Method, apparatus, device, medium and product for controlling oscillating air flow

Abstract

Embodiments of the present application provide a method, device, equipment, medium and product for controlling oscillating airflow. The method comprises: obtaining a current oscillation cycle signal of oscillating airflow generated by a sputum discharge device, and obtaining positive and negative half cycle peak values and positive and negative half cycle areas of the current oscillation cycle signal; judging a current human body inhale and exhale state; adjusting positive and negative half cycle pressure and positive and negative half cycle time of a next oscillation cycle signal of the oscillating airflow according to the positive and negative half cycle peak values and the positive and negative half cycle areas, so that a ratio of an absolute value of a negative half cycle peak value to an absolute value of a positive half cycle peak value of the next oscillation cycle signal of the inhalation phase is greater than a first value, and an absolute value of the positive half cycle area is not less than an absolute value of the negative half cycle area; a ratio of an absolute value of a negative half cycle peak value to an absolute value of a positive half cycle peak value of the next oscillation cycle signal of the exhalation phase is greater than a second value, and an absolute value of the positive half cycle area is not greater than an absolute value of the negative half cycle area. The scheme of the present application improves the effectiveness of airway secretion discharge.

Description

Technical Field

[0001] This application relates to the field of respiratory therapy equipment technology, and in particular to a method, device, equipment, medium and product for controlling oscillating airflow. Background Technology

[0002] Airway clearance techniques use mechanical methods to loosen and liquefy airway secretions, moving them from the peripheral small airways to the central main airway, maintaining airway patency, and reducing the risk of complications caused by secretions. One type of airway clearance technique involves using an airflow system generated by a sputum expectoration device to assist in the removal of airway secretions.

[0003] Current methods for assisting airway secretion removal using oscillating airflow generate a constant oscillating airflow. This causes airway secretions to move deeper into the airways, and the energy of the oscillating waves transmitted to the distal small airways is limited, resulting in poor effectiveness of airway secretion removal. Summary of the Invention

[0004] The oscillating airflow control method, apparatus, equipment, medium, and product provided in this application are used to asymmetrically adjust the periodic oscillation signal of the oscillating airflow in the inspiratory and expiratory phases, respectively, thereby improving the effectiveness of the oscillating airflow in assisting the expulsion of airway secretions.

[0005] In a first aspect, embodiments of this application provide a method, including:

[0006] Acquire the current oscillation period signal of the oscillating airflow generated by the sputum suction device;

[0007] Based on the current oscillation period signal, calculations are performed to obtain the peak values ​​and areas of the positive and negative half-cycles of the current oscillation period signal.

[0008] Determine the current state of human breathing; the state of human breathing includes the inspiratory phase and the expiratory phase;

[0009] Based on the positive and negative half-cycle peak values ​​and the positive and negative half-cycle areas, the positive and negative half-cycle pressures and times of the next oscillation cycle signal of the oscillating airflow are adjusted so that the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value of the next oscillation cycle signal of the inspiratory phase is greater than a first value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal of the inspiratory phase is not less than the absolute value of the negative half-cycle area; the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value of the next oscillation cycle signal of the expiratory phase is greater than a second value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal of the expiratory phase is not greater than the absolute value of the negative half-cycle area; the second value is greater than the first value.

[0010] In one possible implementation, adjusting the positive and negative half-cycle pressure and positive and negative half-cycle time of the next oscillation cycle signal of the oscillating airflow based on the positive and negative half-cycle peak values ​​and the positive and negative half-cycle areas includes:

[0011] Based on the positive and negative half-cycle peak values, adjust the positive and negative half-cycle pressures of the next oscillation cycle signal of the oscillating airflow to obtain the positive and negative half-cycle peak values ​​of the next oscillation cycle signal of the oscillating airflow after pressure adjustment.

[0012] Based on the positive and negative half-cycle areas and the positive and negative half-cycle peak values ​​of the next oscillation cycle signal of the oscillating airflow after pressure adjustment, the positive and negative half-cycle times of the next oscillation cycle signal of the oscillating airflow are adjusted to obtain the positive and negative half-cycle areas of the next oscillation cycle signal of the oscillating airflow after time adjustment.

[0013] In one possible implementation, the step of calculating the peak values ​​and areas of the positive and negative half-cycles of the current oscillation period signal based on the current oscillation period signal includes:

[0014] The current oscillation period signal is extracted to obtain the positive half-cycle peak value, negative half-cycle peak value, positive half-cycle time, and negative half-cycle time.

[0015] The area of ​​the positive half-cycle is calculated based on the positive half-cycle peak value and the positive half-cycle time.

[0016] The negative half-cycle area is calculated based on the negative half-cycle peak value and the negative half-cycle time.

[0017] In one possible implementation, the method further includes:

[0018] If the current human body is in the expiratory phase and the current expiratory phase is not the first expiratory phase, then obtain the expiratory time of the previous expiratory phase;

[0019] Based on the exhalation time and a preset frequency scanning range, and using a frequency sweep function model, the oscillation frequency of each oscillation cycle signal of the current exhalation phase is adjusted so that the oscillation frequency of the current exhalation phase varies within the frequency scanning range during the exhalation time; the frequency sweep function characterizes the relationship between time and the oscillation frequency of the oscillation cycle signal.

[0020] In one possible implementation, adjusting the oscillation frequency of each oscillation cycle signal of the expiratory phase based on the expiratory time and a preset frequency scanning range, using a frequency sweep function model, includes:

[0021] If the sputum expectoration device does not have a disease type set, then based on the expiratory time and a preset frequency scanning range, the oscillation frequency of each oscillation cycle signal of the expiratory phase is adjusted according to a linear function model.

[0022] If the sputum expectoration device is configured with disease types, then based on the expiratory time and a preset frequency scanning range, the oscillation frequency of each oscillation cycle signal of the expiratory phase is adjusted according to a nonlinear exponential function model.

[0023] In one possible implementation, obtaining the expiratory time of the previous expiratory phase includes:

[0024] Obtain the positive and negative half-cycle times of each oscillation cycle within the previous expiratory phase;

[0025] The sum of the positive and negative half-cycle times of each oscillation cycle within the previous expiratory phase is calculated to obtain the expiratory time of the previous expiratory phase.

[0026] In one possible implementation, the method further includes:

[0027] If the current human body's inhalation and exhalation state is the inhalation phase, then based on the current oscillation cycle signal, signal extraction is performed to obtain the oscillation frequency of the current oscillation cycle signal of the inhalation phase;

[0028] The oscillation frequency of the current oscillation cycle signal of the intake phase is reduced so that the oscillation frequency of each oscillation cycle signal of the subsequent intake phase is lower than the oscillation frequency of the current oscillation cycle signal.

[0029] In one possible implementation, the method further includes: determining the current human breathing state, including:

[0030] Acquire a first gas signal; the first gas signal includes an oscillating airflow signal superimposed with the gas signal of the current human respiration;

[0031] The first gas signal is filtered to obtain the current flow rate of the human body's breathing gas;

[0032] If the current human body's respiratory gas flow rate is greater than a preset threshold, then the current human body's inhalation and exhalation state is determined to be the inspiratory phase.

[0033] If the current flow rate of the human body's breathing gas is not greater than the preset threshold, then the current human body's inhalation and exhalation state is determined to be the expiratory phase.

[0034] Secondly, embodiments of this application provide a control device for oscillating airflow, comprising:

[0035] The acquisition module is used to acquire the current oscillation period signal of the oscillating airflow generated by the sputum suction device;

[0036] The calculation module is used to perform calculations based on the current oscillation period signal to obtain the peak values ​​and areas of the positive and negative half-cycles of the current oscillation period signal.

[0037] The judgment module is used to determine the current human breathing state; the human breathing state includes the inhalation phase and the exhalation phase;

[0038] The adjustment module is used to adjust the positive and negative half-cycle pressure and positive and negative half-cycle time of the next oscillation cycle signal of the oscillating airflow according to the positive and negative half-cycle peak values ​​and the positive and negative half-cycle areas, so that the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value of the next oscillation cycle signal of the inspiratory phase is greater than a first value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal of the inspiratory phase is not less than the absolute value of the negative half-cycle area; the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value of the next oscillation cycle signal of the expiratory phase is greater than a second value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal of the expiratory phase is not greater than the absolute value of the negative half-cycle area; the second value is greater than the first value.

[0039] In one possible implementation, the adjustment module is specifically used for:

[0040] Based on the positive and negative half-cycle peak values, adjust the positive and negative half-cycle pressures of the next oscillation cycle signal of the oscillating airflow to obtain the positive and negative half-cycle peak values ​​of the next oscillation cycle signal of the oscillating airflow after pressure adjustment.

[0041] Based on the positive and negative half-cycle areas and the positive and negative half-cycle peak values ​​of the next oscillation cycle signal of the oscillating airflow after pressure adjustment, the positive and negative half-cycle times of the next oscillation cycle signal of the oscillating airflow are adjusted to obtain the positive and negative half-cycle areas of the next oscillation cycle signal of the oscillating airflow after time adjustment.

[0042] In one possible implementation, the computing module is specifically used for:

[0043] The current oscillation period signal is extracted to obtain the positive half-cycle peak value, negative half-cycle peak value, positive half-cycle time, and negative half-cycle time.

[0044] The area of ​​the positive half-cycle is calculated based on the positive half-cycle peak value and the positive half-cycle time.

[0045] The negative half-cycle area is calculated based on the negative half-cycle peak value and the negative half-cycle time.

[0046] In one possible implementation, the adjustment module is further configured to:

[0047] If the current human body is in the expiratory phase and the current expiratory phase is not the first expiratory phase, then obtain the expiratory time of the previous expiratory phase;

[0048] Based on the exhalation time and a preset frequency scanning range, and using a frequency sweep function model, the oscillation frequency of each oscillation cycle signal of the current exhalation phase is adjusted so that the oscillation frequency of the current exhalation phase varies within the frequency scanning range during the exhalation time; the frequency sweep function characterizes the relationship between time and the oscillation frequency of the oscillation cycle signal.

[0049] In one possible implementation, the adjustment module is specifically used for:

[0050] If the sputum expectoration device does not have a disease type set, then based on the expiratory time and a preset frequency scanning range, the oscillation frequency of each oscillation cycle signal of the expiratory phase is adjusted according to a linear function model.

[0051] If the sputum expectoration device is configured with disease types, then based on the expiratory time and a preset frequency scanning range, the oscillation frequency of each oscillation cycle signal of the expiratory phase is adjusted according to a nonlinear exponential function model.

[0052] In one possible implementation, the adjustment module is specifically used for:

[0053] Obtain the positive and negative half-cycle times of each oscillation cycle within the previous expiratory phase;

[0054] The sum of the positive and negative half-cycle times of each oscillation cycle within the previous expiratory phase is calculated to obtain the expiratory time of the previous expiratory phase.

[0055] In one possible implementation, the adjustment module is further configured to:

[0056] If the current human body's inhalation and exhalation state is the inhalation phase, then based on the current oscillation cycle signal, signal extraction is performed to obtain the oscillation frequency of the current oscillation cycle signal of the inhalation phase;

[0057] The oscillation frequency of the current oscillation cycle signal of the intake phase is reduced so that the oscillation frequency of each oscillation cycle signal of the subsequent intake phase is lower than the oscillation frequency of the current oscillation cycle signal.

[0058] In one possible implementation, the determining module is specifically used for:

[0059] Acquire a first gas signal; the first gas signal includes an oscillating airflow signal superimposed with the gas signal of the current human respiration;

[0060] The first gas signal is filtered to obtain the current flow rate of the human body's breathing gas;

[0061] If the current human body's respiratory gas flow rate is greater than a preset threshold, then the current human body's inhalation and exhalation state is determined to be the inspiratory phase.

[0062] If the current flow rate of the human body's breathing gas is not greater than the preset threshold, then the current human body's inhalation and exhalation state is determined to be the expiratory phase.

[0063] Thirdly, embodiments of this application provide an electronic device, including: a memory and a processor;

[0064] The memory stores computer-executed instructions;

[0065] The processor executes computer execution instructions stored in the memory, causing the processor to perform the first aspect and / or various possible implementations of the first aspect as described above.

[0066] Fourthly, embodiments of this application provide a computer-readable storage medium storing computer-executable instructions, which, when executed by a processor, are used to implement the first aspect and / or various possible implementations of the first aspect.

[0067] Fifthly, embodiments of this application provide a computer program product, including a computer program that, when executed by a processor, implements the first aspect and / or various possible implementations of the first aspect.

[0068] The oscillating airflow control method, apparatus, device, medium, and product provided in this application adjust the positive and negative half-cycle pressure and time of the next oscillating cycle signal of the oscillating airflow based on the peak values ​​and areas of the upper and lower half-cycles of the current oscillating signal during the inspiratory phase. This ensures that the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak of the next oscillating cycle signal is greater than a first value, and the absolute value of the positive half-cycle area of ​​the next oscillating cycle signal during the inspiratory phase is not less than the absolute value of the negative half-cycle area. During the expiratory phase, the oscillating airflow is adjusted based on the peak values ​​and areas of the upper and lower half-cycles of the current oscillating signal during the oscillating phase. The positive and negative half-cycle pressure and time of the signal are adjusted so that the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak of the next oscillation cycle signal is greater than the second value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal in the expiratory phase is not greater than the absolute value of the negative half-cycle area. Among them, the positive half-cycle area represents the volume of gas delivered to the human body by the sputum-clearing device during the inspiratory phase, the negative half-cycle area represents the volume of gas assisted by the sputum-clearing device to be expelled by the human body during the expiratory phase, the positive half-cycle peak value represents the gas flow rate delivered to the human body by the sputum-clearing device during the inspiratory phase, and the negative half-cycle peak value represents the gas flow rate assisted by the sputum-clearing device to be expelled by the human body during the expiratory phase, and the second value is greater than the first value. Therefore, during the inhalation phase, the flow rate of gas delivered to the body by the sputum-clearing device is less than the flow rate of gas assisted in being expelled by the device, and the ratio between the two is greater than the first value; the volume of gas delivered to the body by the sputum-clearing device during the inhalation phase is greater than or equal to the volume of gas assisted in being expelled by the device. This ensures that during the inhalation phase, the volume of gas entering the body is greater than the volume of gas being expelled, avoiding the generation of outward gas during the inhalation phase, which could cause discomfort to the body; at the same time, the peak flow rate of the expelled gas is greater than the peak flow rate of the gas entering the body, so that the oscillating airflow can assist in expelling airway secretions from the body. During the expiratory phase, the flow rate of gas delivered to the body by the sputum-clearing device is less than the flow rate of gas assisted in being expelled by the device, and the ratio between the two is greater than the second value; the second value is greater than the first value. In other words, during the expiratory phase, the degree to which the flow rate of gas delivered to the body by the sputum-clearing device is less than the degree to which it assisted in being expelled is greater than during the inspiratory phase. During the inspiratory phase, the volume of gas delivered to the body by the sputum-clearing device is less than or equal to the volume of gas assisted in being expelled. This ensures that during the expiratory phase, the volume of gas input is slightly less than the volume of gas expelled, allowing for more effective removal of airway secretions. Simultaneously, compared to the inspiratory phase, the peak flow rate of the expelled gas is greater than the peak flow rate of the input gas, enhancing shear force and allowing the oscillating airflow to better assist in the removal of airway secretions, thus improving the effectiveness of airway secretion removal. Attached Figure Description

[0069] The accompanying drawings, which are incorporated in and form part of this specification, illustrate embodiments consistent with this application and, together with the description, serve to explain the principles of this application.

[0070] Figure 1 A flowchart illustrating a method for controlling oscillating airflow provided in this application embodiment. Figure 1 ;

[0071] Figure 2 A waveform diagram of an oscillating periodic signal as an example;

[0072] Figure 3 A flowchart illustrating a method for controlling oscillating airflow provided in this application embodiment. Figure 2 ;

[0073] Figure 4 A schematic diagram illustrating the frequency variation of the oscillation period signal during the expiratory phase, as an example;

[0074] Figure 5 A waveform diagram of symmetrical oscillating airflow superimposed with human respiratory gas signals, serving as an example;

[0075] Figure 6 The example is a waveform diagram of asymmetric oscillating airflow superimposed with human respiratory gas signals;

[0076] Figure 7 A schematic diagram of the oscillating airflow control process for example;

[0077] Figure 8 A schematic diagram of the structure of the control device for the oscillating airflow provided in this application;

[0078] Figure 9 This is a schematic diagram of the structure of an electronic device as an example.

[0079] The accompanying drawings illustrate specific embodiments of this application, which will be described in more detail below. These drawings and descriptions are not intended to limit the scope of the concept in any way, but rather to illustrate the concept of this application to those skilled in the art through reference to particular embodiments. Detailed Implementation

[0080] Exemplary embodiments will now be described in detail, examples of which are illustrated in the accompanying drawings. When the following description relates to the drawings, unless otherwise indicated, the same numbers in different drawings denote the same or similar elements. The embodiments described in the following exemplary embodiments do not represent all embodiments consistent with this application. Rather, they are merely examples of apparatuses and methods consistent with some aspects of this application as detailed in the appended claims.

[0081] Airway clearance techniques mechanically loosen and liquefy airway secretions, moving them from the peripheral small airways to the central main airway, maintaining airway patency, and reducing the risk of complications caused by secretions. A commonly used intrapulmonary oscillation technique is a constant-frequency oscillation mode, which generates a symmetrical oscillating airflow with the same amplitude and frequency during both inspiratory and expiratory phases. Its pressure and flow rate amplitude is a unipolar oscillating airflow from zero to positive values, and its frequency and pressure cannot be precisely adjusted. The symmetrical oscillating airflow generated during inspiration may even cause airway secretions to move deeper. During expiration, the single-frequency oscillation wave has limited energy transmitted to the distal small airways, affecting treatment efficacy and resulting in poor effectiveness of airway secretion removal.

[0082] The oscillating airflow control method, apparatus, device, medium, and product provided in this application adjust the positive and negative half-cycle pressure and time of the next oscillating cycle signal of the oscillating airflow based on the peak values ​​and areas of the upper and lower half-cycles of the current oscillating signal during the inspiratory phase. This ensures that the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak of the next oscillating cycle signal is greater than a first value, and the absolute value of the positive half-cycle area of ​​the next oscillating cycle signal during the inspiratory phase is not less than the absolute value of the negative half-cycle area. During the expiratory phase, the oscillating airflow is adjusted based on the peak values ​​and areas of the upper and lower half-cycles of the current oscillating signal during the oscillating phase. The positive and negative half-cycle pressure and time of the signal are adjusted so that the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak of the next oscillation cycle signal is greater than the second value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal in the expiratory phase is not greater than the absolute value of the negative half-cycle area. Among them, the positive half-cycle area represents the volume of gas delivered to the human body by the sputum-clearing device during the inspiratory phase, the negative half-cycle area represents the volume of gas assisted by the sputum-clearing device to be expelled by the human body during the expiratory phase, the positive half-cycle peak value represents the gas flow rate delivered to the human body by the sputum-clearing device during the inspiratory phase, and the negative half-cycle peak value represents the gas flow rate assisted by the sputum-clearing device to be expelled by the human body during the expiratory phase, and the second value is greater than the first value. Therefore, during the inspiratory phase, the flow rate of gas delivered to the body by the sputum-clearing device is less than the flow rate of gas assisted in being expelled by the device, and the ratio between the two is greater than the first value; the volume of gas delivered to the body by the sputum-clearing device during the inspiratory phase is greater than or equal to the volume of gas assisted in being expelled. This ensures that during the inspiratory phase, the volume of gas entering the body is greater than the volume of gas being expelled, avoiding the generation of outward gas during the inspiratory phase, which could cause discomfort to the body; at the same time, the peak flow rate of the expelled gas is greater than the peak flow rate of the gas entering the body, so that the oscillating airflow can assist in expelling airway secretions from the body. During the expiratory phase, the flow rate of gas delivered to the body by the sputum-clearing device is less than the flow rate of gas assisted in being expelled by the device, and the ratio between the two is greater than the second value; the second value is greater than the first value. In other words, during the expiratory phase, the degree to which the flow rate of gas delivered to the body by the sputum-clearing device is less than the degree to which it assisted in being expelled is greater than during the inspiratory phase. During the inspiratory phase, the volume of gas delivered to the body by the sputum-clearing device is less than or equal to the volume of gas assisted in being expelled. This ensures that during the expiratory phase, the volume of gas input is slightly less than the volume of gas expelled, allowing for more effective removal of airway secretions. Simultaneously, compared to the inspiratory phase, the peak flow rate of the expelled gas is greater than the peak flow rate of the input gas, enhancing shear force and allowing the oscillating airflow to better assist in the removal of airway secretions, thus improving the effectiveness of airway secretion removal.

[0083] The technical solution of this application and how the technical solution of this application solves the above-mentioned technical problems are described in detail below with specific embodiments. These specific embodiments can be combined with each other, and the same or similar concepts or processes may not be described again in some embodiments. The embodiments of this application will now be described with reference to the accompanying drawings.

[0084] Figure 1 A flowchart illustrating a method for controlling oscillating airflow provided in this application embodiment. Figure 1 ;like Figure 1 As shown, the method includes the following specific steps:

[0085] Step 101: Obtain the current oscillation period signal of the oscillating airflow generated by the sputum suction device.

[0086] In this embodiment, when the sputum suction device starts working, the current oscillation period signal of the oscillating airflow generated by the sputum suction device can be acquired in real time. For example, the current oscillation period signal can be extracted by using a bandpass filter. The oscillation period signal is a high-frequency oscillation wave signal. The oscillation period signal is a bipolar oscillation signal, that is, the oscillation period signal has positive and negative half cycles.

[0087] Step 102: Based on the current oscillation period signal, perform calculations to obtain the peak values ​​and areas of the positive and negative half-cycles of the current oscillation period signal.

[0088] Optionally, step 102 specifically includes:

[0089] The current oscillation period signal is extracted to obtain the peak value of the positive half cycle, the peak value of the negative half cycle, the time of the positive half cycle, and the time of the negative half cycle.

[0090] The area of ​​the positive half-cycle is calculated based on the peak value and duration of the positive half-cycle.

[0091] The area of ​​the negative half-cycle is calculated based on the peak value and duration of the negative half-cycle.

[0092] In this embodiment, by performing signal extraction and analysis on the current oscillation period signal, the peak value of the positive half-cycle, the peak value of the negative half-cycle, the duration of the positive half-cycle, and the duration of the negative half-cycle of the current oscillation period signal can be obtained. For example, the waveform of the oscillation period signal is similar to a sine wave. Figure 2 A waveform diagram of an example oscillating periodic signal; as shown. Figure 2 As shown, It is half a week. For a negative half-week period, The peak value of the positive half-cycle. It is the peak value of the negative half-cycle.

[0093] Furthermore, the positive half-cycle area can be calculated based on the positive half-cycle peak value and positive half-cycle time; that is, the area of ​​the positive portion of the oscillation period signal. Similarly, the negative half-cycle area can be calculated based on the negative half-cycle peak value and negative half-cycle time; that is, the area of ​​the negative portion of the oscillation period signal. For example, the positive half-cycle peak value is the peak flow rate of the oscillating airflow delivered to the body by the sputum suction device; the positive half-cycle area represents the gas volume of the oscillating airflow delivered to the body by the sputum suction device. The negative half-cycle peak value is the peak flow rate of the oscillating airflow assisted in being discharged by the sputum suction device; the negative half-cycle area represents the gas volume of the oscillating airflow assisted in being discharged by the sputum suction device.

[0094] In this embodiment, by extracting and analyzing the current oscillation period signal, the peak values ​​and durations of the positive and negative half-cycles are obtained; then, based on the peak values ​​and durations of the positive and negative half-cycles, the areas of the positive and negative half-cycles are calculated, thus improving the accuracy of obtaining the peak values ​​and areas of the positive and negative half-cycles.

[0095] Step 103: Determine the current state of human breathing; the state of human breathing includes the inhalation phase and the exhalation phase.

[0096] In this embodiment, after obtaining the peak values ​​and areas of the positive and negative half-cycles of the current oscillation cycle signal, the current human inhalation and exhalation state is determined; so as to adjust and control the oscillation cycle signal based on different inhalation and exhalation states. Specifically, the human inhalation and exhalation state includes an inspiratory phase and an expiratory phase; wherein, the inspiratory phase represents an inhalation stage, that is, from the beginning to the end of inhalation; the expiratory phase represents an exhalation stage, that is, from the beginning to the end of exhalation.

[0097] Optionally, determine the current human breathing state, including:

[0098] Acquire a first gas signal; the first gas signal includes an oscillating airflow signal superimposed with the gas signal of the current human respiration.

[0099] In this embodiment, a first gas signal can be acquired when the sputum clearance device starts working. For example, the first gas signal includes both the oscillating airflow signal generated by the current sputum clearance device and the gas signal generated by the current human respiration; the first signal is the superposition of the two.

[0100] For example, a flow sensor can be used to collect the first gas signal pressure difference value at the airway outlet of the sputum clearance device, and the pressure difference can be converted into a flow rate value through pre-calibration; wherein, the pressure difference value can be the pressure difference across the air resistance of the current sputum clearance device. Then, a pressure sensor can be used to collect the first gas signal pressure value at the airway outlet.

[0101] The first gas signal is filtered to obtain the current flow rate of the human body's respiratory gas.

[0102] In this embodiment, a low-pass filter can be used, with a cutoff frequency of 1 Hz, to filter out the gas signals containing oscillating airflow and current human respiration to obtain the current human respiration gas flow rate value.

[0103] If the current flow rate of the human body's breathing gas is greater than a preset threshold, then the current human body's inhalation and exhalation state is determined to be the inspiratory phase.

[0104] If the current inhalation gas flow rate of the human body is not greater than the preset threshold, then the current inhalation and exhalation state of the human body is determined to be the exhalation phase.

[0105] In this embodiment, the current inspiratory and expiratory state of the human body can be determined based on the current flow rate of the respiratory gas. For example, assuming a preset threshold of 2, if the current flow rate of the respiratory gas is greater than 2, the current inspiratory and expiratory state is determined to be the inspiratory phase; if the current flow rate of the respiratory gas is not greater than 2, the current inspiratory and expiratory state is determined to be the expiratory phase. Alternatively, the inspiratory and expiratory state can be determined based on the filtered flow rate and pressure value of the respiratory gas. For example, if the current flow rate of the respiratory gas is greater than 0, and the pressure value fluctuates within a preset time period, the current inspiratory and expiratory state is determined to be the inspiratory phase. If the current flow rate of the respiratory gas is less than 0, and the pressure value fluctuates within a preset time period, the current inspiratory and expiratory state is determined to be the expiratory phase.

[0106] For example, the net inhalation volume in one inhalation phase is ,when When the lungs are inflated, their air volume increases; when... When the lungs are in a state of exhalation, the lung volume decreases; when... When, it can be equivalent to holding one's breath; the net expiratory volume during one expiratory phase is ,when When the lungs are inflated, their air volume increases; when... When the lungs are in a state of exhalation, the lung volume decreases; when... This is equivalent to breath-holding, controlling the oscillation effect of the system without affecting the patient's spontaneous inhalation volume or inhalation volume under mechanical ventilation. The sum of the net inhalation volume in each oscillation cycle within the inspiratory and expiratory phases is the total inhalation volume. Net inhalation volume within each oscillation cycle This indicates the number of oscillating periodic waves present in a single intake phase. It indicates the number of oscillatory periodic waves present during one expiratory phase. This represents the result of differentiating the area of ​​the positive half-cycle within one oscillation period, which is the flow rate value of the positive half-cycle. This represents the result of differentiating the negative half-cycle area within one oscillation cycle, which is the flow rate value of the negative half-cycle. This represents the positive half-cycle time within one oscillation period; This represents the negative half-cycle time within one oscillation period; This represents the frequency of the positive half-cycle within one oscillation period; It represents the frequency of the negative half-cycle within one oscillation period.

[0107] but:

[0108]

[0109]

[0110]

[0111] In this embodiment, by acquiring the current first gas signal in real time and combining the flow rate value and pressure value of the first gas signal, the current human breathing state is determined, thereby improving the accuracy of the determination of the current human breathing state.

[0112] Step 104: Based on the positive and negative half-cycle peak values ​​and areas, adjust the positive and negative half-cycle pressure and time of the next oscillation cycle signal of the oscillating airflow so that the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak of the next oscillation cycle signal in the inspiratory phase is greater than the first value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal in the inspiratory phase is not less than the absolute value of the negative half-cycle area; the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak of the next oscillation cycle signal in the expiratory phase is greater than the second value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal in the expiratory phase is not greater than the absolute value of the negative half-cycle area.

[0113] In this embodiment, after determining the current breathing state of the human body based on the aforementioned judgment method, the pressure and time of the inhalation and exhalation phases are adjusted respectively.

[0114] Optional, Figure 3 A flowchart illustrating a method for controlling oscillating airflow provided in this application embodiment. Figure 2 ;like Figure 3 As shown, based on the peak values ​​and areas of the positive and negative half-cycles, the pressure and time of the positive and negative half-cycles of the next oscillation cycle signal of the oscillating airflow are adjusted, including:

[0115] Step 201: Based on the positive and negative half-cycle peak values, adjust the positive and negative half-cycle pressures of the next oscillation cycle signal of the oscillating airflow to obtain the positive and negative half-cycle peak values ​​of the next oscillation cycle signal of the oscillating airflow after pressure adjustment.

[0116] In this embodiment, if the human body is currently in the inspiratory phase, the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak is first determined based on the positive and negative half-cycle peak values ​​of the current oscillation cycle. If the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak is not greater than the first value, the positive and negative half-cycle pressures of the oscillating airflow are first adjusted, which is to adjust the positive and negative half-cycle pressures of the next oscillation cycle signal of the oscillating airflow, so that the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak is greater than the first value, thus obtaining the positive and negative half-cycle peak values ​​of the next oscillation cycle signal of the oscillating airflow after pressure adjustment.

[0117] For example, the first value can be 1; when it is the intake phase, the pressure of the positive half-cycle within one oscillation cycle is set to the user-defined pressure, and this pressure will generate an amplitude of The peak flow rate during the positive half-cycle makes ,in, Indicates the peak value of the negative half-cycle. This represents the peak value of the positive half-cycle. The closed-loop adjustment of the pressure value during the negative half-cycle ensures that the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value is greater than the first value.

[0118] Similarly, if the human body is currently in the exhalation phase, first determine whether the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak is greater than the second value based on the positive and negative half-cycle peak values ​​of the current oscillation cycle. If the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak is not greater than the second value, then first adjust the positive and negative half-cycle pressure of the oscillating airflow, that is, adjust the positive and negative half-cycle pressure of the next oscillation cycle signal of the oscillating airflow, so that the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak is greater than the second value. At this time, the positive and negative half-cycle peak values ​​of the next oscillation cycle signal of the oscillating airflow after pressure adjustment are obtained.

[0119] For example, the second value can be 1.5; when it is the expiratory phase, the pressure of the positive half-cycle within one oscillation cycle is set by the user, and this pressure will produce an amplitude of The peak flow rate during the positive half-cycle makes ,in, Indicates the peak value of the negative half-cycle. This represents the peak value of the positive half-cycle. The closed-loop adjustment of the pressure value during the negative half-cycle ensures that the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value is greater than the second value.

[0120] Step 202: Based on the positive and negative half-cycle areas and the peak values ​​of the positive and negative half-cycles of the next oscillation cycle signal of the oscillating airflow after pressure adjustment, adjust the positive and negative half-cycle times of the next oscillation cycle signal of the oscillating airflow to obtain the positive and negative half-cycle areas of the next oscillation cycle signal of the time-adjusted oscillating airflow.

[0121] In this embodiment, after pressure regulation, during the intake phase, it is determined whether the positive and negative half-cycle areas of the current oscillation cycle signal satisfy the condition that the positive half-cycle area is not less than the negative half-cycle area. If the positive and negative half-cycle areas of the current oscillation cycle signal do not satisfy this condition, then based on the positive and negative half-cycle peak values ​​after pressure regulation and the positive and negative half-cycle areas of the current oscillation cycle signal, the positive and negative half-cycle times of the next oscillation cycle signal are adjusted to ensure that the positive and negative half-cycle areas of the next oscillation cycle signal satisfy the condition that the positive half-cycle area is not less than the negative half-cycle area. For example, the initial duty cycle of the positive and negative half-cycle times of the current oscillation cycle signal can be set to 50%. Closed-loop regulation of duty cycle (Duty); This represents the area of ​​the positive half-perimeter. This represents the area of ​​the negative half-circumference.

[0122] Similarly, during the exhalation phase, it is determined whether the positive and negative half-cycle areas of the current oscillation cycle signal satisfy the condition that the positive half-cycle area is not greater than the negative half-cycle area. If the positive and negative half-cycle areas of the current oscillation cycle signal do not satisfy this condition, then the positive and negative half-cycle times of the next oscillation cycle signal are adjusted based on the peak values ​​of the positive and negative half-cycles after pressure regulation and the positive and negative half-cycle areas of the current oscillation cycle signal, so that the positive and negative half-cycle areas of the next oscillation cycle signal satisfy the condition that the positive half-cycle area is not greater than the negative half-cycle area. For example, the initial duty cycle of the positive and negative half-cycle times of the current oscillation cycle signal can be set to 50%. Closed-loop regulation of duty cycle (Duty); This represents the area of ​​the positive half-perimeter. This represents the area of ​​the negative half-circumference.

[0123] It should be noted that the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak can be represented by R, where R is the airflow bias index. When R > 1, it indicates that the airflow is biased towards the expiratory phase, which is a necessary condition for airway mucus clearance. When R < 1, it indicates that the airflow is biased towards the inspiratory phase, resulting in no mucus clearance and even mucus accumulation. When R > 1.5, a net shear force is generated between the airway mucus and the airway mucosa towards the mouth, propelling the mucus. In this asymmetric oscillation, the negative half-cycle time is shorter, the negative half-cycle flow velocity is higher, the airflow profile is flatter, the boundary layer is thinner, and the shear force is stronger.

[0124] In one example, after adjusting the oscillation cycle signal for an inhalation or exhalation phase, the pressure adjustment parameters, time adjustment parameters, inhalation time, and exhalation time of the currently adjusted inhalation and exhalation phases can be recorded. Subsequently, when entering a new inhalation or exhalation phase, the corresponding parameters from the previous inhalation and exhalation phases can be used to control the oscillating airflow.

[0125] In this embodiment, during the inspiratory phase, the positive and negative half-cycle pressure and positive and negative half-cycle time of the next oscillation cycle signal of the oscillating airflow are adjusted based on the peak values ​​and areas of the positive and negative half-cycles of the current oscillation signal of the oscillating airflow. This ensures that the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak of the next oscillation cycle signal is greater than a first value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal during the inspiratory phase is not less than the absolute value of the negative half-cycle area. During the expiratory phase, the positive and negative half-cycle pressure and positive and negative half-cycle time of the next oscillation cycle signal of the oscillating airflow are adjusted based on the peak values ​​and areas of the positive and negative half-cycles of the current oscillation signal of the oscillating airflow. The half-cycle time is adjusted so that the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak of the next oscillation cycle signal is greater than the second value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal in the expiratory phase is not greater than the absolute value of the negative half-cycle area. Among them, the positive half-cycle area represents the volume of gas delivered to the human body by the sputum-clearing device during the inspiratory phase, the negative half-cycle area represents the volume of gas assisted by the sputum-clearing device to be expelled by the human body during the inspiratory phase, the positive half-cycle peak value represents the gas flow rate delivered to the human body by the sputum-clearing device during the inspiratory phase, and the negative half-cycle peak value represents the gas flow rate assisted by the sputum-clearing device to be expelled by the human body during the expiratory phase, and the second value is greater than the first value. Therefore, during the inspiratory phase, the flow rate of gas delivered to the body by the sputum-clearing device is less than the flow rate of gas assisted in being expelled by the device, and the ratio between the two is greater than the first value; the volume of gas delivered to the body by the sputum-clearing device during the inspiratory phase is greater than or equal to the volume of gas assisted in being expelled. This ensures that during the inspiratory phase, the volume of gas entering the body is greater than the volume of gas being expelled, avoiding the generation of outward gas during the inspiratory phase, which could cause discomfort to the body; at the same time, the peak flow rate of the expelled gas is greater than the peak flow rate of the gas entering the body, so that the oscillating airflow can assist in expelling airway secretions from the body. During the expiratory phase, the flow rate of gas delivered to the body by the expectoration device is less than the flow rate of gas assisted in being expelled by the device, and the ratio between the two is greater than the second value; the second value is greater than the first value. In other words, during the expiratory phase, the degree to which the flow rate of gas delivered to the body by the expectoration device is less than the degree to which it assisted in being expelled is greater than during the inspiratory phase. During the inspiratory phase, the volume of gas delivered to the body by the expectoration device is less than or equal to the volume of gas assisted in being expelled. This ensures that during the expiratory phase, the volume of gas input is slightly less than the volume of gas expelled, allowing for more effective removal of airway secretions. Simultaneously, compared to the inspiratory phase, the peak flow rate of the expelled gas is greater than the peak flow rate of the input gas, enhancing shear force and allowing the oscillating airflow to better assist in the removal of airway secretions, improving the effectiveness of airway secretion removal. Furthermore, it prevents sputum from moving deeper into the airways, avoiding adverse effects.

[0126] Optionally, the method also includes:

[0127] If the current human body is in the expiratory phase and the current expiratory phase is not the first expiratory phase, then obtain the expiratory time of the previous expiratory phase.

[0128] Based on the exhalation time and a preset frequency scanning range, the oscillation frequency of each oscillation cycle signal in the current exhalation phase is adjusted according to the frequency sweep function model so that the oscillation frequency of the current exhalation phase varies within the frequency scanning range during the exhalation time; the frequency sweep function characterizes the relationship between time and the oscillation frequency of the oscillation cycle signal.

[0129] In this embodiment, in addition to adjusting the peak flow rate and area of ​​the positive and negative half-cycles of the oscillation period signal as described above, the oscillation frequency of the oscillation period signal of the oscillating airflow is also controlled.

[0130] For example, it is first necessary to determine whether the current expiratory phase is the first expiratory phase. If the current expiratory phase is not the first expiratory phase, the expiratory time of the previous expiratory phase is obtained based on the previous expiratory phase. For example, the oscillation frequency of the oscillation period signal of the oscillating airflow can be left unadjusted during the first expiratory phase. After obtaining the expiratory time based on the first expiratory phase, the oscillation frequency of the oscillation period signal of the oscillating airflow can be adjusted and controlled based on the expiratory time.

[0131] In practical applications, low-frequency oscillations (1~10Hz) primarily affect the distal airways, while mid-to-high-frequency oscillations (10~20Hz) primarily affect the proximal airways. To improve sputum expectoration efficiency, the oscillation frequency is dynamically adjusted from low to high frequencies based on a frequency sweep function model. When in the low-frequency range, the oscillation energy is transferred to the peripheral small airways more efficiently, promoting the liquefaction and movement of sputum from the peripheral small airways towards the main airway. During this movement, the frequency gradually switches to the mid-to-high-frequency oscillation range to maintain the sputum's movement speed.

[0132] Figure 4 This is a schematic diagram illustrating the frequency variation of the oscillation period signal during the expiratory phase; for example... Figure 4 As shown, the oscillation frequency changes from the lower range to the mid-to-high frequency range as time goes on.

[0133] In addition, since different patients have different sputum morphology and humidification levels, fixed frequency and pressure are difficult to meet the physiological conditions of some patients. In order to improve the universality of different patients, a method based on a sweep frequency function model combined with asymmetric pressure is used to control the oscillating airflow.

[0134] In this embodiment, the use of the aforementioned dynamic variation of pressure and frequency provides a more effective new approach for airway clearance physical therapy in clinical patients. Current technologies still have limitations in controlling the oscillation frequency and amplitude of airway clearance sputum clearance oscillations, essentially operating at fixed frequencies and amplitudes. In contrast, this application controls the expiratory phase oscillation frequency based on different sweep functions, allowing the oscillation period signal of the oscillating airflow to be scanned across a range covering both low and high frequencies, further improving the effectiveness of airway secretion removal.

[0135] Optionally, based on the expiratory time and a preset frequency scanning range, the oscillation frequency of each oscillation cycle signal during the expiratory phase is adjusted according to a frequency sweep function model, including:

[0136] If the sputum expectoration device does not have a disease type set, the oscillation frequency of each oscillation cycle signal in the expiratory phase is adjusted based on the expiratory time and the preset frequency scanning range, using a linear function model.

[0137] If the sputum expectoration device is set to a disease type, the oscillation frequency of each oscillation cycle signal in the expiratory phase is adjusted based on the expiratory time and the preset frequency scanning range, using a nonlinear exponential function model.

[0138] In this embodiment, when no disease type is set and the expiratory phase is entered again, the oscillation frequency is adjusted based on the expiratory time of the previous expiratory phase, the preset frequency scanning range, and a linear function model.

[0139] In one example, the exhalation time The set start frequency of the sweep range to cutoff frequency The sweep frequency function model is Calculate the linear coefficients of the linear sweep frequency. and After each oscillation cycle, based on the linear coefficient and Adjust the oscillation frequency This causes its oscillation frequency to change from [previous frequency] throughout the expiratory phase cycle. linear change to .

[0140] The specific method for calculating the linear coefficients is as follows:

[0141] linear coefficients The set start frequency linear coefficients .

[0142] When setting the disease type, the oscillation frequency is adjusted based on the expiration time and the preset frequency scanning range, using a nonlinear exponential function model.

[0143] In one example, when the sputum clearance device is set to chronic obstructive pulmonary disease (COPD), the time to re-enter the expiratory phase is based on the previous expiratory time. The set frequency sweep range arrive The sweep frequency function model is Calculate the coefficients of the nonlinear exponential function frequency sweep. and After each oscillation cycle, the coefficients are swept according to a nonlinear exponential function. and Adjust the oscillation frequency This causes its oscillation frequency to change from [previous frequency] throughout the expiratory phase cycle. Nonlinear change to The specific method for calculating the nonlinear coefficients is as follows:

[0144] Nonlinear coefficients The set start frequency Nonlinear coefficients .

[0145] For example, the sweep frequency can be set to start at 5Hz and end at 20Hz. Physiologically, the 5Hz frequency has stronger penetration ability, and the oscillation wave can spread to the small airways, driving the secretions in the small airways to move towards the central airway. The change from low frequency to high frequency during the expiratory cycle can make the airway secretions move upward more quickly.

[0146] In this embodiment, by setting disease types and not setting disease types, the frequency of expiratory phase oscillation is controlled based on different frequency sweep functions. This allows the oscillation period signal of the oscillating airflow to be scanned within a range covering both low and high frequencies, further improving the effectiveness of airway secretion discharge.

[0147] Optionally, obtain the expiratory time of the previous expiratory phase, including:

[0148] Obtain the positive and negative half-cycle times of each oscillation cycle within the previous expiratory phase.

[0149] The sum of the positive and negative half-cycle times of each oscillation cycle within the previous expiratory phase is used to obtain the expiratory time of the previous expiratory phase.

[0150] In this embodiment, the positive and negative half-cycle times of multiple oscillation cycles of the previous expiratory phase can be obtained; the expiratory time is obtained by summing the multiple positive and negative half-cycle times.

[0151] For example, it can be assumed that the inspiratory time of the multiple inspiratory phases and the expiratory time of the multiple expiratory phases are equal throughout the entire breathing process.

[0152] In this embodiment, the accuracy of obtaining the expiratory time is improved by acquiring the positive and negative half-cycle times of multiple oscillation period signals of the expiratory phase and summing the positive and negative half-cycle times of the multiple oscillation period signals of the expiratory phase.

[0153] Optionally, the method also includes:

[0154] If the current human body is in the inspiratory phase, then the signal is extracted based on the current oscillation cycle signal to obtain the oscillation frequency of the current oscillation cycle signal in the inspiratory phase.

[0155] The oscillation frequency of the current oscillation cycle signal in the intake phase is reduced so that the oscillation frequency of each subsequent oscillation cycle signal in the intake phase is lower than the oscillation frequency of the current oscillation cycle signal.

[0156] In this embodiment, if the current human body is in the inspiratory phase, the oscillation frequency of the current oscillation period signal can be obtained, and the frequency can be reduced so that the oscillation frequency of the oscillation period signal of each subsequent inspiratory phase is lower than the current frequency.

[0157] In this embodiment, the oscillation frequency is reduced to a certain extent during the inspiratory phase. This can prevent airway secretions from moving deeper into the lungs due to an excessively high frequency during the inspiratory phase, which would be detrimental to the expulsion effect. At the same time, it avoids the discomfort caused to the human body by an excessively high oscillation frequency.

[0158] Figure 5 A waveform diagram of symmetrical oscillating airflow superimposed on human respiratory gas signals, as shown in the example; Figure 5 As shown, in the waveform diagram of the human breathing phase, the positive half-cycle represents the inhalation phase and the negative half-cycle represents the exhalation phase. The waveform of the symmetrical oscillating airflow is consistent in the inhalation and exhalation phases.

[0159] Figure 6 The example is a waveform diagram of asymmetric oscillating airflow superimposed with human respiratory gas signals; such as... Figure 6 As shown in the waveform diagram of the human breathing phase, the positive half-cycle represents the inspiratory phase and the negative half-cycle represents the expiratory phase. The waveform of the asymmetric oscillating airflow is inconsistent between the inspiratory and expiratory phases; specifically, the peak flow rate and oscillation frequency are inconsistent.

[0160] Figure 7 A schematic diagram of the oscillating airflow control process for example; as shown. Figure 7As shown, firstly, a first gas signal is acquired, obtaining its flow rate and pressure values. This first gas signal is then filtered to obtain the human body's respiratory gas flow rate and pressure values. The current respiratory state of the human body is then determined. Based on this respiratory state, the pressure and frequency adjustment method for the oscillation period signal of the oscillating airflow is determined. Depending on whether a disease type is set, a sweep function is determined. The pressure and frequency of the oscillating airflow's oscillation period signal are then controlled. The oscillating airflow with controlled pressure and frequency is acquired in real-time and cyclically, obtaining the first gas signal generated by the cyclically controlled oscillating airflow. Subsequent control processes are then performed based on this first gas signal.

[0161] In one example, by adding a tracer to artificial sputum and injecting fresh sheep lungs to simulate an in vitro scenario, this application improves the sputum movement distance by 50% compared to current technical solutions by using a bipolar airway clearance oscillation airflow with dynamic pressure and frequency conversion based on the patient's inhalation and exhalation phase discrimination, integrated flow, pressure and volume control.

[0162] In animal experiments, the movement of sputum in the main airway and fourth-order bronchi of anesthetized experimental pigs was observed through fiberoptic bronchioles. Compared with the current technical approach, the sputum movement distance was increased by 40%.

[0163] The oscillating airflow control method provided in this application adjusts the positive and negative half-cycle pressure and time of the next oscillating cycle signal of the oscillating airflow based on the peak values ​​and areas of the upper and lower half-cycles of the current oscillating signal during the inspiratory phase. This ensures that the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak of the next oscillating cycle signal is greater than a first value, and the absolute value of the positive half-cycle area of ​​the next oscillating cycle signal during the inspiratory phase is not less than the absolute value of the negative half-cycle area. During the expiratory phase, the method adjusts the positive and negative half-cycle pressure and time of the next oscillating cycle signal based on the peak values ​​and areas of the upper and lower half-cycles of the current oscillating signal during the oscillating phase. The half-cycle pressure and positive and negative half-cycle times are adjusted so that the ratio of the absolute value of the negative half-cycle peak to the absolute value of the positive half-cycle peak of the next oscillation cycle signal is greater than the second value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal in the expiratory phase is not greater than the absolute value of the negative half-cycle area. Among them, the positive half-cycle area represents the volume of gas delivered to the human body by the sputum-clearing device during the inspiratory phase, the negative half-cycle area represents the volume of gas assisted by the sputum-clearing device to be expelled by the human body during the expiratory phase, the positive half-cycle peak value represents the gas flow rate delivered to the human body by the sputum-clearing device during the inspiratory phase, and the negative half-cycle peak value represents the gas flow rate assisted by the sputum-clearing device to be expelled by the human body during the expiratory phase, and the second value is greater than the first value. Therefore, during the inspiratory phase, the flow rate of gas delivered to the body by the sputum-clearing device is less than the flow rate of gas assisted in being expelled by the device, and the ratio between the two is greater than the first value; the volume of gas delivered to the body by the sputum-clearing device during the inspiratory phase is greater than or equal to the volume of gas assisted in being expelled. This ensures that during the inspiratory phase, the volume of gas entering the body is greater than the volume of gas being expelled, avoiding the generation of outward gas during the inspiratory phase, which could cause discomfort to the body; at the same time, the peak flow rate of the expelled gas is greater than the peak flow rate of the gas entering the body, so that the oscillating airflow can assist in expelling airway secretions from the body. During the expiratory phase, the flow rate of gas delivered to the body by the sputum-clearing device is less than the flow rate of gas assisted in being expelled by the device, and the ratio between the two is greater than the second value; the second value is greater than the first value. In other words, during the expiratory phase, the degree to which the flow rate of gas delivered to the body by the sputum-clearing device is less than the degree to which it assisted in being expelled is greater than during the inspiratory phase. During the inspiratory phase, the volume of gas delivered to the body by the sputum-clearing device is less than or equal to the volume of gas assisted in being expelled. This ensures that during the expiratory phase, the volume of gas input is slightly less than the volume of gas expelled, allowing for more effective removal of airway secretions. Simultaneously, compared to the inspiratory phase, the peak flow rate of the expelled gas is greater than the peak flow rate of the input gas, enhancing shear force and allowing the oscillating airflow to better assist in the removal of airway secretions, thus improving the effectiveness of airway secretion removal.

[0164] Figure 8A schematic diagram of the structure of the control device for the oscillating airflow provided in this application; as shown Figure 8 As shown, the control device for the oscillating airflow provided in this embodiment includes:

[0165] The acquisition module 21 is used to acquire the current oscillation period signal of the oscillating airflow generated by the sputum suction device.

[0166] The calculation module 22 is used to perform calculations based on the current oscillation period signal to obtain the peak values ​​and areas of the positive and negative half-cycles of the current oscillation period signal.

[0167] The judgment module 23 is used to judge the current human body's inhalation and exhalation state; the human body's inhalation and exhalation state includes the inhalation phase and the exhalation phase.

[0168] The adjustment module 24 is used to adjust the positive and negative half-cycle pressure and positive and negative half-cycle time of the next oscillation cycle signal of the oscillating airflow according to the positive and negative half-cycle peak values ​​and the negative half-cycle area, so that the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value of the next oscillation cycle signal in the inspiratory phase is greater than a first value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal in the inspiratory phase is not less than the absolute value of the negative half-cycle area; the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value of the next oscillation cycle signal in the expiratory phase is greater than a second value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal in the expiratory phase is not greater than the absolute value of the negative half-cycle area; the second value is greater than the first value.

[0169] In one possible implementation, the adjustment module 24 is specifically used for:

[0170] Based on the positive and negative half-cycle peak values, adjust the positive and negative half-cycle pressures of the next oscillation cycle signal of the oscillating airflow to obtain the positive and negative half-cycle peak values ​​of the next oscillation cycle signal of the oscillating airflow after pressure regulation.

[0171] Based on the positive and negative half-cycle areas and the peak values ​​of the positive and negative half-cycles of the next oscillation cycle signal of the oscillating airflow after pressure adjustment, the positive and negative half-cycle times of the next oscillation cycle signal of the oscillating airflow are adjusted to obtain the positive and negative half-cycle areas of the next oscillation cycle signal of the time-adjusted oscillating airflow.

[0172] In one possible implementation, the computing module 22 is specifically used for:

[0173] The current oscillation period signal is extracted to obtain the peak value of the positive half cycle, the peak value of the negative half cycle, the time of the positive half cycle, and the time of the negative half cycle.

[0174] The area of ​​the positive half-cycle is calculated based on the peak value and duration of the positive half-cycle.

[0175] The area of ​​the negative half-cycle is calculated based on the peak value and duration of the negative half-cycle.

[0176] In one possible implementation, the adjustment module 24 is further configured to:

[0177] If the current human body is in the expiratory phase and the current expiratory phase is not the first expiratory phase, then obtain the expiratory time of the previous expiratory phase.

[0178] Based on the exhalation time and a preset frequency scanning range, the oscillation frequency of each oscillation cycle signal in the current exhalation phase is adjusted according to the frequency sweep function model so that the oscillation frequency of the current exhalation phase varies within the frequency scanning range during the exhalation time; the frequency sweep function characterizes the relationship between time and the oscillation frequency of the oscillation cycle signal.

[0179] In one possible implementation, the adjustment module 24 is specifically used for:

[0180] If the sputum expectoration device does not have a disease type set, the oscillation frequency of each oscillation cycle signal in the expiratory phase is adjusted based on the expiratory time and the preset frequency scanning range, using a linear function model.

[0181] If the sputum expectoration device is set to a disease type, the oscillation frequency of each oscillation cycle signal in the expiratory phase is adjusted based on the expiratory time and the preset frequency scanning range, using a nonlinear exponential function model.

[0182] In one possible implementation, the adjustment module 24 is specifically used for:

[0183] Obtain the positive and negative half-cycle times of each oscillation cycle within the previous expiratory phase.

[0184] The sum of the positive and negative half-cycle times of each oscillation cycle within the previous expiratory phase is used to obtain the expiratory time of the previous expiratory phase.

[0185] In one possible implementation, the adjustment module 24 is further configured to:

[0186] If the current human body is in the inspiratory phase, then the current oscillation period signal is extracted based on the current oscillation period signal to obtain the oscillation frequency of the current oscillation period signal in the inspiratory phase.

[0187] The oscillation frequency of the current oscillation cycle signal in the intake phase is reduced so that the oscillation frequency of each oscillation cycle signal in subsequent intake phases is lower than the oscillation frequency of the current oscillation cycle signal.

[0188] In one possible implementation, the determination module 23 is specifically used for:

[0189] Acquire a first gas signal; the first gas signal includes an oscillating airflow signal superimposed with the gas signal of the current human respiration.

[0190] The first gas signal is filtered to obtain the current flow rate of the human body's respiratory gas.

[0191] If the current flow rate of the human body's breathing gas is greater than a preset threshold, then the current human body's inhalation and exhalation state is determined to be the inspiratory phase.

[0192] If the current inhalation gas flow rate of the human body is not greater than the preset threshold, then the current inhalation and exhalation state of the human body is determined to be the exhalation phase.

[0193] The oscillating airflow control device provided in this embodiment can execute the oscillating airflow control method provided in the above method embodiment. Its implementation principle and technical effect are similar, and will not be described in detail here.

[0194] Figure 9 This is a schematic diagram of the structure of an electronic device as an example. The device includes:

[0195] The device includes a processor 291 and a memory 292; it may also include a communication interface 293 and a bus 294. The processor 291, memory 292, and communication interface 293 can communicate with each other via the bus 294. The communication interface 293 can be used for information transmission. The processor 291 can invoke logical instructions stored in the memory 292 to execute the methods described in the example above.

[0196] Furthermore, the logic instructions in the aforementioned memory 292 can be implemented as software functional units and, when sold or used as independent products, can be stored in a computer-readable storage medium.

[0197] The memory 292, as a computer-readable storage medium, can be used to store software programs and computer-executable programs, such as program instructions / modules corresponding to the methods in the embodiments of this application. The processor 291 executes functional applications and data processing by running the software programs, instructions, and modules stored in the memory 292, that is, it implements the methods in the above method examples.

[0198] The memory 292 may include a program storage area and a data storage area. The program storage area may store the operating system and application programs required for at least one function; the data storage area may store data created based on the use of the terminal device. Furthermore, the memory 292 may include high-speed random access memory and may also include non-volatile memory.

[0199] This application also provides a computer-readable storage medium storing computer-executable instructions, which, when executed by a processor, are used to implement the method in any of the embodiments.

[0200] This application also provides a computer program product, including a computer program that, when executed by a processor, is used to implement the method in any of the embodiments.

[0201] It should be noted that, for the sake of simplicity, the foregoing method embodiments are all described as a series of actions. However, those skilled in the art should understand that this application is not limited to the described order of actions, as some steps may be performed in other orders or simultaneously according to this application. Furthermore, those skilled in the art should also understand that the embodiments described in the specification are all optional embodiments, and the actions and modules involved are not necessarily essential to this application.

[0202] It should be further noted that although the steps in the flowchart are shown sequentially according to the arrows, these steps are not necessarily executed in the order indicated by the arrows. Unless explicitly stated herein, there is no strict order restriction on the execution of these steps, and they can be executed in other orders. Moreover, at least some steps in the flowchart may include multiple sub-steps or multiple stages. These sub-steps or stages are not necessarily completed at the same time, but can be executed at different times. The execution order of these sub-steps or stages is not necessarily sequential, but can be performed alternately or in turn with other steps or at least some of the sub-steps or stages of other steps.

[0203] It should be understood that the above-described device embodiments are merely illustrative, and the device of this application can also be implemented in other ways. For example, the division of units / modules in the above embodiments is only a logical functional division, and there may be other division methods in actual implementation. For example, multiple units, modules, or components may be combined, or integrated into another system, or some features may be ignored or not executed.

[0204] Furthermore, unless otherwise specified, the functional units / modules in the various embodiments of this application can be integrated into one unit / module, or each unit / module can exist physically separately, or two or more units / modules can be integrated together. The integrated units / modules described above can be implemented in hardware or as software program modules.

[0205] When integrated units / modules are implemented in hardware, the hardware can be digital circuits, analog circuits, etc. The physical implementation of the hardware structure includes, but is not limited to, transistors, memristors, etc. Unless otherwise specified, the processor can be any suitable hardware processor, such as a CPU, GPU, FPGA, DSP, and ASIC, etc. Unless otherwise specified, the storage unit can be any suitable magnetic or magneto-optical storage medium, such as Resistive Random Access Memory (RRAM), Dynamic Random Access Memory (DRAM), Static Random Access Memory (SRAM), Enhanced Dynamic Random Access Memory (EDRAM), High-Bandwidth Memory (HBM), Hybrid Memory Cube (HMC), etc.

[0206] If the integrated unit / module is implemented as a software program module and sold or used as an independent product, it can be stored in a computer-readable storage device (CMD). Based on this understanding, the technical solution of this application, in essence, or the part that contributes to the prior art, or all or part of the technical solution, can be embodied in the form of a software product. This computer software product is stored in a memory and includes several instructions to cause a computer device (which may be a personal computer, server, or network device, etc.) to execute all or part of the steps of the methods of the various embodiments of this application. The aforementioned memory includes various media capable of storing program code, such as a USB flash drive, read-only memory (ROM), random access memory (RAM), portable hard drive, magnetic disk, or optical disk.

[0207] In the above embodiments, the descriptions of each embodiment have their own emphasis. For parts not described in detail in a certain embodiment, please refer to the relevant descriptions of other embodiments. The technical features of the above embodiments can be combined arbitrarily. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as the combination of these technical features does not contradict each other, it should be considered within the scope of this specification.

[0208] Other embodiments of this application will readily occur to those skilled in the art upon consideration of the specification and practice of the invention disclosed herein. This application is intended to cover any variations, uses, or adaptations of this application that follow the general principles of this application and include common knowledge or customary techniques in the art not disclosed herein. The specification and examples are to be considered exemplary only, and the true scope and spirit of this application are indicated by the foregoing claims.

[0209] It should be understood that this application is not limited to the precise structure described above and shown in the accompanying drawings, and various modifications and changes can be made without departing from its scope. The scope of this application is limited only by the appended claims.

Claims

1. An electronic device, characterized in that, include: Memory, processor; The memory stores computer-executed instructions; The processor executes the computer execution instructions stored in the memory, causing the processor to perform the following steps: Acquire the current oscillation period signal of the oscillating airflow generated by the sputum suction device; Based on the current oscillation period signal, calculations are performed to obtain the peak values ​​and areas of the positive and negative half-cycles of the current oscillation period signal. Determine the current state of human breathing; the state of human breathing includes the inspiratory phase and the expiratory phase; Based on the positive and negative half-cycle peak values ​​and the positive and negative half-cycle areas, the positive and negative half-cycle pressures and times of the next oscillation cycle signal of the oscillating airflow are adjusted so that the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value of the next oscillation cycle signal of the inspiratory phase is greater than a first value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal of the inspiratory phase is not less than the absolute value of the negative half-cycle area; the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value of the next oscillation cycle signal of the expiratory phase is greater than a second value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal of the expiratory phase is not greater than the absolute value of the negative half-cycle area; the second value is greater than the first value.

2. The electronic device according to claim 1, characterized in that, When the processor executes the step of adjusting the positive and negative half-cycle pressure and positive and negative half-cycle time of the next oscillation cycle signal of the oscillating airflow based on the positive and negative half-cycle peak values ​​and the positive and negative half-cycle areas, it specifically performs the following steps: Based on the positive and negative half-cycle peak values, adjust the positive and negative half-cycle pressures of the next oscillation cycle signal of the oscillating airflow to obtain the positive and negative half-cycle peak values ​​of the next oscillation cycle signal of the oscillating airflow after pressure adjustment. Based on the positive and negative half-cycle areas and the positive and negative half-cycle peak values ​​of the next oscillation cycle signal of the oscillating airflow after pressure adjustment, the positive and negative half-cycle times of the next oscillation cycle signal of the oscillating airflow are adjusted to obtain the positive and negative half-cycle areas of the next oscillation cycle signal of the oscillating airflow after time adjustment.

3. The electronic device according to claim 1, characterized in that, When the processor performs the calculation based on the current oscillation period signal to obtain the peak values ​​and areas of the positive and negative half-cycles of the current oscillation period signal, it specifically executes the following steps: The current oscillation period signal is extracted to obtain the positive half-cycle peak value, negative half-cycle peak value, positive half-cycle time, and negative half-cycle time. The area of ​​the positive half-cycle is calculated based on the positive half-cycle peak value and the positive half-cycle time. The negative half-cycle area is calculated based on the negative half-cycle peak value and the negative half-cycle time.

4. The electronic device according to claim 1, characterized in that, The processor also performs the following steps: If the current human body is in the expiratory phase and the current expiratory phase is not the first expiratory phase, then obtain the expiratory time of the previous expiratory phase; Based on the exhalation time and a preset frequency scanning range, and using a frequency sweep function model, the oscillation frequency of each oscillation cycle signal of the current exhalation phase is adjusted so that the oscillation frequency of the current exhalation phase varies within the frequency scanning range during the exhalation time; the frequency sweep function characterizes the relationship between time and the oscillation frequency of the oscillation cycle signal.

5. The electronic device according to claim 4, characterized in that, When the processor performs the step of adjusting the oscillation frequency of each oscillation cycle signal of the expiratory phase based on the expiratory time and a preset frequency scanning range and a frequency sweep function model, it specifically executes the following steps: If the sputum expectoration device does not have a disease type set, then based on the expiratory time and a preset frequency scanning range, the oscillation frequency of each oscillation cycle signal of the expiratory phase is adjusted according to a linear function model. If the sputum expectoration device is configured with disease types, then based on the expiratory time and a preset frequency scanning range, the oscillation frequency of each oscillation cycle signal of the expiratory phase is adjusted according to a nonlinear exponential function model.

6. The electronic device according to claim 4, characterized in that, When the processor executes the step of obtaining the expiratory time of the previous expiratory phase, it specifically performs the following steps: Obtain the positive and negative half-cycle times of each oscillation cycle within the previous expiratory phase; The sum of the positive and negative half-cycle times of each oscillation cycle within the previous expiratory phase is calculated to obtain the expiratory time of the previous expiratory phase.

7. The electronic device according to claim 1, characterized in that, The processor also performs the following steps: If the current human body's inhalation and exhalation state is the inhalation phase, then based on the current oscillation cycle signal, signal extraction is performed to obtain the oscillation frequency of the current oscillation cycle signal of the inhalation phase; The oscillation frequency of the current oscillation cycle signal of the intake phase is reduced so that the oscillation frequency of each oscillation cycle signal of the subsequent intake phase is lower than the oscillation frequency of the current oscillation cycle signal.

8. The electronic device according to any one of claims 1-7, characterized in that, When the processor performs the step of determining the current human breathing state, it specifically executes the following steps: Acquire a first gas signal; the first gas signal includes an oscillating airflow signal superimposed with the gas signal of the current human respiration; The first gas signal is filtered to obtain the current flow rate of the human body's breathing gas; If the current human body's respiratory gas flow rate is greater than a preset threshold, then the current human body's inhalation and exhalation state is determined to be the inspiratory phase. If the current flow rate of the human body's breathing gas is not greater than the preset threshold, then the current human body's inhalation and exhalation state is determined to be the expiratory phase.

9. A control device for oscillating airflow, characterized in that, include: The acquisition module is used to acquire the current oscillation period signal of the oscillating airflow generated by the sputum suction device; The calculation module is used to perform calculations based on the current oscillation period signal to obtain the peak values ​​and areas of the positive and negative half-cycles of the current oscillation period signal. The judgment module is used to determine the current human breathing state; the human breathing state includes the inhalation phase and the exhalation phase; The adjustment module is used to adjust the positive and negative half-cycle pressure and positive and negative half-cycle time of the next oscillation cycle signal of the oscillating airflow according to the positive and negative half-cycle peak values ​​and the positive and negative half-cycle areas, so that the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value of the next oscillation cycle signal of the inspiratory phase is greater than a first value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal of the inspiratory phase is not less than the absolute value of the negative half-cycle area; the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value of the next oscillation cycle signal of the expiratory phase is greater than a second value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal of the expiratory phase is not greater than the absolute value of the negative half-cycle area; the second value is greater than the first value.

10. A computer-readable storage medium, characterized in that, The computer-readable storage medium stores computer-executable instructions, which, when executed by a processor, are used to perform the following steps: Acquire the current oscillation period signal of the oscillating airflow generated by the sputum suction device; Based on the current oscillation period signal, calculations are performed to obtain the peak values ​​and areas of the positive and negative half-cycles of the current oscillation period signal. Determine the current state of human breathing; the state of human breathing includes the inspiratory phase and the expiratory phase; Based on the positive and negative half-cycle peak values ​​and the positive and negative half-cycle areas, the positive and negative half-cycle pressures and times of the next oscillation cycle signal of the oscillating airflow are adjusted so that the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value of the next oscillation cycle signal of the inspiratory phase is greater than a first value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal of the inspiratory phase is not less than the absolute value of the negative half-cycle area; the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value of the next oscillation cycle signal of the expiratory phase is greater than a second value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal of the expiratory phase is not greater than the absolute value of the negative half-cycle area; the second value is greater than the first value.

11. The computer-readable storage medium according to claim 10, characterized in that, When the computer execution instructions are executed by the processor, they are specifically used to implement the following steps: Based on the positive and negative half-cycle peak values, adjust the positive and negative half-cycle pressures of the next oscillation cycle signal of the oscillating airflow to obtain the positive and negative half-cycle peak values ​​of the next oscillation cycle signal of the oscillating airflow after pressure adjustment. Based on the positive and negative half-cycle areas and the positive and negative half-cycle peak values ​​of the next oscillation cycle signal of the oscillating airflow after pressure adjustment, the positive and negative half-cycle times of the next oscillation cycle signal of the oscillating airflow are adjusted to obtain the positive and negative half-cycle areas of the next oscillation cycle signal of the oscillating airflow after time adjustment.

12. The computer-readable storage medium according to claim 10, characterized in that, When the computer execution instructions are executed by the processor, they are specifically used to implement the following steps: The current oscillation period signal is extracted to obtain the positive half-cycle peak value, negative half-cycle peak value, positive half-cycle time, and negative half-cycle time. The area of ​​the positive half-cycle is calculated based on the positive half-cycle peak value and the positive half-cycle time. The negative half-cycle area is calculated based on the negative half-cycle peak value and the negative half-cycle time.

13. The computer-readable storage medium according to claim 10, characterized in that, When the computer execution instructions are executed by the processor, they are also used to perform the following steps: If the current human body is in the expiratory phase and the current expiratory phase is not the first expiratory phase, then obtain the expiratory time of the previous expiratory phase; Based on the exhalation time and a preset frequency scanning range, and using a frequency sweep function model, the oscillation frequency of each oscillation cycle signal of the current exhalation phase is adjusted so that the oscillation frequency of the current exhalation phase varies within the frequency scanning range during the exhalation time; the frequency sweep function characterizes the relationship between time and the oscillation frequency of the oscillation cycle signal.

14. The computer-readable storage medium according to claim 13, characterized in that, When the computer execution instructions are executed by the processor, they are specifically used to implement the following steps: If the sputum expectoration device does not have a disease type set, then based on the expiratory time and a preset frequency scanning range, the oscillation frequency of each oscillation cycle signal of the expiratory phase is adjusted according to a linear function model. If the sputum expectoration device is configured with disease types, then based on the expiratory time and a preset frequency scanning range, the oscillation frequency of each oscillation cycle signal of the expiratory phase is adjusted according to a nonlinear exponential function model.

15. The computer-readable storage medium according to claim 13, characterized in that, When the computer execution instructions are executed by the processor, they are specifically used to implement the following steps: Obtain the positive and negative half-cycle times of each oscillation cycle within the previous expiratory phase; The sum of the positive and negative half-cycle times of each oscillation cycle within the previous expiratory phase is calculated to obtain the expiratory time of the previous expiratory phase.

16. The computer-readable storage medium according to claim 10, characterized in that, When the computer execution instructions are executed by the processor, they are also used to perform the following steps: If the current human body's inhalation and exhalation state is the inhalation phase, then based on the current oscillation cycle signal, signal extraction is performed to obtain the oscillation frequency of the current oscillation cycle signal of the inhalation phase; The oscillation frequency of the current oscillation cycle signal of the intake phase is reduced so that the oscillation frequency of each oscillation cycle signal of the subsequent intake phase is lower than the oscillation frequency of the current oscillation cycle signal.

17. The computer-readable storage medium according to any one of claims 10-16, characterized in that, When the computer execution instructions are executed by the processor, they are specifically used to implement the following steps: Acquire a first gas signal; the first gas signal includes an oscillating airflow signal superimposed with the gas signal of the current human respiration; The first gas signal is filtered to obtain the current flow rate of the human body's breathing gas; If the current human body's respiratory gas flow rate is greater than a preset threshold, then the current human body's inhalation and exhalation state is determined to be the inspiratory phase. If the current flow rate of the human body's breathing gas is not greater than the preset threshold, then the current human body's inhalation and exhalation state is determined to be the expiratory phase.

18. A computer program product, characterized in that, This includes a computer program that, when executed by a processor, performs the following steps: Acquire the current oscillation period signal of the oscillating airflow generated by the sputum suction device; Based on the current oscillation period signal, calculations are performed to obtain the peak values ​​and areas of the positive and negative half-cycles of the current oscillation period signal. Determine the current state of human breathing; the state of human breathing includes the inspiratory phase and the expiratory phase; Based on the positive and negative half-cycle peak values ​​and the positive and negative half-cycle areas, the positive and negative half-cycle pressures and times of the next oscillation cycle signal of the oscillating airflow are adjusted so that the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value of the next oscillation cycle signal of the inspiratory phase is greater than a first value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal of the inspiratory phase is not less than the absolute value of the negative half-cycle area; the ratio of the absolute value of the negative half-cycle peak value to the absolute value of the positive half-cycle peak value of the next oscillation cycle signal of the expiratory phase is greater than a second value, and the absolute value of the positive half-cycle area of ​​the next oscillation cycle signal of the expiratory phase is not greater than the absolute value of the negative half-cycle area; the second value is greater than the first value.

19. The computer program product according to claim 18, characterized in that, When executed by the processor, this computer program specifically performs the following steps: Based on the positive and negative half-cycle peak values, adjust the positive and negative half-cycle pressures of the next oscillation cycle signal of the oscillating airflow to obtain the positive and negative half-cycle peak values ​​of the next oscillation cycle signal of the oscillating airflow after pressure adjustment. Based on the positive and negative half-cycle areas and the positive and negative half-cycle peak values ​​of the next oscillation cycle signal of the oscillating airflow after pressure adjustment, the positive and negative half-cycle times of the next oscillation cycle signal of the oscillating airflow are adjusted to obtain the positive and negative half-cycle areas of the next oscillation cycle signal of the oscillating airflow after time adjustment.

20. The computer program product according to claim 18, characterized in that, When executed by the processor, this computer program specifically performs the following steps: The current oscillation period signal is extracted to obtain the positive half-cycle peak value, negative half-cycle peak value, positive half-cycle time, and negative half-cycle time. The area of ​​the positive half-cycle is calculated based on the positive half-cycle peak value and the positive half-cycle time. The negative half-cycle area is calculated based on the negative half-cycle peak value and the negative half-cycle time.

21. The computer program product according to claim 18, characterized in that, When executed by the processor, this computer program also performs the following steps: If the current human body is in the expiratory phase and the current expiratory phase is not the first expiratory phase, then obtain the expiratory time of the previous expiratory phase; Based on the exhalation time and a preset frequency scanning range, and using a frequency sweep function model, the oscillation frequency of each oscillation cycle signal of the current exhalation phase is adjusted so that the oscillation frequency of the current exhalation phase varies within the frequency scanning range during the exhalation time; the frequency sweep function characterizes the relationship between time and the oscillation frequency of the oscillation cycle signal.

22. The computer program product according to claim 21, characterized in that, When executed by the processor, this computer program specifically performs the following steps: If the sputum expectoration device does not have a disease type set, then based on the expiratory time and a preset frequency scanning range, the oscillation frequency of each oscillation cycle signal of the expiratory phase is adjusted according to a linear function model. If the sputum expectoration device is configured with disease types, then based on the expiratory time and a preset frequency scanning range, the oscillation frequency of each oscillation cycle signal of the expiratory phase is adjusted according to a nonlinear exponential function model.

23. The computer program product according to claim 21, characterized in that, When executed by the processor, this computer program specifically performs the following steps: Obtain the positive and negative half-cycle times of each oscillation cycle within the previous expiratory phase; The sum of the positive and negative half-cycle times of each oscillation cycle within the previous expiratory phase is calculated to obtain the expiratory time of the previous expiratory phase.

24. The computer program product according to claim 18, characterized in that, When executed by the processor, this computer program specifically performs the following steps: If the current human body's inhalation and exhalation state is the inhalation phase, then based on the current oscillation cycle signal, signal extraction is performed to obtain the oscillation frequency of the current oscillation cycle signal of the inhalation phase; The oscillation frequency of the current oscillation cycle signal of the intake phase is reduced so that the oscillation frequency of each oscillation cycle signal of the subsequent intake phase is lower than the oscillation frequency of the current oscillation cycle signal.

25. The computer program product according to any one of claims 18-24, characterized in that, When executed by the processor, this computer program specifically performs the following steps: Acquire a first gas signal; the first gas signal includes an oscillating airflow signal superimposed with the gas signal of the current human respiration; The first gas signal is filtered to obtain the current flow rate of the human body's breathing gas; If the current human body's respiratory gas flow rate is greater than a preset threshold, then the current human body's inhalation and exhalation state is determined to be the inspiratory phase. If the current flow rate of the human body's breathing gas is not greater than the preset threshold, then the current human body's inhalation and exhalation state is determined to be the expiratory phase.

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