An android device that simulates various physiological characteristics when a person is breathing normally

Abstract

The application is a bionic device for simulating various physiological characteristics when a human being breathes normally, comprising a human body half model, a simulated lung breathing device arranged in the trunk of the human body half model, a nasal cavity trachea and an oral cavity trachea arranged in the head cavity of the human body half model, an opening and closing valve arranged on the nasal cavity trachea and the oral cavity trachea, the nasal cavity trachea and the oral cavity trachea connected with the simulated lung breathing device through the trachea, the nasal cavity trachea being communicated with a nasal cavity, the nasal cavity being provided with a PTC ceramic heating sheet, an ultrasonic atomizer and a temperature and humidity sensor, the ultrasonic atomizer being connected with a liquid supply device, the simulated lung breathing device being wrapped with a heat tracing band outside, the oral cavity trachea extending to an oral cavity and being sealedly connected with a flow sensor, and the simulated lung breathing device being connected with a CO2 injection device. The application can simulate the airflow movement of human body breathing under different parameters, can warm, humidify and regulate the end-expiratory CO2 content of the breathing gas, and provides a physical experimental device for virus transmission mechanism research.

Description

Technical Field

[0001] This invention relates to the field of simulating respiratory characteristics, and more particularly to a bionic human device that simulates various physiological characteristics of normal human breathing. Background Technology

[0002] This year, there have been frequent major public health emergencies worldwide involving airborne transmission via droplets. In research on these infectious disease events, the mechanism of virus transmission through human droplets is particularly important. Respiratory simulation devices can realistically simulate the human breathing process, providing effective evidence for preventing the large-scale spread of public infectious diseases through experimental research on virus transmission mechanisms. Currently, research on respiratory simulation devices involves interdisciplinary issues of medicine and engineering applications. However, existing research mostly focuses on ventilator testing, with relatively few devices capable of generating respiratory simulations, thus failing to adequately support research. Summary of the Invention

[0003] The present invention aims to overcome the shortcomings of the prior art and provide a bionic human device that simulates various physiological characteristics of normal human breathing.

[0004] To achieve the above objectives, the present invention adopts the following technical solution:

[0005] A bionic human device simulating various physiological characteristics of normal human breathing includes a human half-body model. The torso of the half-body model contains a simulated lung breathing device. The head cavity of the half-body model contains a nasal trachea and an oral trachea, each equipped with an on / off valve. Both the nasal and oral tracheas are connected to the simulated lung breathing device via tracheas. The nasal trachea connects to the nasal cavity. PTC ceramic heating pads are located on both sides of the nasal cavity. An ultrasonic nebulizer is connected to the lower part of the nasal cavity, and the ultrasonic nebulizer is connected to a liquid supply device. A temperature and humidity sensor is located at the upper part of the nasal cavity. A heating cable is wrapped around the simulated lung breathing device. The oral trachea extends out of the oral cavity and is sealed with a flow sensor. A nasopharyngeal tube connects the nasal cavity and the oral cavity. The temperature and humidity sensor and the flow sensor are connected to a PLC processor. The simulated lung breathing device is connected to a CO2 injection device.

[0006] The simulated lung breathing device includes an upper fixed plate and a lower fixed plate. Two cylinders are installed between the upper and lower fixed plates. The bottom of the piston inside each cylinder is connected to a push rod of a servo electric cylinder. The push rod of the servo electric cylinder is mounted on a lead screw, which is connected to a servo motor. The upper fixed plate has a hollow structure inside. The top of each cylinder is connected to the hollow structure of the upper fixed plate. The top of the hollow structure of the upper fixed plate is connected to a trachea. A heat tracing cable is wrapped around the outside of the cylinder.

[0007] The liquid supply device includes a water tank installed inside the nasal cavity, a liquid level sensor inside the water tank, and the liquid level sensor is connected to a PLC processor. The water tank is connected to an external water source through a peristaltic pump and a conduit.

[0008] The CO2 injection device includes an injection pipe connected to the inner cavity of the upper fixed plate of the simulated lung breathing device, and a thermal flow meter and a needle valve are sequentially installed on the injection pipe.

[0009] The beneficial effects of this invention are: this invention can simulate the airflow movement of human respiration under different parameters, and can heat and humidify the respiratory gas and regulate the CO2 content at the end of respiration, providing a physical experimental device for the study of virus transmission mechanisms. Attached Figure Description

[0010] Figure 1 This is the left view of the present invention;

[0011] Figure 2 This is the front view of the present invention;

[0012] Figure 3 This is a detailed view of the head structure of the present invention;

[0013] Figure 4 This is a schematic diagram of the structure of the PTC ceramic heating element in this invention;

[0014] Figure 5 This is a schematic diagram of the ultrasonic atomizer in this invention;

[0015] Figure 6 This is a schematic diagram of the temperature and humidity sensor in this invention;

[0016] Figure 7 This is a fitting graph of the respiratory process data of experimental subject 1 in a specific embodiment;

[0017] Figure 8 This illustrates the relationship between calm breathing flow rate and time in a specific embodiment.

[0018] Figure 9 This is a specific example illustrating the relationship between shallow, rapid breathing flow and time.

[0019] Figure 10 This is a specific example illustrating the relationship between deep, slow breathing flow rate and time.

[0020] Figure 11 This is a specific example illustrating the relationship between respiratory flow and time in elderly individuals.

[0021] Figure 12 This is a specific example illustrating the relationship between infant respiratory flow and time.

[0022] Figure 13 This is the relationship between respiratory flow and time in State 1 of the specific embodiment;

[0023] Figure 14 This is the relationship between respiratory flow and time in state 2 of the specific embodiment;

[0024] In the diagram: 1-Human half-body model; 2-Simulated lung breathing device; 3-Nasal trachea; 4-Oral trachea; 5-Trachea; 6-Nasal cavity; 7-PTC ceramic heating element; 8-Ultrasonic nebulizer; 9-Liquid supply device; 10-Temperature and humidity sensor; 11-Heat tracing tape; 12-Oral cavity; 13-Flow sensor; 14-CO2 injection device; 15-Simulated chest cavity movement device.

[0025] 201 - Upper fixing plate; 202 - Lower fixing plate; 203 - Cylinder; 204 - Cylinder piston; 205 - Servo electric cylinder; 206 - Push rod; 207 - Servo motor;

[0026] 1401 - Injection pipe; 1402 - Thermal flow meter; 1403 - Needle valve;

[0027] The following will describe in detail, with reference to the accompanying drawings, embodiments of the present invention. Detailed Implementation

[0028] The principles and features of the present invention are described below with reference to the accompanying drawings. The examples given are for illustrative purposes only and are not intended to limit the scope of the invention. The invention is described more specifically in the following paragraphs by way of example with reference to the accompanying drawings. The advantages and features of the invention will become clearer from the following description. It should be noted that the drawings are in a very simplified form and use non-precise proportions, and are only used to facilitate and clarify the illustration of the embodiments of the invention.

[0029] It should be noted that when a component is described as "fixed to" another component, it can be directly on the other component or may have a component in between. When a component is considered "connected to" another component, it can be directly connected to the other component or may have a component in between. When a component is considered "set on" another component, it can be directly set on the other component or may have a component in between. The terms "vertical," "horizontal," "left," "right," and similar expressions used in this document are for illustrative purposes only.

[0030] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention pertains. The terminology used herein in the description of the invention is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. The term "and / or" as used herein includes any and all combinations of one or more of the associated listed items.

[0031] The present invention will be further described below with reference to the accompanying drawings and embodiments:

[0032] Human respiration can be divided into nasal breathing and mouth breathing. Under normal circumstances, it is nasal breathing, which means that the lungs exchange gases with the outside world through the nasal cavity. The breathing process consists of two steps: inhalation and exhalation. When a person inhales, the respiratory muscles contract, the chest cavity and lungs expand, and outside air enters the alveoli. The capillary tissues metabolize and produce carbon dioxide. At this time, the pressure inside the lungs is lower than the external atmospheric pressure. When a person exhales, the respiratory muscles relax, the chest cavity and lungs contract, and the lungs expel carbon dioxide and other gases from the body. The pressure inside the lungs is higher than the external atmospheric pressure.

[0033] The respiratory parameters are as follows:

[0034] Tidal volume: refers to the amount of air inhaled or exhaled by the human body in a resting state. The normal range of tidal volume for the human body is 400-500 ml.

[0035] Respiratory rate: refers to the number of times a person breathes per minute. One inhalation and one exhalation is counted as one breath. The normal respiratory rate of an adult at rest is about 12-20 breaths / min. The respiratory rate of adult women is about 2-3 breaths / min faster than that of adult men. The respiratory rate of the elderly is about 1-2 breaths / min slower than that of young people. The respiratory rate of infants is about 30 breaths / min.

[0036] Breathing ratio: refers to the ratio of the time of one inhalation to the time of one exhalation. The ratio of inhalation to exhalation time is approximately 1:(1.5-2), while the inhalation time is approximately 0.8-1.4 seconds.

[0037] End-tidal CO2 content: refers to the proportion of carbon dioxide in the gas during exhalation. Under normal circumstances, the CO2 content in the human exhaled gas is about 4% of the tidal volume.

[0038] This invention is a bionic human device developed to simulate various parameters of human respiration, mimicking the physiological characteristics of normal human breathing. Specifically, it includes:

[0039] A bionic humanoid device that simulates various physiological characteristics of normal human breathing, such as... Figures 1-3As shown, the device includes a human half-body model 1. The torso of the human half-body model 1 contains a simulated lung breathing device 2. The head cavity of the human half-body model 1 contains a nasal trachea 3 and an oral trachea 4. Both the nasal trachea 3 and oral trachea 4 are equipped with opening and closing valves. The nasal trachea 3 and oral trachea 4 are connected to the simulated lung breathing device 2 via tracheas 5. The nasal trachea 3 connects to a nasal cavity 6. PTC ceramic heating pads 7 are located on both sides of the nasal cavity 6. An ultrasonic nebulizer 8 is connected to the lower part of the nasal cavity 6. The ultrasonic nebulizer 8 is connected to a liquid supply device 9. A temperature and humidity sensor 10 is located at the upper part of the nasal cavity 6. A heating cable 11 is wrapped around the outside of the simulated lung breathing device 2. The oral trachea 4 extends out of the oral cavity 12 and is sealed to a flow sensor 13. A nasopharyngeal tube connects the nasal cavity 6 and the oral cavity 12. The temperature and humidity sensor 10 and the flow sensor 13 are connected to a PLC processor. The simulated lung breathing device 2 is connected to a CO2 injection device 14. A simulated chest cavity rise and fall device 15 is located in the chest cavity inside the torso of the human half-body model 1.

[0040] The human half-body model 1 extends from the shoulders to the pelvis and includes arms. Since the torso of the human half-body model 1 needs to house a simulated lung breathing device 2, and existing torsos are too slender for the internal dimensions to be realized, but standard human torso modeling is complex, 3D scanning technology was used to scan and model existing standard human solid models. Finally, the scanned model was 3D printed to create the torso model of human half-body model 1. Carbon fiber is attached to the exterior of the torso to enhance its strength, and a rubber suit is worn on the outside of the breathing manipulator, simulating human skin while also improving its protective performance against water spray disinfection.

[0041] During normal human respiration, both the oral cavity 12 and nasal cavity 6 in the respiratory system transport air through exhalation and inhalation. The oral cavity 12 and nasal cavity 6 are connected by the nasopharyngeal tube. The posterior part of the oral cavity 12 connects to the pharynx, extending upwards to the nasal cavity 6 and downwards to the larynx. The posterior nasal openings in the nasal cavity 6 connect to the nasopharynx, structurally enabling gas exchange between the nasal cavity 6 and the oral cavity 12. The nasal cavity 6 warms, humidifies, and cleans the inhaled air, while the oral cavity 12 primarily assists in respiration.

[0042] In the head design of the human half-body model 1, based on the actual human breathing process, it is divided into two parts: the nasal cavity component and the oral cavity component. The main functions designed in the nasal cavity 6 are heating and humidifying the breathing gas, and temperature and humidity detection; the oral cavity 12 has teeth and a tongue, and the lower jaw can be manually opened and closed to adjust the opening angle of the oral cavity 12.

[0043] In the nasal cavity component design, two patch-type PTC ceramic heating pads 7 are added to both sides of the nasal cavity 6 to heat the breathing gas. The patch-type PTC ceramic heating pads 7 are as follows: Figure 4As shown, this is a new type of electronic ceramic material, characterized by self-controlled constant temperature heating, high thermal efficiency, and uniform heating. The patch-type PTC ceramic heating element 7 is set to a constant temperature of 70℃ and is placed on both sides of the nasal cavity 6, which can achieve an exhaled gas temperature of about 36℃.

[0044] In the nasal cavity component design, an ultrasonic nebulizer 8 is connected below the nasal cavity 6 to achieve the function of humidifying the breathing gas. The ultrasonic nebulizer 8 is as follows: Figure 5 As shown, the working principle is to use ultrasonic energy to turn water into a fine mist. The amount of mist produced is adjustable, and the droplets are small and uniform. Compared with the heating atomization method, this module saves 90% of energy. Due to the heat generated by the electronic components in the ultrasonic atomizer 8, the atomized droplets are also heated to a certain extent. A small water tank is equipped in the nasal cavity 6. The water tank has liquid level sensors at the top and bottom, which can realize real-time monitoring of the water level. When the water tank is low, water can be replenished from the outside through a peristaltic pump and a tube.

[0045] The required humidification amount for the bionic human device can be calculated using a formula.

[0046] W = γ × G × (d2 - d1) × 10 -3 ;

[0047] In the formula, W represents the effective humidification capacity (kg / h); γ represents the specific gravity of air (taken as 1.2); and G represents the fresh air volume (maximum 8.28 m³ / h). 3 / h; d2 represents the air moisture content after humidification, which can be obtained from the enthalpy-humidity chart as 37g / Kg; d1 represents the air moisture content before humidification, 10g / Kg.

[0048] Calculations show that the maximum humidification capacity required for the bionic human device is 0.27 kg / h, while the maximum humidification capacity of the ultrasonic nebulizer is 0.5 kg / h, which is suitable for humidifying the breathing gas of the bionic human device.

[0049] The temperature and humidity of the respired air are important characteristics during human respiration. A temperature and humidity sensor 10 is installed above the nasal cavity 6 to monitor the temperature and humidity of the respired air from the bionic human device in real time. This data can be used as reference data when conducting experimental analysis using the bionic human device. The temperature and humidity sensor 10... Figure 6 As shown, the sensor used is the TE HPP815A535 from TE Connectivity. This product integrates a humidity sensor and an NTC temperature sensor into one unit, featuring a built-in microcontroller chip. It is characterized by its small size, high measurement accuracy, wide applicability, strong stability, and multiple signal outputs. The sensor's temperature data is converted by a temperature acquisition and transmitter and transmitted to the PLC processor via the Modbus protocol.

[0050] The selected PLC processor is the Siemens S7-200smart model.

[0051] The simulated lung breathing device 2 includes an upper fixed plate 201 and a lower fixed plate 202. Two cylinders 203 are installed between the upper fixed plate 201 and the lower fixed plate 202. The bottom of the cylinder piston 204 inside each cylinder 203 is connected to the push rod 206 of the servo electric cylinder 205. The push rod 206 of the servo electric cylinder 205 is movably mounted on a lead screw, which is connected to a servo motor 207. The upper fixed plate 203 has a hollow structure inside. The top of each cylinder 203 is connected to the hollow structure of the upper fixed plate 203. The top of the hollow structure of the upper fixed plate 203 is connected to the air pipe 5. The heating cable 11 is wrapped around the outside of the cylinder 203. A pressure sensor is installed on the upper fixed plate 201 corresponding to the cavity. The pressure sensor is connected to the PLC processor.

[0052] The main structure of the simulated lung breathing device 2 of this invention consists of a servo motor 207, a servo electric cylinder 205, a cylinder 203, an upper fixed plate 201, and a lower fixed plate 202. The servo electric cylinder 205 is chosen because it integrates the servo motor 207 and the lead screw. Due to its closed-loop servo control, the servo electric cylinder 205 offers high control precision and flexible configuration. The push rod 206 precisely converts the rotational motion of the servo motor 207 into the vertical linear motion of the cylinder piston 204 of the cylinder 203.

[0053] The simulated lung breathing device 2 uses a cylinder 203 to simulate the structure of the human lung. The up-and-down movement of the cylinder piston 204 simulates the contraction and relaxation of the respiratory muscles during human respiration. Its working principle involves a servo motor 207 rotating in both directions, driving the push rod 206 inside the servo cylinder 205 to move up and down. The push rod 206 is connected to the cylinder piston 204. When the servo motor 207 reverses, the push rod 206 drives the cylinder piston 204 upwards, expelling gas from the cylinder 203, simulating the human exhalation process; conversely, the reverse motion simulates the human inhalation process. The upper fixed plate 201 has an internal gas channel, connects to the air pipe 5 of the upper connector assembly, and is connected to a pressure sensor that detects the pressure inside the simulated lung. A heating cable 11 is wrapped around the cylinder 203. The heating cable 11 heats the simulated lung temperature and also evaporates and cleans water droplets inside the simulated lung through high temperature.

[0054] The simulated lung tidal volume is determined by the distance traveled by the piston 204 in the cylinder driven by the servo motor 207. The flow sensor 13 used in the bionic human device to simulate human tidal volume is a CAFS4000B-300-IV-A bidirectional gas mass flow meter from Consens-SmithKline.

[0055] The experimental environment was a room without ventilation. During the breathing process of the bionic human device, the gas flow rates in the nasal cavity 6 and oral cavity 12 were the same under the same breathing parameters. Therefore, to facilitate the connection of the flow sensor 13, the flow sensor 13 was connected to the oral cavity 12 of the bionic human device. Measuring the gas flow rate at the oral cavity 12 is equivalent to measuring the flow rate during the breathing process of the bionic human device. When measuring the respiratory gas flow rate at the oral cavity 12, the oral trachea 4 of the bionic human device was extended to the outside, and the external port of the oral trachea 4 was sealed to the gas flow meter 13, with good sealing at the connection. When reading the gas flow rate data, the signal line of the gas flow meter 13 was connected to the analog input port of the PLC. The data from the gas flow meter 13 could be monitored in real time through the OPC client S7-200 PC Access SMART. All monitored data had timestamps, facilitating the correspondence between the monitored instantaneous flow rate value and time, thus obtaining the experimental flow rate data.

[0056] During normal human respiration, the inhaled gas is air, of which CO2 accounts for about 0.03%. At the end of respiration, CO2 accounts for about 4%. Therefore, in simulating human exhalation, it is necessary to increase the concentration of CO2 at the end of respiration.

[0057] The simulated alveolar gas exchange is achieved by the CO2 injection device 14, which consists of an injection pipe 1401, a thermal gas flow meter 1402, and a needle valve 1403. The amount of CO2 injected at the end of the breath is calculated based on the tidal volume, which is generally 4% of the tidal volume. The corresponding CO2 volume is injected to simulate the amount of CO2 finally exhaled.

[0058] A simulated chest cavity movement device 15 is designed in the chest cavity area of ​​the human half-body model 1. This device consists of a motor, a positioning plate, and a moving plate. It controls the forward and backward movement of the chest cavity during the inhalation and exhalation processes of the bionic human device, simulating the chest cavity movement during human respiration. The design principle of the simulated chest cavity movement device 15 is to control the forward and backward movement of the motor, which drives the moving plate, made of the chest cavity material, to move forward and backward. When the bionic human device inhales, the motor moves forward, causing the moving plate to move outward, thus expanding the chest cavity. When the bionic human device exhales, the motor moves the chest cavity back to its normal position. The motor's movement speed and distance are directly proportional to the respiratory time and tidal volume, respectively. Because the breathing contour movement device is located in the chest cavity of the human half-body model 1, and the simulated lung breathing device 2 is placed inside the model, the remaining space for the motor is small. Therefore, the physical dimensions of the motor must be considered when selecting the motor for the breathing contour movement device. Due to the relatively low control precision requirements, a through-type stepper motor, capable of linear reciprocating motion, was ultimately chosen. Specific implementation examples:

[0060] The following is an experiment to detect the actual flow rate during human respiration:

[0061] Five male and five female students aged 22-30 were selected as subjects for the experiment. A gas flow meter was used to detect the airflow in the nasal cavity during the subjects' normal breathing. Five respiratory cycles were collected from each of the 10 subjects to obtain the real instantaneous flow rate and time relationship during human breathing.

[0062] The basic information of the experimental subjects is shown in Table 1.

[0063] Table 1 Basic Information of Experimental Subjects

[0064]

[0065] Taking experimental subject 1 as an example, the experimental data on the relationship between instantaneous respiratory flow and time for experimental subject 1 were fitted using Fourier series in MATLAB. The fitted graph of the relationship between instantaneous respiratory flow and time for experimental subject 1 is shown below. Figure 7 As shown, inspiratory flow rate is positive and expiratory flow rate is negative. The coefficient of determination of the fitted equation is 0.9167, indicating a good overall fit. Therefore, the instantaneous flow rate versus time during human respiration can be approximated as a sinusoidal law.

[0066] Data from 10 experimental subjects were analyzed, revealing that a single cycle of human respiration can be divided into 10 segments. Based on changes in respiratory flow during respiration, these segments were further categorized into five phases: rapid increase, slow increase, stable flow, slow decrease, and rapid decrease. The ratio of the time spent maintaining stable respiratory flow to the total respiratory cycle time was averaged across the 10 data sets. This resulted in the maximum stable respiratory flow time accounting for approximately 25.7% of a respiratory cycle. For ease of computation, the bionic human device simulated maximum respiratory flow time at 26% of a respiratory cycle.

[0067] The experimental verification process of the bionic human device's breathing process is as follows:

[0068] In the process of adjusting the instantaneous respiratory flow rate of the bionic human device according to an approximately sinusoidal relationship with time, due to the small tidal volume, the normal operating distance of the piston 204 in the simulated lung cylinder is between 2-6 cm. Although multi-segment speed adjustment is possible, considering that both the actual respiratory time and the piston 204's operating distance are short, multi-segment speed adjustment during the respiratory process is not very meaningful. Therefore, it is more reasonable to divide the inhalation or exhalation process of the bionic human device into 3 or 5 segments for speed adjustment based on the respiratory frequency. The following experimental verification of the simulated respiratory process of the breathing manipulator by changing different respiratory parameters is as follows.

[0069] I. The normal adult human respiration process

[0070] In the current medical definition, the respiratory state of a normal adult can be divided into calm breathing, shallow and rapid breathing, and deep and slow breathing. The three respiratory states are determined by the tidal volume and respiratory rate, as shown in Table 2.

[0071] Table 2 Parameters of different respiratory states in normal adults

[0072]

[0073] The parameters of the bionic human device were set according to the tidal volume and respiratory rate in the table, with a breathing time of 1 minute. Data from flow sensor 13 was monitored in real time using an S7-200 PC Access SMART. The instantaneous respiratory flow rate of the bionic human device detected in real time by flow sensor 13 was recorded, and the data from flow sensor 13 was processed to create a flow rate versus time graph. The correspondence between respiratory flow rate and time under quiet breathing conditions is shown below. Figure 8 As shown; the relationship between respiratory flow and time under shallow and rapid breathing is as follows: Figure 9 As shown; the relationship between respiratory flow and time during deep, slow breathing is as follows: Figure 10 As shown.

[0074] As shown in the graph of respiratory flow versus time, the instantaneous output flow rate during simulated lung respiration meets the requirements of the human body's tidal volume range (flow sensor 13 is bidirectional, positive for inhalation and negative for exhalation). The respiratory cycle of quiet breathing is 3.75s, the average maximum instantaneous flow rate is 26.27L / min, and the duration of the maximum instantaneous flow rate during inhalation or exhalation is 0.5s. The maximum speed of its servo motor 207 is 146 rpm. The respiratory cycle of shallow and rapid breathing is approximately 3s, the average maximum instantaneous flow rate is 20.26L / min, and the duration of the maximum instantaneous flow rate during inhalation or exhalation is 0.4s. The maximum speed of its servo motor 207 is 115 rpm. The respiratory cycle of deep and slow breathing is approximately 5s, the average maximum instantaneous flow rate is 37.17L / min, and the duration of the maximum instantaneous flow rate during inhalation or exhalation is 0.7s. The maximum speed of its servo motor 207 is 227 rpm. Under different breathing states, there are corresponding breathing cycles and sinusoidal flow peaks. By integrating the flow peaks, the minute ventilation is calculated to meet the preset breathing process. The breathing process of the bionic human device can simulate the real breathing process of a normal adult human.

[0075] II. Respiratory Process in Humans at Other Ages

[0076] The respiratory parameters for the elderly and infants were set as shown in Table 3.

[0077] Table 3 Respiratory parameters of people at other ages

[0078]

[0079] Based on the tidal volume and respiratory rate in the table, the parameters for the respiratory manikin were set. The flow sensor data were then processed, and a flow-time graph was plotted. The relationship between respiratory flow and time for elderly individuals is shown below. Figure 11 As shown; the relationship between respiratory flow and time under shallow and rapid breathing is as follows: Figure 12 As shown.

[0080] The graphs showing the relationship between respiratory flow and time in the elderly and infants reveal that the respiratory cycle of the elderly is 6 seconds, with an average maximum instantaneous flow rate of 20.53 L / min and a duration of 0.8 seconds for the maximum instantaneous flow rate during inspiration or expiration. The maximum speed of their servo motor 207 is 103 rpm. In contrast, the respiratory cycle of infants is approximately 2 seconds, with an average maximum instantaneous flow rate of 29.15 L / min and a duration of 0.3 seconds for the maximum instantaneous flow rate during inspiration or expiration. The maximum speed of their servo motor 207 is 149 rpm. Both the elderly and infants exhibit corresponding respiratory cycles and sinusoidal flow rate peaks during respiration. Integrating these peak flow rates yields a minute ventilation rate that matches the preset respiratory process. Therefore, the bionic human device's breathing process can accurately simulate the real breathing process of people of other ages.

[0081] III. Respiratory Processes in Other States

[0082] Using the normal adult breathing state as a prototype, we conducted an experimental study on the breathing process by changing various parameters such as the breathing ratio, in order to verify the accuracy of the breathing simulator in other breathing modes. The specific breathing states are shown in Table 4.

[0083] Table 4 Respiratory parameters under other conditions

[0084]

[0085] The relationship between respiratory flow and time in state 1 is as follows: Figure 13 As shown; the relationship between respiratory flow and time in state 2 is as follows: Figure 14 As shown.

[0086] From the above graph showing the relationship between respiratory flow and time during different respiratory parameters, it can be seen that in state 1, the respiratory cycle is 5s, the average maximum instantaneous flow rate during inspiration is 30.41L / min, the duration of maximum instantaneous flow rate is 0.4s, and the maximum speed of servo motor 207 is 180 rpm; during expiration, the average maximum instantaneous flow rate is 20.28L / min, the duration of maximum instantaneous flow rate is 0.9s, and the maximum speed of servo motor 207 is 90 rpm. In state 2, the respiratory cycle is 5s, the average maximum instantaneous flow rate during inspiration is 50.77L / min, the duration of maximum instantaneous flow rate is 0.3s, the maximum speed of servo motor 207 is 323 rpm; during expiration, the average maximum instantaneous flow rate is 20.45L / min, the duration of maximum instantaneous flow rate is 0.7s, and the maximum speed of servo motor 207 is 110 rpm. During the breathing process under different breathing parameters, there are corresponding breathing cycles and sinusoidal flow peaks. By integrating the flow peaks during inhalation and exhalation respectively, the minute ventilation is calculated to meet the preset breathing process. The breathing simulation of the human breathing process can meet the requirements of simulating the real human breathing process with different breathing ratios and different breath-holding times.

[0087] In summary, through experiments on the breathing process of people of different ages and with different breathing parameters using a breathing simulator, it can be verified that the breathing process of the breathing simulator can simulate the breathing process of people at different age stages, and the parameters of tidal volume, respiratory rate, respiratory ratio and breath-holding time can be adjusted. The maximum tidal volume of the lungs can be adjusted to 2300ml.

[0088] During respiration, the CO2 content at the end of the breath can be increased proportionally according to the respiratory gas, and the respiratory gas can also be heated and humidified. After the PTC ceramic heating element 7 is preheated for 1 minute, the gas temperature at the nasal cavity 6 during respiration is between 36.0-37.2℃, and the humidity of the exhaled gas is between 91%-100%, which meets the temperature and humidity changes of human respiratory gas.

[0089] This invention can simulate the airflow movement of human respiration under different parameters, and can heat and humidify the respiratory gas and regulate the CO2 content at the end of respiration, providing a physical experimental device for the study of virus transmission mechanisms.

[0090] The present invention has been described above by way of example with reference to the accompanying drawings. Obviously, the specific implementation of the present invention is not limited to the above-described manner. Any improvements made using the inventive concept and technical solution of the present invention, or direct application to other occasions without modification, are all within the protection scope of the present invention.

Claims

1. A bionic man device that simulates various physiological characteristics when a human is breathing normally, characterized by, Includes a human half-body model (1), the shape of which extends from the shoulders to the pelvis and includes arms, with carbon fiber attached to the outside of the torso and a rubber suit. The human half-body model (1) has a simulated lung breathing device (2) inside its torso. The head cavity of the human half-body model (1) has a nasal trachea (3) and an oral trachea (4). Both the nasal trachea (3) and the oral trachea (4) are equipped with opening and closing valves. The nasal trachea (3) and the oral trachea (4) are connected to the simulated lung breathing device (2) through tracheas (5). The nasal trachea (3) is connected to the nasal cavity (6). PTC ceramic heating pads (7) are provided on both sides of the nasal cavity (6). An ultrasonic nebulizer (8) is connected to the lower part of the nasal cavity (6). The ultrasonic nebulizer (8) is connected to a liquid supply device (9). A temperature and humidity device is provided at the upper part of the nasal cavity (6). Temperature sensor (10), simulated lung breathing device (2) is wrapped with a heat tracing cable (11), oral trachea (4) extends out of oral cavity (12) and is sealed with flow sensor (13), nasopharyngeal tube is connected between nasal cavity (6) and oral cavity (12), oral cavity (12) has teeth and tongue, the lower jaw can be manually opened and closed to adjust the opening angle of oral cavity (12), temperature and humidity sensor (10) and flow sensor (13) are connected to PLC processor, simulated lung breathing device (2) is connected to CO2 injection device (14), and the human half-body model (1) has a simulated chest cavity rise and fall device (15) in the chest cavity inside the torso. The simulated chest cavity undulation device (15) includes a through stepper motor mounted on a positioning plate, the through stepper motor being connected to an undulation screw, the nut of the undulation screw being connected to a moving plate, and the moving plate moving back and forth inside the chest cavity.

2. The bionic man device of claim 1, wherein, The simulated lung breathing device (2) includes an upper fixed plate (201) and a lower fixed plate (202). Two cylinders (203) are installed between the upper fixed plate (201) and the lower fixed plate (202). The bottom of the cylinder piston (204) inside each cylinder (203) is connected to the push rod (206) of the servo electric cylinder (205). The push rod (206) of the servo electric cylinder (205) is movably mounted on the lead screw, which is connected to the servo motor (207). The upper fixed plate (203) has a hollow structure inside. The top of each cylinder (203) is connected to the hollow structure of the upper fixed plate (203). The top of the hollow structure of the upper fixed plate (203) is connected to the trachea (5). The heat tracing cable (11) is wrapped around the outside of the cylinder (203).

3. The bionic man device of claim 2, wherein, A pressure sensor is installed in the corresponding cavity on the upper fixed plate (201), and the pressure sensor is connected to the PLC processor.

4. A bionic human device simulating various physiological characteristics of normal human breathing according to claim 3, characterized in that, The liquid supply device (9) includes a water tank installed inside the nasal cavity (6), a liquid level sensor is installed in the water tank, the liquid level sensor is connected to the PLC processor, and the water tank is connected to an external water source through a peristaltic pump and a conduit.

5. A bionic human device simulating various physiological characteristics of normal human breathing according to claim 4, characterized in that, The CO2 injection device (14) includes an injection pipe (1401) connected to the inner cavity of the upper fixed plate (201) of the simulated lung breathing device (2). A thermal flow meter (1402) and a needle valve (1403) are sequentially provided on the injection pipe (1401).

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