C5 is grounded. Inductor L1 is also connected to a field-effect transistor to amplify the waveform voltage. The field-effect transistor is also connected to resistors R9, R10, and R11. The ends of resistors R9 and R10 away from the field-effect transistor are grounded. The other end of resistor R11 is connected to pin 7 of the atomization control chip U6.
[0025] As a further embodiment of this application, the main control chip U1 is an 89C52 microcontroller, the digital-to-analog converter chip U2 of the carbon dioxide concentration detection module and the digital-to-analog converter chip of the pressure detection module are ADC0832 digital-to-analog converters, and the display processing chip U3 is an LCD1602 liquid crystal display module.
[0026] Compared with the prior art, this application has the following advantages:
[0027] This application utilizes a cleverly designed circuit to effectively detect a patient's respiratory rate. Through the coordinated operation of a main control module, a carbon dioxide detection module, and a pressure detection module, this application accurately collects the patient's respiratory rate data. The data is fed back to the display module in real time based on the patient's specific respiratory rate, and the collected respiratory rate data is processed in the main control module to apply a more personalized treatment plan. Furthermore, by incorporating a judgment module to administer medication based on both inhalation and exhalation modes, the device can adjust the current path and parameters according to real-time respiratory feedback data, optimizing the treatment effect and improving the accuracy of nebulization therapy.
[0028] This application further processes the electrical signals of different judgment modes through the nebulizer output control module connected to the judgment module, accurately generates control digital signals, and inputs them into the oscillation drive module connected to the nebulizer output control module. This application then utilizes the oscillation drive module acting on the nebulizer to achieve effective control of the aerosol particle volume during nebulization therapy. It can directly adjust the vibration frequency of the nebulizer screen to better adapt to the patient's breathing rate, maximizing the absorption of the drug mist by the patient and avoiding drug waste or coughing reactions caused by poor absorption during exhalation. Combined with the reset circuit and crystal oscillator circuit design of the main control module of this application, the stability and safety performance of the equipment are improved. Attached Figure Description
[0029] Figure 1 This is a schematic diagram of a controllable ventilator nebulization device provided in Embodiment 1 of this application.
[0030] Figure 2 This is a partial cross-sectional view of the nebulizer of a controllable ventilator nebulization device provided in Embodiment 1 of this application.
[0031] Figure 3 The circuit diagram shows the main control module, carbon dioxide concentration detection module, and display module of a controllable ventilator nebulization device provided in Embodiment 2 of this application.
[0032] Figure 4 The circuit diagram shows the nebulization output module and oscillation drive module of a controllable ventilator nebulization processing device provided in Embodiment 2 of this application.
[0033] Figure 5 This is a schematic diagram of the judgment module of a controllable ventilator nebulization processing device provided in Embodiment 2 of this application.
[0034] Figure 6 This is a circuit diagram of the pressure detection module mounted on a controllable ventilator nebulization device provided in Embodiment 2 of this application.
[0035] Figure 7 This is a schematic diagram of the crystal oscillator circuit of a controllable ventilator nebulization device provided in Embodiment 2 of this application.
[0036] Figure 8 This is a front view of the nebulizer screen of a controllable ventilator nebulization device provided in Embodiment 1 of this application.
[0037] Figure 9 This is a schematic diagram of the applicable structure of a controllable ventilator nebulization device provided in Embodiment 1 of this application.
[0038] In the diagram: 10. Controller;
[0039] 101. Main control module; 102. Judgment module; 103. Ventilator control line; 104. Nebulizer control line; 105. Airway pressure detection data line; 106. Carbon dioxide detection data line;
[0040] 20. Ventilator;
[0041] 201. Display module; 202. Ventilation device; 203. Power supply module;
[0042] 30. Atomizing pipeline;
[0043] 301. Inlet pipe; 302. Humidifier; 303. Y-connector; 304. Outlet pipe;
[0044] 3011, First air intake pipe; 3012, Second air intake pipe; 3013, Atomizer interface;
[0045] 40. Atomizer;
[0046] 401. Drug delivery port; 402. Nebulization output control module; 403. Nebulization screen; 404. Oscillation drive module;
[0047] 50. Detection components;
[0048] 501. Carbon dioxide concentration detection device; 502. Pressure detection device;
[0049] 5011, Carbon dioxide concentration detection module; 5021, Pressure detection module; 5022, Pressure detector. Detailed Implementation
[0050] The technical solution of this patent will be further described in detail below with reference to specific implementation methods.
[0051] To make the objectives, technical solutions, and advantages of this application clearer, the following detailed description is provided in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and not intended to limit the scope of this application.
[0052] In the description of this application, it should be noted that the terms "center," "upper," "lower," "left," "right," "vertical," "horizontal," "inner," and "outer," etc., indicating orientation or positional relationships based on the orientation or positional relationships shown in the accompanying drawings, are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation on this application; the terms "first," "second," and "third" are used for descriptive purposes only and should not be construed as indicating or implying relative importance; furthermore, unless otherwise expressly specified and limited, the terms "installed," "connected," and "linked" should be interpreted broadly, for example, they can be fixed connections, detachable connections, or integral connections; they can be mechanical connections or electrical connections; they can be direct connections or indirect connections through an intermediate medium; they can be internal connections between two elements. Those skilled in the art can understand the specific meaning of the above terms in this application based on the specific circumstances.
[0053] The inventors of this application have discovered that existing medical nebulizer devices generally suffer from low precision and poor feedback. Specifically, different breathing frequencies and patterns significantly affect the absorption of drug gases by the patient's lungs. During exhalation, a noticeable convection effect occurs, causing the volume of inhaled aerosol particles to increase, preventing them from effectively reaching the lungs for absorption. This can also cause coughing in patients with weak respiratory rates or those unable to breathe independently. Existing nebulizer devices cannot accurately detect the patient's respiratory rate, nor can they provide nebulizer treatment tailored to the patient's breathing state based on their respiratory rate; in other words, they lack effective control over nebulization processing.
[0054] In view of this, this application provides a controllable ventilator nebulization processing device, characterized in that it includes: a controller 10, the controller 10 including a judgment module 102;
[0055] Ventilator 20, which is connected to controller 10;
[0056] Nebulizing tubing 30 is connected to ventilator 20;
[0057] The nebulizer 40 is connected to the controller 10 and is connected to the nebulization tubing 40. The nebulizer 40 includes a drug delivery port 401, a nebulization output control module 402, a nebulization screen 403, and an oscillation drive module 404 that is connected to the nebulization output control module 402 and the nebulization screen 403 respectively. The nebulization output control module 402 and the oscillation drive module 404 are respectively connected to the judgment module 102.
[0058] The detection component 50 is connected to the controller 10.
[0059] To effectively detect and process a patient's respiratory rate, in Embodiment 1 of this application, the controller 10 further includes a main control module 101. The detection component 50 is connected to the nebulization tubing 30 and is connected to the controller 10. The detection component 50 includes a carbon dioxide concentration detection device 501 and a pressure detection device 502. The carbon dioxide concentration detection device 501 includes a carbon dioxide concentration detection module 5011, and the pressure detection device 502 includes a pressure detection module 5021. The carbon dioxide concentration detection module 5011 and the pressure detection module 5021 are respectively connected to the main control module 101 and the judgment module 102. The results output by the carbon dioxide concentration detection module 5011 and the pressure detection module 5021 can be analyzed, judged, processed, and a respiratory rate curve fitting can be output to achieve accurate detection.
[0060] In order to obtain the original respiratory curve data and realize the effective feedback of the processed respiratory rate curve, in the first embodiment of this application, the ventilator 20 is connected to the controller 10. The ventilator 20 includes a display module 201, a ventilation device 202 and a power supply module 203. The display module 201 is connected to the main control module 101, the judgment module 102 and the power supply module 203 respectively. The main control module 101 and the judgment module 102 are connected to the power supply module 203, which can realize the airflow into the nebulization tube 20 and the energy input of each component.
[0061] To achieve the basic airflow effect of nebulization therapy, in Embodiment 1 of this application, the nebulization pipeline 30 includes an air inlet pipe 301, a humidification tank 302, a Y-type connector 303, and an air outlet pipe 304. The humidification tank 302 is connected to the air inlet pipe 301, and the air inlet pipe 301 and the air outlet pipe 302 are respectively connected to the Y-type connector 303, which enables the nebulization therapy process to complete the gas circulation and humidification steps.
[0062] In order to connect the nebulizing tubing 30 to the ventilator 20 and the nebulizer 40, in the first embodiment of this application, the air inlet pipe 301 includes a first air inlet pipe 3011, a second air inlet pipe 3012 and a nebulizer interface 3013. One end of the first air inlet pipe 3011 is connected to the ventilation device 202 and the other end is connected to the humidification tank 302. One end of the second air inlet pipe 3012 is connected to the humidification tank 302 and the other end is connected to the Y-connector 303. The nebulizer interface 3013 is connected to the side of the second air inlet pipe 3012 and is used to connect the nebulizer 40.
[0063] In order to connect the nebulizing tubing 30 to the detection component 50 and the external breathing aid, in Embodiment 1 of this application, one end of the outlet pipe 304 is connected to the Y-connector 303 and the other end is connected to the ventilation device 202. The detection component 50 is connected to the side of the Y-connector 303 that is not connected to the inlet pipe 301 and the outlet pipe 302. The Y-connector 303 is used to connect to the external breathing aid, which can be an oxygen mask or a nasal cannula, etc.
[0064] To achieve circuit connections between modules, in Embodiment 1 of this application, the controller 10 includes a ventilator control line 103, a nebulizer control line 104, an airway pressure detection data line 105, and a carbon dioxide detection data line 106. The ventilator control line 103 is used to connect the controller 10 to the ventilator 20, the nebulizer control line 104 is used to connect the controller 10 to the nebulizer 40, the airway pressure detection data line 105 is used to connect the controller 10 to the pressure detection device 502, and the carbon dioxide detection data line 106 is used to connect the controller 10 to the carbon dioxide concentration detection device 501.
[0065] In the first embodiment of this application, one end of the nebulizer 40 is connected to the nebulizer interface 3013, and the other end is connected to the drug delivery port 401. The nebulizer 40 is provided with an atomizing screen 403 inside. The side of the nebulizer 40 is connected to the nebulizer control line 104, which enables the drug entering through the drug delivery port 401 to be decomposed into aerosol particles of appropriate size (1-5 micrometers).
[0066] In order to detect the airway pressure value of the patient, in the first embodiment of this application, the pressure detection device 502 further includes a pressure sensor 5022, which is used to convert the pressure sensing signal into an electrical signal and input it to the pressure detection module 5021.
[0067] To enable the function of adjusting the nebulization effect according to the patient's respiratory rate, in Embodiment 1 of this application, the display module 201 is used to display and process the digital signal received from the main control module 101 and collect respiratory curve data and process it into a ventilator respiratory rate signal. The carbon dioxide concentration detection module 5011 is used to detect the concentration of carbon dioxide exhaled by the patient and convert the concentration electrical signal into a digital signal for output. The pressure detection module 5021 is used to detect the pressure value of the patient's exhaled airflow and convert the pressure electrical signal into a digital signal for output. The judgment module 102 is used to judge and process the collected concentration electrical signal, pressure electrical signal and ventilator respiratory rate signal output by the display module 201 and output the judgment result to the nebulization output control module 402. The nebulization output control module 402 is used to regulate the nebulization output signal and control the power of the oscillation drive module 404. The oscillation drive module 404 is used to control the size of the nebulized aerosol particles.
[0068] The working principle of this utility model is as follows: First, the controller 10 receives signals from the ventilator 20 and the detection component 50 through the judgment module 102, and judges the current operating status of the ventilator 20 and the nebulization processing requirements. Specifically, it acquires the detection results of the ventilator 20, the carbon dioxide concentration detection device 501, and the pressure detection device 502, processes them, and outputs the results to the nebulizer 40. Then, the controller acquires the original waveform data of the ventilator 20 through the display module 201 built into the ventilator 20, and uses the carbon dioxide concentration detection module 5011 built into the carbon dioxide detection device 501 and the pressure detection module 5022 mounted on the pressure detection device 502 to acquire carbon dioxide concentration detection data and airway pressure detection data, respectively. The above signals are input into the main control module 101 for analysis and processing. The main control module 101 then issues control commands according to the preset program to adjust the display status of the ventilator 20. Subsequently, the nebulization input control module 402 of the nebulizer 40 processes the output result of the judgment module 102, i.e., the judgment signal. The oscillation drive module 404 operates after receiving the output result of the nebulization input control module 402. Specifically, the nebulization input control module 402 outputs a nebulization stop signal during the low-level time region of the judgment signal (exhalation judgment) and outputs a nebulization start signal during the high-level time region of the judgment signal (inhalation judgment). Simultaneously, the oscillation drive module 404 directly acts on the nebulization screen 403. When the nebulization stop signal is received, the oscillation stops, and the nebulizer no longer outputs medication mist during this time region. When the nebulization start signal is received, the oscillation begins, and the nebulization screen 403 atomizes the medication placed through the drug delivery port 401 into tiny particles, which are then delivered to the patient through the nebulization tubing 30, thus achieving closed-loop control of the entire system. The device provided by this utility model is reasonably and ingeniously designed, enabling precise detection of the patient's respiratory rate and precise control of nebulization therapy based on the detected respiratory rate data, maximizing drug utilization efficiency and improving the nebulization therapy effect.
[0069] Example 2
[0070] The inventors of this application have discovered that existing medical nebulizer devices generally suffer from low precision and poor feedback. Specifically, different breathing frequencies and patterns significantly affect the absorption of drug gases by the patient's lungs. During exhalation, a noticeable convection effect occurs, causing the volume of inhaled aerosol particles to increase, preventing them from effectively reaching the lungs for absorption. This can also cause coughing in patients with weak respiratory rates or those unable to breathe independently. Existing nebulizer devices cannot accurately detect the patient's respiratory rate, nor can they provide nebulizer treatment tailored to the patient's breathing state based on their respiratory rate; in other words, they lack effective control over nebulization processing.
[0071] In view of this, this application also provides a controllable ventilator nebulization processing circuit, which is applied to a controllable ventilator nebulization processing device; the controllable ventilator nebulization processing circuit includes: a main control module 101, a display module 201, a carbon dioxide concentration detection module 5011, a pressure detection module 5021, a judgment module 102, a nebulization output control module 402, and an oscillation drive module 404.
[0072] The main control module 101 is used to control and process the signal input and output the processing result. The main control module 101 is connected to the display module 201, the judgment module 102, the carbon dioxide concentration detection module 5011, and the pressure detection module 5021 respectively. The display module 201, the carbon dioxide concentration detection module 5011, and the pressure detection module 5021 are connected to the judgment module 102 respectively. The judgment module 102 is connected to the atomization output control module 402. The atomization output control module 402 is connected to the oscillation drive module 404.
[0073] The display module 201 is used to display and process the digital signals received from the main control module 101, and to collect respiratory curve data and process it into a respiratory rate signal for the ventilator 20. The carbon dioxide concentration detection module 5011 is used to detect the concentration of carbon dioxide exhaled by the patient and convert the concentration electrical signal into a digital signal for output. The pressure detection module 5021 is used to detect the pressure value of the patient's exhaled airflow and convert the pressure electrical signal into a digital signal for output. The judgment module 102 is used to judge and process the collected concentration electrical signal, pressure electrical signal and the respiratory rate signal of the ventilator 20 output by the display module 201, and output the judgment result to the nebulization output control module 402. The nebulization output control module 402 is used to regulate the nebulization output signal and control the power of the oscillation drive module 404. The oscillation drive module 404 is used to control the size of the nebulized aerosol particles.
[0074] It is understood that the pressure detection module 5021 is built into the pressure detection device 502, the carbon dioxide concentration detection module 5011 is built into the carbon dioxide concentration detection device 501, the nebulization output control module 402 and the oscillation drive module 404 are built into the nebulizer 40, and the display module 201 is built into the ventilator 20.
[0075] like Figure 3 As shown, Figure 3This is a circuit diagram of a controllable ventilator nebulization processing circuit, comprising a main control module 101, a carbon dioxide concentration detection module 5011, and a display module 201, according to Embodiment 2 of this application. To output a carbon dioxide concentration detection digital signal to the main control module 101 and the judgment module 102, in Embodiment 2 of this application, the main control module 101 includes a main control chip U1, and the carbon dioxide concentration detection module 5011 includes a digital-to-analog converter chip U2 and a variable resistor R3 connected at one end to the power supply module 203. The other end of the variable resistor R3 is connected to pin 2 of the digital-to-analog converter chip U2 and grounded. The variable resistor R3 is used to adjust its resistance value according to changes in carbon dioxide concentration.
[0076] Pin 1 of the digital-to-analog converter chip U2 is connected to pin 5 of the main control chip U1, pin 7 is connected to pin 3 of the main control chip U1, and pins 5 and 6, which are connected in parallel, are both connected to pin 4 of the main control chip U1. Pin 4 of the digital-to-analog converter chip U2 is grounded. The digital-to-analog converter chip U2 is used to output a signal to the main control chip U1 and change the strength of the converter output signal according to the resistance change of the variable resistor R3.
[0077] refer to Figure 6 As shown, Figure 6 This is a circuit diagram of a pressure detection module in a controllable ventilator nebulization processing circuit according to Embodiment 2 of this application. To output a digital signal of airway pressure detection to the main control module 101 and the judgment module 102, in Embodiment 2 of this application, the pressure detection module 5021 includes a digital-to-analog converter chip U4, a pressure sensor 5022, a capacitor C4, and a resistor R2. Pin 3 of the pressure sensor 5022 is connected to the power supply module 203. Pin 1 of the pressure sensor 5022 is connected to pin 2 of the digital-to-analog converter chip U4 and simultaneously connected to one end of the capacitor C4 and one end of the resistor R2. Pin 2 of the pressure sensor 5022 is grounded and connected to the other end of the capacitor C4 and the other end of the resistor R2, forming a low-pass filter circuit to effectively transmit the pressure sensing signal to the digital-to-analog converter chip U4.
[0078] Pin 1 of the digital-to-analog converter chip U4 is connected to pin 21 of the main control chip U1, pin 7 is connected to pin 16 of the main control chip U1, and pins 5 and 6, which are connected in parallel, are both connected to pin 17 of the main control chip U1. Pin 4 of the digital-to-analog converter chip U4 is grounded, and pin 8 of the digital-to-analog converter chip U4 is connected to the power supply module 203. The digital-to-analog converter chip U4 is used to convert the electrical signal changes of the pressure sensor U5 into digital signals and output them to the main control chip U1.
[0079] To initialize the main control chip U1 when the system is powered on and ensure that it starts running, in Embodiment 2 of this application, the main control module 101 further includes a reset circuit, which includes a capacitor C3 and a resistor R1. One end of the capacitor C3 is connected to the power supply module 203, and the other end is connected to one end of the resistor R1 and pin 9 of the main control chip U1. The other end of the resistor R2 is grounded, together forming a reset circuit.
[0080] like Figure 7 As shown, Figure 7 This is a circuit diagram of a crystal oscillator circuit for a controllable ventilator nebulization processing circuit provided in an embodiment of this application. To generate a stable clock signal and provide a timing reference for the main processing chip U1, in Embodiment 2 of this application, the main control module 101 further includes a crystal oscillator circuit. The crystal oscillator circuit includes capacitors C1 and C2, and a crystal oscillator Y1. Pin 1 of the crystal oscillator Y1 is simultaneously connected to one end of capacitor C2 and pin 18 of the main control chip U1. Pin 2 of the crystal oscillator Y1 is simultaneously connected to one end of capacitor C1 and pin 19 of the main control chip U1. The other ends of capacitors C1 and C2 are interconnected and grounded.
[0081] refer to Figure 3 In order to provide intuitive real-time feedback on the input digital signal, in Embodiment 2 of this application, the display module 201 includes a display processing chip U3 and a variable resistor R3. Pin 3 of the display processing chip U3 is connected to one end of the variable resistor R3 and grounded. The other end of the variable resistor R3 is connected to the power supply module 203, which is used to obtain data such as tidal volume and respiratory ratio according to the change of its resistance value, and to regulate the change of the respiratory curve of the display processing chip U3.
[0082] Pins 1 and 5 of the display processing chip U3 are grounded, and pin 2 is connected to the power supply module 203. Pin 4 of the display processing chip U3 is connected to pin 24 of the main control chip U1, pin 6 is connected to pin 25 of the main control chip U1, pin 7 is connected to pin 39 of the main control chip U1, pin 8 is connected to pin 38 of the main control chip U1, pin 9 is connected to pin 37 of the main control chip U1, pin 10 is connected to pin 36 of the main control chip U1, pin 11 is connected to pin 35 of the main control chip U1, pin 12 is connected to pin 34 of the main control chip U1, pin 13 is connected to pin 33 of the main control chip U1, and pin 14 is connected to pin 32 of the main control chip U1. The display processing chip U3 is used to display the changes in the patient's respiratory curve and convert them into digital signals for output to the main control chip U1, while also receiving feedback signals from the main control module 101.
[0083] refer to Figure 5 As shown, Figure 5This is a schematic diagram of a judgment module in a controllable ventilator nebulization processing circuit according to Embodiment 2 of this application. To effectively determine the respiratory rate, identify the nebulization mode, and provide feedback to the nebulizer 20, in Embodiment 2 of this application, pin 51 of the judgment module 102 is connected to the carbon dioxide concentration detection module 5011 to receive carbon dioxide concentration change signals; pin 53 of the judgment module 102 is connected to the pressure detection module 5021 to receive pressure change signals; and pin 52 of the judgment module 102 is connected to the display module 201 to receive respiratory curve change signals from the ventilator 20.
[0084] Pin 49 of the judgment module 102 is grounded, and pin 50 of the judgment module 102 is connected to the atomization output control module 402. The digital signal after receiving and judging each detection signal is output to the atomization output control module 402. When judging inhalation, a high-level electrical signal is released, and when judging exhalation, a low-level electrical signal is released.
[0085] refer to Figure 4 , Figure 4 The circuit diagram shows the nebulization output module 402 and the oscillation drive module 404 of a controllable ventilator nebulization processing circuit provided in Embodiment 2 of this application. To process the received judgment signal and control the atomization operation process, in Embodiment 2 of this application, the atomization output control module 402 includes an atomization control chip U6, a resistor R7, a light-emitting diode D1, a switch S1, and variable resistors R7 and R8 connected in parallel. Pin 1 of the atomization control chip U6 is connected to the power supply module 203, pin 8 of the atomization control chip U6 is grounded, pin 2 of the atomization control chip U6 is connected to one end of the resistor R5, the other end of the resistor R5 is connected to the positive terminal of the light-emitting diode D1, and the negative terminal of the light-emitting diode D1 is grounded. Pin 4 of the atomization control chip U6 is simultaneously connected to one end of the switch S1 and the +5V power supply, the other end of the switch S1 is grounded, and the atomization control chip U6 is simultaneously connected to one end of the variable resistor R6, one end of the variable resistor R7, and the oscillation drive module 404. The other ends of the variable resistors R6 and R7 are interconnected and grounded. The variable resistors R6 and R7 are used to control the atomization output based on the change in their resistance values.
[0086] like Figure 4As shown, to directly act on the atomizing screen 403 and drive the input control signal to atomize vibration, in Embodiment 2 of this application, the oscillation drive module 404 includes an atomizing plate P1, an inductor L1, a capacitor C5, resistors R8, R9, R10, R11, and R12. One end of resistor R12 is connected to pin 6 of the atomizing control chip U6, and resistors R12 and R8 are connected in series. The end of resistor R8 away from resistor R12 is connected to pin 2 of the atomizing plate P1 and one end of the inductor L1. The other end of inductor L1 is connected to pin 1 of the atomizing plate P1 and one end of capacitor C5. The other end of capacitor C5 is grounded. Inductor L1 is also connected to a field-effect transistor to amplify the waveform voltage. The field-effect transistor is also connected to resistors R9, R10, and R11. The ends of resistors R9 and R10 away from the field-effect transistor are grounded. The other end of resistor R11 is connected to pin 7 of the atomizing control chip U6.
[0087] To provide a preferred chip selection scheme, in Embodiment 2 of this application, the main control chip U1 is an 89C52 microcontroller, the analog-to-digital converter U2 of the carbon dioxide concentration detection module 5011 and the analog-to-digital converter U2 of the pressure detection module 5021 are ADC0832 digital-to-analog converters, and the display processing chip U3 is an LCD1602 liquid crystal display chip.
[0088] The working principle of this utility model is as follows: First, the original waveform data of the ventilator is acquired through the display module 201 built into the ventilator 20. Then, the carbon dioxide concentration detection module 5011 built into the carbon dioxide detection device 501 and the pressure detection module 5021 mounted on the pressure detector 502 are used to acquire carbon dioxide concentration detection data and airway pressure detection data, respectively. The above signals are input into the main control module 101 for analysis and processing. After the analysis, the actual respiratory rate curve signal of the patient is obtained. At the same time, the above signals are also entered into the judgment module 102 for judgment and processing and converted into electrical signals. The actual respiratory rate curve signal of the patient is output by the main control module 101 to the display module 201 for real-time external feedback. The processed electrical signal is transmitted to the nebulizer output control module 402 within the nebulizer 40 for control processing. Specifically, a nebulization stop signal is output during the low-level time period of the judgment signal (exhalation judgment), and a nebulization start signal is output during the high-level time period of the judgment signal (inhalation judgment). Simultaneously, this signal is received by the oscillation drive circuit 404, also located in the nebulizer 40, and directly acts on the nebulizer screen 403. When the nebulization stop signal is received, the oscillation stops, and the nebulizer 40 no longer outputs medication mist during this time period. When the nebulization start signal is received, the oscillation begins, and the nebulizer screen 403 oscillates during this time period, allowing aerosol particles to enter the patient's respiratory system. The circuit design provided by this utility model is reasonable and ingenious, enabling accurate detection of the patient's respiratory rate and precise control of nebulization therapy based on the detected respiratory rate data, maximizing drug utilization efficiency and improving the nebulization therapy effect.
[0089] The preferred embodiments of this patent have been described in detail above. However, this patent is not limited to the above embodiments. Within the scope of knowledge possessed by those skilled in the art, various changes can be made without departing from the spirit of this patent.
Claims
1. A controllable nebulization processing circuit for a ventilator, characterized in that, include: The system includes a main control module, a display module, a carbon dioxide concentration detection module, a pressure detection module, a judgment module, an atomization output control module, and an oscillation drive module. The main control module is used to control and process the signal input and output the processing result. The main control module is connected to the display module, the judgment module, the carbon dioxide concentration detection module, and the pressure detection module respectively. The display module, the carbon dioxide concentration detection module, and the pressure detection module are respectively connected to the judgment module. The judgment module is connected to the atomization output control module. The atomization output control module is connected to the oscillation drive module. The display module is used to display and process the digital signals received from the main control module, and to collect respiratory curve data and process it into a ventilator respiratory rate signal. The carbon dioxide concentration detection module is used to detect the concentration of carbon dioxide exhaled by the patient and convert the concentration electrical signal into a digital signal for output. The pressure detection module is used to detect the pressure value of the patient's exhaled airflow and convert the pressure electrical signal into a digital signal for output. The judgment module is used to judge and process the collected concentration electrical signal, pressure electrical signal and ventilator respiratory rate signal output by the display module, and output the judgment result to the nebulization output control module. The nebulization output control module is used to regulate the nebulization output signal and control the power of the oscillation drive module. The oscillation drive module is used to control the size of the nebulized aerosol particles.
2. The controllable nebulization processing circuit for a ventilator according to claim 1, characterized in that, The main control module includes a main control chip U1, and the carbon dioxide concentration detection module includes a digital-to-analog converter chip U2 and a variable resistor R3 connected at one end to the power supply module. The other end of the variable resistor R3 is connected to pin 2 of the digital-to-analog converter chip U2 and grounded. The variable resistor R3 is used to adjust its resistance value according to the change of carbon dioxide concentration. Pin 1 of the digital-to-analog converter chip U2 is connected to pin 5 of the main control chip U1, pin 7 is connected to pin 3 of the main control chip U1, and pins 5 and 6, which are connected in parallel, are both connected to pin 4 of the main control chip U1. Pin 4 of the digital-to-analog converter chip U2 is grounded. The digital-to-analog converter chip U2 is used to output a signal to the main control chip U1 and change the strength of the converter output signal according to the resistance change of the variable resistor R3.
3. The controllable nebulization processing circuit for a ventilator according to claim 1, characterized in that, The pressure detection module includes a digital-to-analog converter chip U4, a pressure sensor U5, a capacitor C4, and a resistor R2. Pin 3 of the pressure sensor U5 is connected to the power supply module. Pin 1 of the pressure sensor U5 is connected to pin 2 of the digital-to-analog converter chip U4 and is also connected to one end of the capacitor C4 and one end of the resistor R2. Pin 2 of the pressure sensor U5 is grounded and connected to the other end of the capacitor C4 and the other end of the resistor R2, forming a low-pass filter circuit to effectively transmit the pressure sensing signal to the digital-to-analog converter chip U4. Pin 1 of the digital-to-analog converter chip U4 is connected to pin 21 of the main control chip U1, pin 7 is connected to pin 16 of the main control chip U1, and pins 5 and 6, which are connected in parallel, are both connected to pin 17 of the main control chip U1. Pin 4 of the digital-to-analog converter chip U4 is grounded, and pin 8 of the digital-to-analog converter chip U4 is connected to the power supply module. The digital-to-analog converter chip U4 is used to convert the electrical signal changes of the pressure sensor U5 into digital signals and output them to the main control chip U1.
4. The controllable nebulization processing circuit for a ventilator according to claim 1, characterized in that, The main control module also includes a reset circuit, which includes a capacitor C3 and a resistor R1. One end of the capacitor C3 is connected to the power supply module, and the other end is connected to one end of the resistor R1 and pin 9 of the main control chip U1. The other end of the resistor R2 is grounded, together forming a reset circuit, which is used to initialize the main control chip U1 when the system is powered on to ensure that it starts running.
5. The controllable nebulization processing circuit for a ventilator according to claim 1, characterized in that, The main control module also includes a crystal oscillator circuit, which includes capacitors C1 and C2 and a crystal oscillator Y1. Pin 1 of the crystal oscillator Y1 is connected to one end of capacitor C2 and pin 18 of the main control chip U1. Pin 2 of the crystal oscillator Y1 is connected to one end of capacitor C1 and pin 19 of the main control chip U1. The other ends of capacitors C1 and C2 are connected to each other and grounded to generate a stable clock signal and provide a timing reference for the main processing chip U1.
6. The controllable nebulization processing circuit for a ventilator according to claim 1, characterized in that, The display module includes a display processing chip U3 and a variable resistor R3. Pin 3 of the display processing chip U3 is connected to one end of the variable resistor R3 and grounded. The other end of the variable resistor R3 is connected to the power supply module, which is used to obtain tidal volume and respiratory ratio data according to the change of its resistance value, and to regulate the change of the respiratory curve of the display processing chip U3. Pins 1 and 5 of the display processing chip U3 are grounded, and pin 2 is connected to the power supply module. Pin 4 of the display processing chip U3 is connected to pin 24 of the main control chip U1, pin 6 is connected to pin 25 of the main control chip U1, pin 7 is connected to pin 39 of the main control chip U1, pin 8 is connected to pin 38 of the main control chip U1, pin 9 is connected to pin 37 of the main control chip U1, pin 10 is connected to pin 36 of the main control chip U1, pin 11 is connected to pin 35 of the main control chip U1, pin 12 is connected to pin 34 of the main control chip U1, pin 13 is connected to pin 33 of the main control chip U1, and pin 14 is connected to pin 32 of the main control chip U1. The display processing chip U3 is used to display the changes in the patient's respiratory curve and convert them into digital signals for output to the main control chip U1, while also receiving feedback signals from the main control module.
7. The controllable nebulization processing circuit for a ventilator according to claim 1, characterized in that, Pin 51 of the judgment module is connected to the carbon dioxide concentration detection module to receive carbon dioxide concentration change signals; pin 53 of the judgment module is connected to the pressure detection module to receive pressure change signals; pin 52 of the judgment module is connected to the display module to receive ventilator breathing curve change signals. Pin 49 of the judgment module is grounded, and pin 50 of the judgment module is connected to the atomization output control module. It is used to output the digital signal after receiving and judging each detection signal to the atomization output control module, and release a high-level electrical signal when judging inhalation and a low-level electrical signal when judging exhalation.
8. The controllable nebulization processing circuit for a ventilator according to claim 1, characterized in that, The atomization output control module includes an atomization control chip U6, a resistor R7, a light-emitting diode D1, a switch S1, and variable resistors R7 and R8 connected in parallel. Pin 1 of the atomization control chip U6 is connected to the power supply module, pin 8 of the atomization control chip U6 is grounded, pin 2 of the atomization control chip U6 is connected to one end of the resistor R5, the other end of the resistor R5 is connected to the positive terminal of the light-emitting diode D1, and the negative terminal of the light-emitting diode D1 is grounded. Pin 4 of the atomization control chip U6 is connected to one end of the switch S1 and the +5V power supply, and the other end of the switch S1 is grounded. The atomization control chip U6 is also connected to one end of the variable resistor R6, one end of the variable resistor R7, and the oscillation drive module. The other ends of the variable resistors R6 and R7 are connected to each other and grounded. The variable resistors R6 and R7 are used to control the atomization output based on the change in their resistance values.
9. The controllable nebulization processing circuit for a ventilator according to claim 1, characterized in that, The oscillation drive module includes an atomizing plate P1, an inductor L1, a capacitor C5, resistors R8, R9, R10, R11, and R12. One end of resistor R12 is connected to pin 6 of the atomization control chip U6. Resistor R12 and resistor R8 are connected in series. The end of resistor R8 away from resistor R12 is connected to pin 2 of the atomizing plate P1 and one end of inductor L1. The other end of inductor L1 is connected to pin 1 of the atomizing plate P1 and one end of capacitor C5. The other end of capacitor C5 is grounded. Inductor L1 is also connected to a field-effect transistor to amplify the waveform voltage. The field-effect transistor is also connected to resistors R9, R10, and R11. The ends of resistors R9 and R10 away from the field-effect transistor are grounded. The other end of resistor R11 is connected to pin 7 of the atomization control chip U6.
10. A controllable nebulizer nebulization processing circuit according to claim 6, characterized in that, The main control chip U1 is an 89C52 microcontroller, the digital-to-analog converter chip U2 of the carbon dioxide concentration detection module and the digital-to-analog converter chip of the pressure detection module are ADC0832 digital-to-analog converters, and the display processing chip U3 is an LCD1602 liquid crystal display chip.