Noninvasive expectoration machine

Abstract

The invention discloses a noninvasive expectoration machine which comprises a control panel, a blower device, an external connecting channel and an oscillation generating device, the control panel can control the blower device to conduct positive pressure inflation or negative pressure air exhaust, and then the oscillation generating device is controlled based on a preset oscillation instruction; the air passage connecting end of the oscillation generating device is opened or closed through the opening and closing device, and the fluid resistance in the air passage of the blower device is adjusted, so that the air flow of positive pressure inflation and negative pressure exhaust at the breathing mask is oscillated, and the cough state of a patient is simulated. Therefore, deep respiration of the patient can be simulated through positive-pressure air inflation and negative-pressure air exhaust of the blower device, and the cough state of the patient is simulated in combination with the oscillation generation device, so that secretions in the respiratory tract of the patient oscillate along with oscillation of air flow, and then the secretions are separated from the respiratory tract of the patient; secretions in the respiratory tract of the patient can be quickly loosened and discharged, and the sputum excretion efficiency of the patient is improved.

Description

Technical Field

[0001] This invention relates to the field of motor control, and in particular to a non-invasive expectorant machine. Background Technology

[0002] Traditional cough suppressants are devices that assist patients' breathing by using positive pressure inflation and negative pressure degassing. Specifically, during a cough cycle, the blower in the cough suppressant first introduces positive pressure gas into the patient's airway to simulate the patient's deep inhalation, allowing the patient's lungs to fully expand and loosen the secretions that have condensed in the patient's airway. Then, it quickly switches to negative pressure degassing from the patient's airway to simulate the patient's forceful exhalation, prompting the secretions in the patient's airway to be expelled, thereby clearing the secretions in the patient's airway.

[0003] Based on this, traditional expectoration machines simulate the patient's breathing state to assist in expectoration. However, if the secretions in the respiratory tract are viscous and adhere to the respiratory tract, traditional expectoration machines cannot effectively separate the secretions from the respiratory tract, resulting in poor clearance of secretions. Summary of the Invention

[0004] The purpose of this invention is to provide a non-invasive expectorant device that can simulate a patient's deep breathing through positive pressure inflation and negative pressure suction of a blower, and also incorporates an oscillation generator to simulate a patient's cough state. This causes the secretions in the patient's respiratory tract to oscillate with the airflow, thereby detaching them from the patient's respiratory tract and ensuring that the secretions in the patient's respiratory tract can be quickly loosened and discharged, thus improving the patient's expectoration efficiency.

[0005] To solve the above-mentioned technical problems, the present invention provides a non-invasive expectorant device, comprising:

[0006] The control board has a first output terminal connected to the control terminal of the blower and a second output terminal connected to the control terminal of the oscillation generator. The control board is used to control the blower to perform positive pressure inflation or negative pressure degassing, and to control the oscillation generator based on a preset oscillation command.

[0007] The blower device has its air duct channel connected to the first end of the external connection channel. The blower device is used to perform positive pressure inflation or negative pressure degassing through a breathing mask.

[0008] The external connection channel has a second end connected to the breathing mask and a third end connected to the airway connection end of the oscillation generator.

[0009] The oscillation generating device is used to open or close its airway connection terminal based on the preset oscillation command under the control of the control board, so as to cause the airflow at the breathing mask to oscillate during positive pressure inflation and negative pressure degassing.

[0010] Preferably, it also includes a pressure detection module;

[0011] The input end of the pressure detection module is connected to the air duct channel of the blower, and the output end of the pressure detection module is connected to the first input end of the control board, for detecting the actual pressure in the air duct channel;

[0012] The control panel is also used to control the blower based on a preset pressure range, so as to adjust the air volume in the air duct of the blower and make the actual pressure within the preset pressure range.

[0013] Preferably, the blowing device includes a blower and a breathing gas switching device;

[0014] The air inlet of the blower is connected to the positive pressure air inlet of the breathing air switching device, the air outlet of the blower is connected to the negative pressure air outlet of the breathing air switching device, and the control terminal of the blower is connected to the third output terminal of the control board for adjusting the air volume of the air inlet or the air outlet based on the control of the control board.

[0015] The tracheal channel of the breathing gas switching device is connected to the first end of the external connection channel, and the control end of the breathing gas switching device is connected to the first output end of the control board. It is used to switch the positive pressure inflation port and the negative pressure suction port based on the control of the control board, so as to perform positive pressure inflation or negative pressure suction.

[0016] Controlling the blower based on a preset pressure range to adjust the airflow in the blower's air duct channel, so that the actual pressure is within the preset pressure range, includes:

[0017] The PWM duty cycle is adjusted when controlling the blower based on the preset pressure range to regulate the air volume at the blower's inlet or outlet, so that the actual pressure is within the preset pressure range; the air volume is positively correlated with the PWM duty cycle, and the actual pressure is positively correlated with the air volume.

[0018] Preferably, adjusting the PWM duty cycle when controlling the blower based on the preset pressure range to adjust the air volume at the blower's inlet or outlet, so that the actual pressure is within the preset pressure range, includes:

[0019] When it is determined that the actual pressure is not below the preset pressure range and the airway is in an under-pressure state, the PWM duty cycle when controlling the blower is increased by a first preset step.

[0020] After determining that the actual pressure rises to enter the preset pressure range, the PWM duty cycle when controlling the blower is reduced by a second preset step.

[0021] Preferably, after determining that the actual pressure has risen to within the preset pressure range, and after reducing the PWM duty cycle when controlling the blower with a second preset step, the method further includes:

[0022] If it is determined that the actual pressure has increased and the airway is in an overpressure state, then the PWM duty cycle is reduced to the minimum duty cycle.

[0023] Preferably, before increasing the PWM duty cycle for controlling the blower by a first preset step when it is determined that the actual pressure is not within the preset pressure range and the airway is under-pressured, the method further includes:

[0024] The blower is started by controlling the preset initial PWM duty cycle.

[0025] Preferably, the oscillation generating device includes an oscillation generator and an amplitude generator;

[0026] The airway connection end of the oscillation generator is connected to the third end of the external connection channel, and the control end of the oscillation generator is connected to the first output end of the control board. It is used to open or close its airway connection end at a preset oscillation frequency in the preset oscillation command based on the control of the control board, so that the airflow at the breathing mask during positive pressure inflation and negative pressure degassing will oscillate.

[0027] The output terminal of the amplitude generator is connected to the airway connection terminal of the oscillation generator, and the control terminal of the amplitude generator is connected to the first output terminal of the control board. The control terminal is used to adjust the opening of the airway connection terminal of the oscillation generator based on the control of the control board, so that the opening of the airway connection terminal of the oscillation generator corresponds to the preset oscillation amplitude in the preset oscillation command.

[0028] Preferably, the oscillation generator includes a channel control module and an oscillation generation stepper motor;

[0029] The channel control module is connected to the third end of the peripheral connection channel, and the control end of the channel control module is connected to the output end of the oscillation generation stepper motor. It is used to open or close the third end of the peripheral connection channel based on the rotation of the oscillation generation stepper motor, so that the airflow at the breathing mask during positive pressure inflation and negative pressure degassing will oscillate.

[0030] The control terminal of the stepper motor that generates the oscillation is connected to the first output terminal of the control board, and is used to rotate according to the preset oscillation frequency based on the control of the control board.

[0031] Preferably, the amplitude generator includes a channel blocking module and an amplitude generating stepper motor;

[0032] The channel blocking module is connected to the third end of the peripheral connection channel, and the control end of the channel blocking module is connected to the output end of the amplitude generating stepper motor, for adjusting the opening degree of the third end of the peripheral connection channel based on the rotation of the amplitude generating stepper motor;

[0033] The control terminal of the amplitude generating stepper motor is connected to the first output terminal of the control board, and is used to rotate to an angle corresponding to the preset oscillation amplitude based on the control of the control board, so that the opening of the third terminal of the peripheral connection channel corresponds to the preset oscillation amplitude.

[0034] Preferably, it also includes a respiratory detection module and / or a flow detection module;

[0035] The input terminal of the breathing detection module is connected to the breathing mask, and the output terminal of the breathing detection module is connected to the second input terminal of the control board. The breathing detection module is used to detect the airflow direction of the breathing mask to determine the corresponding exhalation and inhalation states and feed them back to the control board so that the control board can control the positive pressure inflation and negative pressure degassing of the blower.

[0036] The input terminal of the flow detection module is connected to the air duct channel of the blower, and the output terminal of the flow detection module is connected to the third input terminal of the control board. The flow detection module is used to detect the air flow in the air duct channel and feed it back to the control board so that the control board can control the blower.

[0037] This application provides a non-invasive expectorant device, including a control board, a blower, an external connection channel, and an oscillation generator. The control board can control the blower to perform positive pressure inflation or negative pressure degassing, and combined with the control of the oscillation generator based on preset oscillation commands, it opens or closes the airway connection end of the oscillation generator, thereby adjusting the fluid resistance inside the tracheal channel of the blower. This causes the airflow during positive pressure inflation and negative pressure degassing at the breathing mask to oscillate, simulating the patient's cough. Therefore, this application not only simulates the patient's deep breathing through the positive pressure inflation and negative pressure degassing of the blower, but also simulates the patient's cough by combining the oscillation generator with the airflow oscillation, causing secretions in the patient's respiratory tract to oscillate and thus detach from the patient's respiratory tract, ensuring that secretions in the patient's respiratory tract can be quickly loosened and expelled, improving the patient's expectoration efficiency. Attached Figure Description

[0038] To more clearly illustrate the embodiments of the present invention, the accompanying drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0039] Figure 1 This is a structural schematic diagram of a non-invasive expectorant provided in this application;

[0040] Figure 2 A schematic diagram of the specific structure of a non-invasive expectorant provided in this application;

[0041] Figure 3 A schematic diagram of a blower device provided in this application being positively pressurized;

[0042] Figure 4 A schematic diagram of a blower device provided in this application performing negative pressure extraction;

[0043] Figure 5 This is a flowchart illustrating the process of a control board controlling a blower, as provided in this application. Detailed Implementation

[0044] The core of this invention is to provide a non-invasive expectorant device that can not only simulate a patient's deep breathing through positive pressure inflation and negative pressure suction of a blower, but also combine an oscillation generator to simulate a patient's cough state, so that the secretions in the patient's respiratory tract oscillate with the airflow, thereby detaching them from the patient's respiratory tract, ensuring that the secretions in the patient's respiratory tract can be quickly loosened and discharged, and improving the patient's expectoration efficiency.

[0045] To make the objectives, technical solutions, and advantages of the embodiments of the present invention clearer, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0046] Please refer to Figure 1 , Figure 1 This is a schematic diagram of a non-invasive expectorant device provided in this application. The non-invasive expectorant device includes:

[0047] Control board 1, the first output terminal of control board 1 is connected to the control terminal of blower 2, the second output terminal of control board 1 is connected to the control terminal of oscillation generator 4, control board 1 is used to control blower 2 to perform positive pressure inflation or negative pressure degassing, and to control oscillation generator 4 based on preset oscillation commands;

[0048] The blower device 2 has its air duct channel connected to the first end of the external connection channel 3. The blower device 2 is used for positive pressure inflation or negative pressure degassing through a breathing mask.

[0049] External connection channel 3, the second end of external connection channel 3 is connected to the breathing mask, and the third end of external connection channel 3 is connected to the airway connection end of the oscillation generator 4;

[0050] The oscillation generator 4 is used to open or close its airway connection end based on the control of the control board 1 according to a preset oscillation command, so that the airflow at the breathing mask during positive pressure inflation and negative pressure de-inflation will oscillate.

[0051] For patients with weakened or lost coughing ability, clearing respiratory secretions, such as sputum, becomes extremely difficult. Retention of secretions can lead to a series of serious complications, including atelectasis, lung infection, and hypoxemia, endangering the patient's life. To facilitate the expulsion of sputum, traditional cough machines typically use a blower to inflate the lungs with positive pressure, causing them to expand. Then, negative pressure is drawn from the lungs, mimicking deep inhalation and exhalation. The pressure difference between the exhaled air and the alveoli in the mask during suction helps move sputum towards the large airways, facilitating its removal. However, if the secretions are viscous and adhere to the airway, deep breathing cannot quickly separate and expel them, reducing sputum clearance efficiency.

[0052] In this application, an additional oscillation generator 4 is added to the traditional expectoration machine. The oscillation generator 4 is connected between the blower 2 and the breathing mask via an external connection channel 3. Specifically, the control board 1 first controls the blower 2 to perform positive pressure inflation and negative pressure degassing through the breathing mask. In actual application, after the patient puts on the breathing mask, the control board 1 controls the blower 2 to perform positive pressure inflation into the patient's lungs through the breathing mask and to perform negative pressure degassing from the patient's lungs through the breathing mask within one respiratory cycle, thereby assisting the patient in taking a deep breath. Meanwhile, because the external connection channel 3, such as the three-way valve, connects to the tracheal channel of the blower 2, the breathing mask, and the airway connection of the oscillation generator 4, when the airway connection of the oscillation generator 4 is opened, the third end of the external connection channel 3 also opens accordingly. Part of the gas in the tracheal channel of the blower 2 flows between the blower 2 and the breathing mask, while part flows to the outside of the cough machine through the oscillation generator 4. At this time, the fluid resistance of the airflow at the breathing mask is small, and the gas pressure at the breathing mask is small. Conversely, when the airway connection of the oscillation generator 4 is closed, the third end of the external connection channel 3 also... When the blower is closed, the gas in the tracheal passage of the blower 2 flows entirely between the blower 2 and the breathing mask. At this time, the fluid resistance of the airflow at the breathing mask is relatively high, and the gas pressure at the breathing mask is relatively high. Based on this, by opening and closing the airway connection end of the oscillation generator 4, the third end of the external connection channel 3 is opened and closed. The fluid resistance of the airflow at the breathing mask also changes accordingly, and the airflow at the breathing mask oscillates, thereby causing the airflow in the patient's respiratory tract to oscillate, simulating the state of the patient coughing, shaking off the secretions adhering inside the patient's respiratory tract, and promoting the discharge of secretions. It should be noted that the opening and closing of the airway connection end mentioned in this application refers to the outlet of the airway connection end being blocked or opened. When the airway connection end is closed, gas cannot pass through, and when the airway connection end is open, gas can pass through.

[0053] For example, when the blower 2 is in positive pressure inflation mode, the blower 2 specifically inflates the breathing mask through the trachea, that is, it inflates the patient's lungs through the breathing mask. If the airway connection of the oscillation generator 4 is open, then part of the gas output from the trachea of ​​the blower 2 flows to the breathing mask, while the other part flows to the outside of the cough machine through the oscillation generator 4. At this time, the fluid resistance of the airflow at the breathing mask is small and the airflow pressure is large. If the airway connection of the oscillation generator 4 is closed, then all the gas output from the trachea of ​​the blower 2 flows to the breathing mask. At this time, the fluid resistance of the airflow at the breathing mask is large and the airflow pressure is large. This cycle continues. When the oscillation generator 4 opens and closes the airway connection under the control of the control board 1, the airflow at the breathing mask oscillates.

[0054] In summary, this application not only simulates the patient's deep breathing through the positive pressure inflation and negative pressure suction of the blower device 2, but also combines the oscillation generator device 4 to simulate the patient's cough state, so that the secretions in the patient's respiratory tract oscillate with the airflow, thereby detaching from the patient's respiratory tract, ensuring that the secretions in the patient's respiratory tract can be quickly loosened and discharged, and improving the patient's sputum expectoration efficiency.

[0055] Based on the above embodiments:

[0056] In a preferred embodiment, a pressure detection module is also included;

[0057] The input end of the pressure detection module is connected to the air duct channel of the blower 2, and the output end of the pressure detection module is connected to the first input end of the control board 1, which is used to detect the actual pressure in the air duct channel.

[0058] The control panel 1 is also used to control the blower 2 based on a preset pressure range, so as to adjust the air volume in the air duct of the blower 2 and make the actual pressure within the preset pressure range.

[0059] Different patients have different pressure tolerance ranges, and the pressure required to clear secretions during assisted coughing also varies. Therefore, this application includes a pressure detection module located at one end of the tracheal passage of the blower device 2. This module directly detects the airflow pressure during positive pressure inflation and negative pressure suction of the blower device 2 as the actual pressure. The actual pressure is then fed back to the control board 1. The control board 1 controls the blower device 2 based on the actual pressure and the preset pressure range. By increasing or decreasing the airflow of the blower device 2, it ensures that the actual pressure in the tracheal passage of the blower device 2 remains within the preset pressure range, thereby promoting the patient's sputum expectoration efficiency while ensuring patient safety.

[0060] In a preferred embodiment, the blower device 2 includes a blower and a breathing gas switching device;

[0061] The blower's air inlet is connected to the positive pressure air inlet of the breathing air switching device, the blower's air outlet is connected to the negative pressure air outlet of the breathing air switching device, and the blower's control terminal is connected to the third output terminal of the control board 1, which is used to adjust the air volume of the air inlet or air outlet based on the control of the control board 1.

[0062] The tracheal channel of the breathing gas switching device is connected to the first end of the external connection channel 3, and the control end of the breathing gas switching device is connected to the first output end of the control board 1. It is used to switch the positive pressure inflation port and the negative pressure suction port based on the control of the control board 1, so as to perform positive pressure inflation or negative pressure suction.

[0063] Controlling the blower device 2 based on a preset pressure range to adjust the airflow in the air duct of the blower device 2, so that the actual pressure is within the preset pressure range, includes:

[0064] The duty cycle of PWM (Pulse Width Modulation) is adjusted when controlling the blower based on the preset pressure range to regulate the air volume at the blower's inlet or outlet, so that the actual pressure is within the preset pressure range; the air volume is positively correlated with the PWM duty cycle, and the actual pressure is positively correlated with the air volume.

[0065] The blower device 2 in this embodiment specifically includes a blower and a breathing gas switching device. The blower is mainly used to provide airflow for the positive pressure inflation and negative pressure degassing of the blower device 2. The breathing gas switching device can switch between positive pressure inflation and negative pressure inflation. When the positive pressure inflation port of the breathing gas switching device is open, its negative pressure degassing port is closed, and the blower inflates the breathing mask with positive pressure through the positive pressure inflation port of the breathing gas switching device. When the negative pressure inflation port of the breathing gas switching device is open, its positive pressure degassing port is closed, and the blower degassing the breathing mask with negative pressure through the negative pressure inflation port of the breathing gas switching device.

[0066] Since the blower is actually a motor that provides airflow, when the control board 1 controls the blower, it actually controls it by outputting a corresponding PWM signal to the blower's drive device. The larger the PWM duty cycle of the PWM signal output by the control board 1, the higher the power of the blower and the greater the airflow it provides. The greater the airflow, the greater the actual pressure in the air duct channel. Based on this, the PWM duty cycle can be negatively fed back and adjusted by the actual pressure and the preset pressure range to ensure that the actual pressure is within the preset pressure range.

[0067] It should be noted that the breathing gas switching device may specifically include a positive pressure inflation channel, a negative pressure suction channel, and an endotracheal channel, as well as a positive pressure inflation coil and a negative pressure suction coil. One end of the positive pressure inflation channel is the positive pressure inflation port of the breathing gas switching device, and the other end is connected to the endotracheal channel. One end of the negative pressure suction channel is the negative pressure suction port of the breathing gas switching device, and the other end is also connected to the endotracheal channel. When positive pressure inflation to the patient's lungs is required, the control board 1 energizes the positive pressure inflation coil, causing the positive pressure inflation coil to engage the positive pressure inflation channel, thus establishing a connection between the positive pressure inflation channel and the endotracheal channel. When the interface is open, it ensures that the air output by the blower can flow to the breathing mask through the positive pressure inflation channel and the tracheal channel. At this time, the negative pressure suction coil is de-energized, and the connection between the negative pressure suction channel and the tracheal channel is disconnected. When the control board 1 needs to perform negative pressure suction to the patient's lungs, it energizes the negative pressure suction coil to make the negative pressure suction coil engage the negative pressure suction channel, thus opening the connection between the negative pressure suction channel and the tracheal channel. This ensures that the blower can perform negative pressure suction from the breathing mask through the negative pressure suction channel and the tracheal channel. At this time, the positive pressure inflation coil is de-energized, and the connection between the positive pressure inflation channel and the tracheal channel is disconnected.

[0068] As a preferred embodiment, adjusting the PWM duty cycle when controlling the blower based on a preset pressure range to regulate the airflow at the blower's inlet or outlet, so that the actual pressure is within the preset pressure range, includes:

[0069] When it is determined that the actual pressure is not within the preset pressure range and the airway is under-pressured, the PWM duty cycle for controlling the blower is increased by the first preset step.

[0070] After determining that the actual pressure rises to within the preset pressure range, the PWM duty cycle for controlling the blower is reduced by a second preset step.

[0071] During the negative feedback adjustment of the PWM duty cycle, if the actual pressure is low and has not reached the preset pressure range, the tracheal passage is in a state of underpressure, and the airflow pressure at the breathing mask is insufficient to remove secretions from the patient's airway. Based on this, the PWM duty cycle for controlling the blower is increased by the first preset step, thereby increasing the blower's airflow and thus increasing the actual pressure. If the actual pressure has not risen to the actual pressure range when the PWM duty cycle has reached the maximum duty cycle, the blower is controlled by maintaining the maximum PWM duty cycle. If the time for controlling the blower by maintaining the maximum PWM duty cycle exceeds the preset time threshold, the control board 1 will issue a pressure abnormality warning.

[0072] After the actual pressure rises to within the preset pressure range, in order to prevent the actual pressure from rising further beyond the preset pressure range and causing overpressure, this embodiment also reduces the PWM duty cycle by a second preset step. By dynamically adjusting the PWM duty cycle, the actual pressure is ensured to be within the preset pressure range, thereby improving the efficiency of assisted coughing for patients while ensuring patient safety.

[0073] It should be noted that the first preset step can increase the duty cycle by 1% for each PWM cycle, and the second preset step can decrease the duty cycle by 1% for each PWM cycle. This application does not limit this.

[0074] As a preferred embodiment, after determining that the actual pressure has risen to within a preset pressure range, and after reducing the PWM duty cycle of the blower control by a second preset step, the method further includes:

[0075] If it is determined that the actual pressure rises and the tracheal passage is in an overpressure state, then the PWM duty cycle is reduced to the minimum duty cycle.

[0076] In this embodiment, after the actual pressure rises to the preset pressure range, while the PWM duty cycle is reduced by the second preset step, the actual pressure continues to rise and rises to the highest pressure not lower than the preset pressure range. Then, the PWM duty cycle is immediately reduced to the lowest duty cycle, such as reducing the PWM duty cycle to 0, to avoid the actual pressure being too high and affecting the patient's safety.

[0077] As a preferred embodiment, before increasing the PWM duty cycle for controlling the blower by a first preset step when it is determined that the actual pressure is not within the preset pressure range and the airway is under-pressured, the method further includes:

[0078] The blower is started by controlling the preset initial PWM duty cycle.

[0079] In this embodiment, considering that the pressure detection module is directly installed at the air duct of the blower 2, the actual pressure detected by the pressure detection module is the pressure of the airflow directly output by the blower 2. If the blower is directly controlled by the PMW duty cycle corresponding to the preset pressure range in actual application, the pressure detection module may directly detect a large actual pressure, which may lead to overshoot of the pressure detection module and affect the subsequent negative feedback adjustment of the PMW duty cycle.

[0080] Based on this, in this application, when the blower is started, the blower is controlled to start with a preset initial PWM duty cycle, such as controlling the blower to start with a 50% PWM duty cycle, to ensure that the air volume and pressure are low when the blower starts, to avoid overshoot in the pressure detection module, to improve the accuracy of blower control, and to ensure that the actual pressure is within the preset pressure range.

[0081] In a preferred embodiment, the oscillation generating device 4 includes an oscillation generator and an amplitude generator;

[0082] The airway connection end of the oscillation generator is connected to the third end of the external connection channel 3, and the control end of the oscillation generator is connected to the first output end of the control board 1. It is used to open or close its own airway connection end according to the control of the control board 1 at the preset oscillation frequency in the preset oscillation command, so that the airflow at the breathing mask during positive pressure inflation and negative pressure degassing will oscillate.

[0083] The output end of the amplitude generator is connected to the airway connection end of the oscillation generator, and the control end of the amplitude generator is connected to the first output end of the control board 1. The control end of the amplitude generator is used to adjust the opening of the airway connection end of the oscillation generator based on the control of the control board 1, so that the opening of the airway connection end of the oscillation generator corresponds to the preset oscillation amplitude in the preset oscillation command.

[0084] The oscillation generating device 4 in this embodiment includes an oscillation generator and an amplitude generator. The amplitude generator is used to adjust the oscillation amplitude of the airflow at the breathing mask, while the oscillation generator is used to adjust the oscillation frequency of the airflow at the breathing mask. For example, if the three ports of the external connection channel 3 have the same diameter, and the preset oscillation amplitude is the maximum amplitude, then the opening of the airway connection end of the oscillation generator is the maximum opening. That is, the opening of the airway connection end of the oscillation generator is positively correlated with the preset oscillation amplitude. The oscillation generator ensures that the oscillation frequency of the airflow at the breathing mask is the preset oscillation frequency by controlling the opening and closing of its own airway connection end at the preset oscillation frequency.

[0085] Based on this, by coordinating the oscillation generator and the amplitude generator, it can be ensured that the oscillation frequency of the airflow at the breathing mask is a preset oscillation frequency and the oscillation amplitude is a preset oscillation amplitude. Of course, the preset oscillation frequency and preset oscillation amplitude can be set according to the patient's cough assistance needs, and this application does not limit this.

[0086] In a preferred embodiment, the oscillation generator includes a channel control module and an oscillation generation stepper motor;

[0087] The channel control module is connected to the third end of the peripheral connection channel 3. The control end of the channel control module is connected to the output end of the oscillation generation stepper motor. It is used to open or close the third end of the peripheral connection channel 3 based on the rotation of the oscillation generation stepper motor, so that the airflow at the breathing mask during positive pressure inflation and negative pressure de-inflation will oscillate.

[0088] The control terminal of the stepper motor that generates the oscillation is connected to the first output terminal of the control board 1, and is used to rotate according to the preset oscillation frequency based on the control of the control board 1.

[0089] The oscillation generator in this embodiment includes a channel control module and an oscillation generation stepper motor. The channel control module is connected to the third end of the peripheral connection channel 3. The channel control module operates as the oscillation generation stepper motor rotates. When the oscillation generation stepper motor rotates one revolution, the channel control module performs one opening and one closing of the peripheral connection channel 3. Therefore, the oscillation generation stepper motor can be controlled to rotate according to a preset oscillation frequency.

[0090] In a preferred embodiment, the amplitude generator includes a channel blocking module and an amplitude generating stepper motor;

[0091] The channel blocking module is connected to the third end of the peripheral connection channel 3. The control end of the channel blocking module is connected to the output end of the amplitude generating stepper motor, and is used to adjust the opening of the third end of the peripheral connection channel 3 based on the rotation of the amplitude generating stepper motor.

[0092] The control terminal of the amplitude generating stepper motor is connected to the first output terminal of the control board 1, and is used to rotate to an angle corresponding to the preset oscillation amplitude based on the control of the control board 1, so that the opening of the third terminal of the peripheral connection channel 3 corresponds to the preset oscillation amplitude.

[0093] The amplitude generator in this embodiment includes a channel blocking module and an amplitude generating stepper motor. The channel blocking module is also connected to the third end of the external connection channel 3. Each time the amplitude generating stepper motor rotates, the channel blocking module adjusts the opening of the third end of the external connection channel 3 from the minimum opening to the maximum opening. Therefore, after determining the corresponding opening based on the preset oscillation amplitude, the control board 1 controls the amplitude generating stepper motor to rotate to the angle corresponding to the preset oscillation amplitude, which ensures that the opening of the third end of the external connection channel 3 corresponds to the preset oscillation amplitude, thereby ensuring that the oscillation amplitude of the airflow at the breathing mask is the preset oscillation amplitude.

[0094] It should be noted that the difference between the channel control module and the channel blocking module is that when the preset oscillation amplitude is determined and remains unchanged, the channel blocking module also fixes the opening of the third end of the external connection channel 3 to the opening corresponding to the preset oscillation amplitude. During the process of keeping the preset oscillation amplitude unchanged, the amplitude generating stepper motor does not need to rotate, and the channel blocking module does not need to adjust the opening of the third end of the external connection channel 3. However, the oscillation generating stepper motor maintains a rotating state based on the preset oscillation frequency. Therefore, the channel control module also maintains a rotating state, thereby ensuring that the third end of the external connection channel 3 is in a cycle of opening and closing, so that the oscillation amplitude of the airflow at the breathing mask is the preset oscillation amplitude and the oscillation frequency is the preset oscillation frequency.

[0095] As a preferred embodiment, it also includes a respiratory detection module and / or a flow detection module;

[0096] The input end of the breathing detection module is connected to the breathing mask, and the output end of the breathing detection module is connected to the second input end of the control board 1. The breathing detection module is used to detect the airflow direction based on the breathing mask to determine the corresponding exhalation and inhalation states and feed them back to the control board 1 so that the control board 1 can control the positive pressure inflation and negative pressure degassing of the blower 2.

[0097] The input end of the flow detection module is connected to the air duct channel of the blower 2, and the output end of the flow detection module is connected to the third input end of the control board 1. The flow detection module is used to detect the air flow in the air duct channel and feed it back to the control board 1 so that the control board 1 can control the blower 2.

[0098] The non-invasive expectorant machine in this embodiment may further include a respiratory detection module and / or a flow detection module. The respiratory detection module can detect whether there is airflow at the breathing mask before the non-invasive expectorant machine is running, that is, whether there is airflow generated by the patient's spontaneous breathing. If airflow is detected and the airflow direction is determined, the corresponding expiratory and inspiratory states can be determined. If the airflow direction is from the breathing mask to the blower, it can be determined that the patient is currently in an expiratory state, and then the blower device 2 is controlled to perform negative pressure suction to match the patient's expiratory state. If the airflow direction is from the blower to the breathing mask, it can be determined that the patient is currently in an inspiratory state, and then the blower device 2 is controlled to perform positive pressure inflation to match the patient's inspiratory state.

[0099] The flow detection module can detect the air flow in the tracheal channel of the blower 2 when the non-invasive expectoration machine is running, and feed the air flow back to the control board 1. The control board 1 adjusts the air volume of the blower 2 according to the air flow to ensure the safety of the patient.

[0100] Specifically, such as Figure 2 As shown, Figure 2This application provides a schematic diagram of the specific structure of a non-invasive expectorant device. The non-invasive expectorant device may include a control board 1, a blower, a breathing gas switching device, an oscillation generator 4, a pulse oximeter finger clip, a pulse oximeter module, a display screen, a pressure detection module, a flow detection module, and a respiration detection module. Specifically, when the control board 1 controls the blower to positively pressurize, it simultaneously controls the positive pressure inlet of the breathing gas switching device to open and the negative pressure outlet to close. Specifically, it can control the positive pressure inlet coil to be energized and the negative pressure outlet coil to be de-energized, allowing the positive pressure gas output from the blower to flow into the breathing mask, causing the patient to inhale. When the blower is de-energized, the control board 1 controls the negative pressure outlet coil to be energized and the positive pressure inlet coil to be de-energized, causing the negative pressure outlet of the breathing gas switching device to open and the positive pressure inlet to close, allowing the gas in the patient's lungs to be drawn into the breathing mask by negative pressure and then flow to the outside through the blower, causing the patient to exhale. The oscillation generating device 4 includes an oscillation generator and an amplitude generator. The airflow generated by the blower through the breathing gas switching device branches through a three-way connector, namely the external connection channel 3 in this application. One end of the external connection channel 3 is connected to the air pipe channel of the blower 2, the other end is connected to the breathing mask for breathing gas, and the other end is connected to the oscillation generator to make the airflow oscillate. It should be noted that in order to extend the settable distance between the blower, the breathing mask and the oscillation generating device 4, a connecting pipe can be set between the air pipe channel of the blower 2 and the external connection channel 3, a connecting pipe can be set between the external connection channel 3 and the breathing mask, and a connecting pipe can be set between the external connection channel 3 and the oscillation generator. Of course, this application does not limit this. The oscillation generator generates airflow oscillation by periodically blocking the airway connection end of the oscillation generator, i.e., the third end of the external connection channel 3, according to the preset oscillation frequency in the preset oscillation command. The amplitude generator generates amplitude by adjusting the channel size of the airway connection end of the oscillation generator, i.e., the third end of the external connection channel 3. The combination of the oscillation generator and the amplitude generator can achieve oscillation requirements with different oscillation frequencies and amplitudes, meet the cough assistance needs of different patients, and thus quickly help patients loosen, move and clear secretions. The respiratory detection module detects whether the patient is breathing by detecting the airflow direction at the breathing mask, thereby realizing the automatic operation mode of the non-invasive expectorant machine. Specifically, the respiratory detection module feeds back the detected airflow direction data to the control board 1. When the control board 1 determines that the patient is wearing the breathing mask and is currently inhaling, it controls the blower 2 to perform positive pressure inflation to assist the patient in inhalation. Conversely, if it determines that the patient is currently in exhalation, it controls the blower 2 to perform negative pressure de-inhalation to assist the patient in exhalation. Of course, the automatic operation mode must be started after the preset pressure range and preset oscillation command have been set. It should be noted that the positive pressure inflation and negative pressure de-inhalation of the blower can also be switched by an additional manual switch, which is not limited in this application.

[0101] In addition, the power supply section includes mains power and a battery. The mains power includes a power cord (i.e., 220V power), a switch (specifically a rocker switch), a switching power supply, and a power board. The power board converts power to charge the battery and simultaneously power the control board 1 when the mains power is on. When the mains power is off, the power board converts the output energy from the battery to power the control board 1. It can also power the fan to cool the entire non-invasive coughing machine.

[0102] Control board 1 controls the power of the blower via a PWM control circuit, thereby controlling the blower's airflow. It also controls the blower's direction of rotation via a blower direction control line, thus controlling whether the blower is inflating or deflating. In this case, the blower itself can achieve positive pressure inflation and negative pressure deflating, reducing hardware costs. If the blower's rotation direction remains unchanged, a breathing gas switching device can be used to switch between positive pressure inflation and negative pressure deflating, simplifying the control logic of control board 1 and improving the switching efficiency. Since the blower uses two different air inlets for positive pressure inflation and negative pressure deflating, a breathing gas switching device is needed to switch the blower's gas direction. Figure 3 and Figure 4 As shown, Figure 3 This is a schematic diagram illustrating the positive pressure inflation of a blower device provided in this application. Figure 4 This is a schematic diagram of a blower device provided in this application performing negative pressure suction. When the positive pressure switching coil is energized, it generates a repulsive force, pushing the positive pressure piston, causing airflow from the blower to the inflation port and then to the breathing mask. Simultaneously, the negative pressure switching coil is de-energized, generating a suction force that engages the negative pressure piston. When the negative pressure switching coil is energized, it generates a repulsive force, pushing the negative pressure piston, causing airflow from the breathing mask to the blower's suction port. Simultaneously, the positive pressure switching coil is de-energized, generating a suction force that engages the positive pressure piston. A pulse oximeter clip can be clipped to the patient's fingertip. It detects the patient's blood oxygen and converts it into a digital or analog signal required by the control board 1, which is then transmitted to the control board 1. The control board 1 displays the patient's blood oxygen data in real time on a control display screen, including blood oxygen saturation and pulse rate, so that staff can monitor the patient's condition during sputum expectoration. In case of abnormal blood oxygen saturation or pulse rate, the blower is stopped, and an alarm is issued.

[0103] It should be noted that sealing gaskets are installed at both the air inlet and outlet of the blower to prevent air leakage; the breathing air switching module can use open molded parts to improve airtightness.

[0104] A flow detection module, such as a flow sensor, can also be connected to the airway of the blower 2 to detect the gas flow in real time, as well as the peak flow rate and tidal volume during the breathing process. The data is then transmitted to the control board 1 and displayed on the screen in real time. The breathing detection module can also be a breathing sensor. Specifically, four three-way valves can be installed between the airway channel of the blower 2 and the breathing mask. The first end of the first three-way valve is connected to the airway channel of the blower 2, the second end of the first three-way valve is connected to the input end of the flow detection module, the third end of the first three-way valve is connected to the first end of the second three-way valve, the second end of the second three-way valve is connected to the input end of the pressure detection module, the third end of the second three-way valve is connected to the first end of the third three-way valve, the second end of the third three-way valve is connected to the input end of the breathing detection module, the third end of the third three-way valve is connected to the first end of the fourth three-way valve, the fourth three-way valve is the external connection channel 3, the second end of the fourth three-way valve is connected to the airway connection end of the oscillation generator 4, and the third end of the fourth three-way valve is connected to the breathing mask. Of course, the flow detection module can bypass the three-way valves and directly surround the airway channel of the blower 2 to perform flow detection. The flow detection module and the pressure detection module can also be interchanged, and the breathing detection module and the oscillation generator 4 can also be interchanged. This application does not limit this. It should also be noted that the third end of the external connection channel 3 is connected to the outside through the oscillation generator 4. When the airway connection end of the oscillation generator 4 is open, the third end of the external connection channel 3 is directly connected to the outside. When the airway connection end of the oscillation generator 4 is closed, the third end of the external connection channel 3 is blocked. The third ends of the other three-way valves are blocked after passing through the corresponding detection modules.

[0105] The control board 1 can interact with the display screen and 4G module via serial port, and receive preset pressure range and preset oscillation commands set by the user through the display screen and / or 4G module.

[0106] During the control of the blower by the control board 1, the user can first set the corresponding parameters through the display screen, such as the preset pressure range, breathing time, pause time (the pause time between normal exhalation and inhalation), preset oscillation frequency, and preset oscillation amplitude. The above parameters are then sent to the control board 1. The control board 1 controls the blower and breathing switching device according to the manual switch command or the detection result of the breathing detection module. For example, it first controls the blower and breathing switching device to perform positive pressure inflation. When the positive pressure inflation time reaches the inhalation time in the breathing, it enters a pause state, and the pause state is maintained for the pause time. After the pause time ends, the control board 1 controls the blower and breathing switching device to perform negative pressure suction. When the negative pressure suction time reaches the exhalation time in the breathing, it enters a pause state again. This cycle is repeated for multiple cycles of breathing. During each positive and negative pressure inflation process of the blower, the control board 1 also controls the oscillation generator 4 to oscillate the airflow according to the preset oscillation frequency and preset oscillation amplitude in the preset oscillation command.

[0107] Let's take the positive pressure inflation control process as an example to illustrate:

[0108] When the control panel 1 controls the blower device 2 to perform positive pressure inflation, it first controls the positive pressure switching coil of the blower to be energized so that the blower generates positive pressure gas. Then, it controls the positive pressure switching coil in the breathing gas switching device to be energized, and the positive pressure inflation port in the breathing gas switching device opens. The positive pressure gas generated by the blower flows to the breathing mask through the airway channel of the breathing gas switching device.

[0109] When controlling the blower, control board 1 specifically generates a PWM signal to control the blower. By changing the PWM duty cycle of the PWM signal, the power of the blower can be changed, thereby changing the air volume. Since the pressure detection module is soldered onto the circuit board, after the blower outputs air, the pressure detection module will detect the pressure in the air pipe. In order to prevent the airflow generated by the blower from passing through the pressure detection module first and causing overshoot, an initial PWM duty cycle is preset to control the blower when it starts, thereby reducing the air volume generated when the blower starts to inflate. For example, a 50% duty cycle can be selected as the preset initial PWM duty cycle for control. During the positive pressure inflation process of the blower, the pressure detection module detects the actual pressure in real time and transmits it to control board 1 in real time.

[0110] Since the pressure range of the standard is -7kPa to 7kPa, the range of the pressure detection module can be selected from -40kPa to 40kPa. This application does not limit this range. The voltage range corresponding to the pressure of -40kPa to 40kPa is 0.2V to 2.7V. When the blower is performing positive pressure inflation, the voltage output range of the pressure detection module after detecting the actual pressure is 1.45V to 2.7V. At this time, the slope of the actual pressure change is (2.7-1.45) / 40=0.03125. The pressure detection module can be calculated according to the formula Y=K×(dKpa)+b, where dKpa is the actual pressure, Y is the voltage corresponding to the actual pressure output by the pressure detection module, K is the slope of change, and b is 1.45. Control board 1 actually acquires the voltage value output by the pressure detection module through the voltage acquisition module to obtain the voltage corresponding to the actual pressure. Then, the actual pressure can be calculated in reverse using the following formula: dKpa=(((3.3×1.0) / 4096)×g_GetPressAINVal-1.45) / 0.03125; where 3.3 is the power supply voltage of control board 1, and g_GetPressAINVal is the voltage value acquired by control board 1 from the pressure detection module. The analog value corresponding to the voltage Y is multiplied by 1.0 to ensure floating-point arithmetic and avoid integer division problems caused by data types in programming; 4096 is the resolution of the voltage acquisition module, and (3.3×1.0 / 4096)×g_GetPressAINVal means restoring the analog value to the voltage value output by the pressure detection module, which is Y; -1.45 represents the voltage difference obtained by subtracting the zero-point offset voltage from the voltage value calculated above, which is the output voltage when the pressure is 0; 0.03125 is the slope.

[0111] During positive pressure inflation, the PWM duty cycle is adjusted in real time according to the actual pressure. A preset pressure range is set with the first target pressure as the center. The lowest pressure in the preset pressure range is the first target pressure minus the floating pressure, and the highest pressure is the first target pressure plus the floating pressure. The floating pressure can be, but is not limited to, 1 kPa. When the actual pressure is less than the lowest pressure, that is, less than the first target pressure - 1 kPa, the airway is in an under-pressure state. The PWM duty cycle is then gradually increased in the first preset step until it reaches its maximum. When the PWM duty cycle reaches 1, the blower performs full-power positive pressure inflation. This ensures rapid inflation and meets the requirements for high-flow-rate air intake. Of course, it is not necessary to increase the PWM duty cycle to the maximum duty cycle every time there is an under-pressure state. It is sufficient to ensure that the actual pressure is not lower than the minimum pressure. When the actual pressure is not lower than the first target pressure - 1 kPa, it can be determined that the actual pressure has entered the preset pressure range. At this time, in order to prevent the actual pressure from rising further beyond the preset pressure range, the control board 1 can gradually reduce the PWM duty cycle in the second preset step. However, if the actual pressure rises to not lower than the highest pressure, that is, the first target pressure + 1 kPa, the airway is in an overpressure state. At this time, the PWM duty cycle can be directly reduced to the lowest duty cycle, such as reducing it to 0 so that the blower stops positive pressure inflation. Until the actual pressure is lower than the first target pressure - 1 kPa again, the PWM duty cycle can be increased again in the first preset step, or the PWM duty cycle can be directly set to the preset initial duty cycle, or the PWM duty cycle can be directly set to the target PWM duty cycle corresponding to the first target pressure. This application does not limit this, as long as the blower continues positive pressure inflation, so that the actual pressure is within the preset pressure range until the inhalation time ends.

[0112] The control process for negative pressure air extraction can refer to the control process for positive pressure air inflation described above, but the differences are explained below:

[0113] When the control panel 1 controls the blower device 2 to perform negative pressure suction, it first controls the negative coil of the blower to be energized so that the blower generates positive pressure gas. Then, it controls the negative pressure switching coil in the breathing gas switching device to be energized, and the negative pressure inflation port in the breathing gas switching device opens, allowing air from the breathing mask or other air passages in the patient's lungs through the breathing gas switching device to flow to the blower.

[0114] When the blower operates under negative pressure, the voltage output range of the pressure detection module after detecting the actual pressure is 0.2V-1.45V. After the control board 1 obtains the analog voltage of the actual pressure output by the pressure detection module, it can calculate the corresponding actual pressure in reverse according to the following formula: dKpa=(1.45-((3.3×1.0) / 4096)×g_GetPressAINVal) / 0.03125; where 1.45-(3.3×1.0 / 4096)×g_GetPressAINVal represents the voltage difference. Based on this, the actual pressure can be calculated.

[0115] Because the airflow direction is different during negative pressure pumping and positive pressure inflation, the actual pressure direction is also different. Therefore, the second target pressure during negative pressure pumping is different from the first target pressure. Taking the first target pressure as positive as an example, the second target pressure is negative. Therefore, the signs of the second target pressure, as well as the minimum and maximum pressures, are negative. However, the negative sign only indicates the direction, not the magnitude. Based on this, during negative pressure suction, the PWM duty cycle is adjusted in real time according to the actual pressure. A preset pressure range is set with the second target pressure as the center. The lowest pressure in the preset pressure range during negative pressure suction is the second target pressure plus the floating pressure, and the highest pressure is the second target pressure minus the floating pressure. The floating pressure can be, but is not limited to, 1 kPa. When the actual pressure is lower than the lowest pressure, that is, when the actual pressure with a negative sign is greater than the second target pressure + 1 kPa, the airway is in an under-pressure state. The PWM duty cycle is then gradually increased in the first preset step until the PWM duty cycle reaches its maximum. For example, when the PWM duty cycle reaches 1, the blower performs full-power negative pressure suction. This ensures rapid suction and meets the requirements for high-flow exhalation. Of course, it is not necessary to increase the PWM duty cycle to the maximum duty cycle every time there is under-pressure; it is sufficient to ensure that the actual pressure is not lower than the lowest pressure. When the actual pressure value with a negative sign is not lower than the second target pressure + 1 kPa, it can be determined that the actual pressure has entered the preset pressure range. At this time, in order to prevent the actual pressure from rising further beyond the preset pressure range, the control board 1 can gradually reduce the PWM duty cycle with a second preset step. However, if the actual pressure rises beyond the preset pressure range, that is, when the actual pressure value with a negative sign is less than the second target pressure - 1 kPa, the tracheal passage is in an overpressure state. At this time, the PWM duty cycle can be directly reduced to the minimum duty cycle, such as reducing it to 0 so that the blower stops negative pressure air extraction, until the actual pressure drops again to enter the preset pressure range. Then, the PWM duty cycle can be increased again with the first preset step, or the PWM duty cycle can be directly set to the preset initial duty cycle, or the PWM duty cycle can be directly set to the target PWM duty cycle corresponding to the target pressure. This application does not limit this, as long as the blower continues negative pressure air extraction, so that the actual pressure is within the preset pressure range until the exhalation time ends.

[0116] Please refer to Figure 5 , Figure 5 This is a flowchart illustrating the control board used in this application to control a blower. It should be noted that the control board 1 can select a preset pressure range corresponding to the first target pressure based on positive pressure inflation (inhalation) or negative pressure deflating (exhalation) commands received from a manual switch or display screen. Alternatively, it can select a preset pressure range corresponding to the first target pressure based on the exhalation or inhalation state detected by the breathing detection module.

[0117] During the process of the control board 1 controlling the oscillation generator 4, the oscillation generator includes a channel control module and an oscillation stepper motor. The control board 1 controls the oscillation stepper motor by generating oscillation control pulses. For example, for each oscillation control pulse output by the control board 1, the oscillation stepper motor rotates 0.9°. Therefore, it takes 400 oscillation control pulses for the oscillation stepper motor to rotate one revolution. The preset oscillation frequency range is set to 1Hz-25Hz, and the corresponding oscillation period is 0.04s-1s. Therefore, when the oscillation stepper motor rotates one revolution, the oscillation control pulses generated by the control board 1 per second are: preset oscillation frequency × 400. When the user starts up, he will set the preset oscillation frequency on the display screen. The control board 1 calculates the corresponding number of oscillation control pulses output per second according to the preset oscillation frequency to control the oscillation stepper motor. The channel control module can be implemented through a bearing. The bearing rotates with the stepper motor that generates the oscillation. When the bearing rotates, it can open or close the third end of the peripheral connection channel 3. Each time the third end of the peripheral connection channel 3 is opened or closed, the airflow will vibrate once. When the stepper motor rotates 400 times per second at the preset oscillation frequency, the oscillation frequency of the airflow is the preset oscillation frequency.

[0118] The amplitude generator includes a channel blocking module and an amplitude generating stepper motor. The channel blocking module blocks the air pipe at the third end of the external connection channel 3. The degree of blocking, i.e., the opening degree of the third end of the external connection channel 3, corresponds to the preset oscillation amplitude. For example, the pressure range of the blower during positive pressure inflation is 0 to 70 cmH2O (0 to 7 kPa), and the pressure range during negative pressure extraction is -70 to 0 cmH2O (-7 to 0 kPa). If the first target pressure is 20 cmH2O to 70 cmH2O and the second target pressure is -70 cmH2O to -20 cmH2O, the preset oscillation amplitude range can be 1-10 cmH2O. Conversely, if the first target pressure is 0 cmH2O to 10 cmH2O and the second target pressure is -70 cmH2O to -20 cmH2O, the preset oscillation amplitude range can be 1-10 cmH2O. cmH20, the preset oscillation amplitude range can be 1-5cmH20, that is, the preset oscillation amplitude is only half of the first target pressure or the second target pressure in the preset pressure range. If the diameter of each three-way valve or each port of the external connection channel 3 is the same, then when the amplitude generating stepper motor rotates from 0 to 90 degrees, the air tube opening at the third end of the external connection channel 3 is from 0 to 100; then for every 1 degree the amplitude generating stepper motor rotates, the air tube opening at the third end of the external connection channel 3 is 10 / 9.

[0119] Taking a first target pressure of 70cmH2O and a second target pressure of -70cmH2O as an example, TPress is the first target pressure, and TPress / 2 is the total opening and closing amplitude of the branch, which is also the total opening and closing amplitude of the third end of the peripheral connection channel 3. The maximum opening is 100, and the pressure value corresponding to each opening is TPress / 2 / 100. The pressure value corresponding to each degree of rotation of the amplitude generating stepper motor is (TPress / 2 / 100)×(10 / 9). The angle that the amplitude generating stepper motor should rotate for the preset oscillation amplitude OscillationAmplitude is Angle=OscillationAmplitude / ((TPress / 2 / 100)×(10 / 9)). For each amplitude control pulse output by the control board 1, the amplitude generating stepper motor rotates 0.9°. In order to achieve the preset vibration amplitude, the number of amplitude control pulses required is Angle / 0.9.

[0120] It should be noted that during the breathing process, the control board 1 first controls the blower to switch between positive pressure inflation and negative pressure depressurization. After the pressure stabilizes within the preset pressure range, it then controls the oscillation generator 4 to make the airflow oscillate with a corresponding preset frequency and preset amplitude.

[0121] It should also be noted that, in this specification, relational terms such as "first" and "second" are used only to distinguish one entity or operation from another, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Furthermore, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, method, article, or apparatus. Unless otherwise specified, an element defined by the phrase "comprising one..." does not exclude the presence of other identical elements in the process, method, article, or apparatus that includes the element.

[0122] The above description of the disclosed embodiments enables those skilled in the art to make or use the invention. Various modifications to these embodiments will be readily apparent to those skilled in the art, and the general principles defined herein may be implemented in other embodiments without departing from the spirit or scope of the invention. Therefore, the invention is not to be limited to the embodiments shown herein, but is to be accorded the widest scope consistent with the principles and novel features disclosed herein.

Claims

1. A non-invasive expectorant machine, characterized in that, include: The control board has a first output terminal connected to the control terminal of the blower and a second output terminal connected to the control terminal of the oscillation generator. The control board is used to control the blower to perform positive pressure inflation or negative pressure degassing, and to control the oscillation generator based on a preset oscillation command. The blower device has its air duct channel connected to the first end of the external connection channel. The blower device is used to perform positive pressure inflation or negative pressure degassing through a breathing mask. The external connection channel has a second end connected to the breathing mask and a third end connected to the airway connection end of the oscillation generator. The oscillation generating device is used to open or close its airway connection terminal based on the preset oscillation command under the control of the control board, so as to cause the airflow at the breathing mask to oscillate during positive pressure inflation and negative pressure degassing.

2. The non-invasive expectorant machine as described in claim 1, characterized in that, It also includes a pressure detection module; The input end of the pressure detection module is connected to the air duct channel of the blower, and the output end of the pressure detection module is connected to the first input end of the control board, for detecting the actual pressure in the air duct channel; The control panel is also used to control the blower based on a preset pressure range, so as to adjust the air volume in the air duct of the blower and make the actual pressure within the preset pressure range.

3. The non-invasive expectorant machine as described in claim 2, characterized in that, The blowing device includes a blower and a breathing gas switching device; The air inlet of the blower is connected to the positive pressure air inlet of the breathing air switching device, the air outlet of the blower is connected to the negative pressure air outlet of the breathing air switching device, and the control terminal of the blower is connected to the third output terminal of the control board for adjusting the air volume of the air inlet or the air outlet based on the control of the control board. The tracheal channel of the breathing gas switching device is connected to the first end of the external connection channel, and the control end of the breathing gas switching device is connected to the first output end of the control board. It is used to switch the positive pressure inflation port and the negative pressure suction port based on the control of the control board, so as to perform positive pressure inflation or negative pressure suction. Controlling the blower based on a preset pressure range to adjust the airflow in the blower's air duct channel, so that the actual pressure is within the preset pressure range, includes: The PWM duty cycle is adjusted when controlling the blower based on the preset pressure range to regulate the air volume at the blower's inlet or outlet, so that the actual pressure is within the preset pressure range; the air volume is positively correlated with the PWM duty cycle, and the actual pressure is positively correlated with the air volume.

4. The non-invasive expectorant machine as described in claim 3, characterized in that, Adjusting the PWM duty cycle when controlling the blower based on the preset pressure range to regulate the air volume at the blower's inlet or outlet, so that the actual pressure is within the preset pressure range, includes: When it is determined that the actual pressure is not within the preset pressure range and the airway is in an under-pressure state, the PWM duty cycle when controlling the blower is increased by a first preset step. After determining that the actual pressure rises to enter the preset pressure range, the PWM duty cycle when controlling the blower is reduced by a second preset step.

5. The non-invasive expectorant machine as described in claim 4, characterized in that, After determining that the actual pressure has risen to within the preset pressure range, and after reducing the PWM duty cycle of the blower control by a second preset step, the method further includes: If it is determined that the actual pressure has increased and the airway is in an overpressure state, then the PWM duty cycle is reduced to the minimum duty cycle.

6. The non-invasive expectorant machine as described in claim 4, characterized in that, When it is determined that the actual pressure is not within the preset pressure range and the airway is in an under-pressure state, before increasing the PWM duty cycle when controlling the blower by a first preset step, the method further includes: The blower is started by controlling the preset initial PWM duty cycle.

7. The non-invasive expectorant machine as described in claim 1, characterized in that, The oscillation generating device includes an oscillation generator and an amplitude generator; The airway connection end of the oscillation generator is connected to the third end of the external connection channel, and the control end of the oscillation generator is connected to the first output end of the control board. It is used to open or close its airway connection end at a preset oscillation frequency in the preset oscillation command based on the control of the control board, so that the airflow at the breathing mask during positive pressure inflation and negative pressure degassing will oscillate. The output terminal of the amplitude generator is connected to the airway connection terminal of the oscillation generator, and the control terminal of the amplitude generator is connected to the first output terminal of the control board. The control terminal is used to adjust the opening of the airway connection terminal of the oscillation generator based on the control of the control board, so that the opening of the airway connection terminal of the oscillation generator corresponds to the preset oscillation amplitude in the preset oscillation command.

8. The non-invasive expectorant machine as described in claim 7, characterized in that, The oscillation generator includes a channel control module and an oscillation generation stepper motor; The channel control module is connected to the third end of the peripheral connection channel, and the control end of the channel control module is connected to the output end of the oscillation generation stepper motor. It is used to open or close the third end of the peripheral connection channel based on the rotation of the oscillation generation stepper motor, so that the airflow at the breathing mask during positive pressure inflation and negative pressure degassing will oscillate. The control terminal of the stepper motor that generates the oscillation is connected to the first output terminal of the control board, and is used to rotate according to the preset oscillation frequency based on the control of the control board.

9. The non-invasive expectorant machine as described in claim 7, characterized in that, The amplitude generator includes a channel blocking module and an amplitude generating stepper motor; The channel blocking module is connected to the third end of the peripheral connection channel, and the control end of the channel blocking module is connected to the output end of the amplitude generating stepper motor, for adjusting the opening degree of the third end of the peripheral connection channel based on the rotation of the amplitude generating stepper motor; The control terminal of the amplitude generating stepper motor is connected to the first output terminal of the control board, and is used to rotate to an angle corresponding to the preset oscillation amplitude based on the control of the control board, so that the opening of the third terminal of the peripheral connection channel corresponds to the preset oscillation amplitude.

10. The non-invasive expectorant machine according to any one of claims 1-9, characterized in that, It also includes a respiratory detection module and / or a flow detection module; The input terminal of the breathing detection module is connected to the breathing mask, and the output terminal of the breathing detection module is connected to the second input terminal of the control board. The breathing detection module is used to detect the airflow direction of the breathing mask to determine the corresponding exhalation and inhalation states and feed them back to the control board so that the control board can control the positive pressure inflation and negative pressure degassing of the blower. The input terminal of the flow detection module is connected to the air duct channel of the blower, and the output terminal of the flow detection module is connected to the third input terminal of the control board. The flow detection module is used to detect the air flow in the air duct channel and feed it back to the control board so that the control board can control the blower.

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