WO2024130777A1 - Visual respiratory therapy instrument, visual processing method, and use method - Google Patents

Abstract

Provided is a visual respiratory therapy instrument comprising a host (100), a patient interface (200), and a patient state display screen (300). The host (100) is provided with an air channel (101), an oxygen channel (102), an air-oxygen mixing portion (103), and a mixed gas channel (104) and comprises a flow sensor (105) for monitoring the flow of mixed gas and a pressure sensor (106) for monitoring the pressure of the mixed gas. An inlet of the air-oxygen mixing portion (103) is in gas communication with the air channel (101) and the oxygen channel (102), and an outlet of the air-oxygen mixing portion (103) is in gas communication with the mixed gas channel (104). The patient interface (200) is in gas communication with the mixed gas channel (104) via a pipeline (107). The host (100) is configured for receiving and processing monitoring data of the flow sensor (105) and the pressure sensor (106) to output high-flow oxygen therapy display information to the patient state display screen (300). The patient state display screen (300) comprises a dynamic display area for a patient end pressure and/or a dynamic display area for a patient inhalation flow and is configured for displaying high-flow oxygen therapy display information.

Description

A visual respiratory therapy device, a visual processing method and a use method

This application claims the priority of the Chinese patent application filed with the China Patent Office on December 23, 2022, with application number 202211668073.9 and invention name "A visual respiratory therapy device, a visual processing method and a use method", the entire contents of which are incorporated by reference in this application.

Technical Field

The present application relates to the technical field of medical data visualization, and in particular to a visualization respiratory therapy device, a visualization processing method, and a use method.

Background technique

High-flow nasal cannula oxygen therapy (HFNC) is a new respiratory support technology that has been widely used in clinical practice. Compared with traditional low-flow oxygen therapy, high-flow oxygen therapy can provide patients with high-flow gas with relatively constant oxygen concentration, temperature and humidity, and perform oxygen therapy through nasal congestion. Compared with non-invasive ventilation through a mask for respiratory support, this treatment method is more comfortable.

At present, during the use of HFNC, medical staff generally set the operating parameters to make the high-flow output device output a fixed high-flow airflow. Since it is difficult to monitor the patient's own respiratory parameters during the operation of the high-flow output device, it is difficult to control the user experience during the patient's use. At the same time, medical staff cannot understand the patient's treatment status in a timely manner, making the current use of high-flow output devices not smart enough.

Summary of the invention

The embodiments of the present application provide a visualized respiratory therapy device, a visualized processing method, and a method of use, which are used to solve the problem that the current high-flow output device cannot flexibly meet the usage needs of patients and medical staff during the use of the HFNC therapy device, and is not flexible and intelligent enough.

On the one hand, an embodiment of the present application provides a visual respiratory therapy device, the therapy device comprising a host and a patient interface, and a patient status display screen;

The main unit is provided with an air channel, an oxygen channel, an air-oxygen mixing portion and a mixed gas channel, and includes a flow sensor for monitoring the flow of the mixed gas and a pressure sensor for monitoring the pressure of the mixed gas;

The inlet of the air-oxygen mixing part is connected to the air channel and the oxygen channel respectively, and the outlet of the air-oxygen mixing part is connected to the mixed gas channel;

The patient interface is connected to the mixed gas channel through a pipeline; wherein the patient interface is a non-sealed patient interface;

The host is used to receive and process the monitoring data of the flow sensor and the pressure sensor to output high-flow oxygen therapy display information to the patient status display screen;

The patient status display screen includes a patient-end pressure dynamic display area and/or a patient inhalation flow dynamic display area, which are used to display the high-flow oxygen therapy display information.

Preferably, the therapeutic apparatus further comprises a humidifier;

The humidifier inlet is in gas communication with the mixed gas channel, and the humidifier outlet is in gas communication with the patient interface.

Preferably, the patient interface is a nasal cannula, and the pipeline and the patient interface are an integral or separate structure; the pipeline and the humidifier are detachably connected.

Preferably, the patient status display screen also includes a patient capacity dynamic display area.

Preferably, the patient-end pressure dynamic display area, the patient inhalation flow dynamic display area, and the patient capacity dynamic display area are located on the same display interface.

Preferably, the oxygen channel further includes an oxygen source interface, an oxygen valve and an oxygen flow sensor for monitoring the oxygen flow.

Preferably, the therapeutic apparatus further comprises: an airflow controller;

The airflow controller is connected to the oxygen valve and the air-oxygen mixing unit, and is used to generate an airflow control signal according to an adjustment instruction from a user interface, so as to control the oxygen valve and/or the air-oxygen mixing unit to adjust the output oxygen flow, oxygen concentration or mixed gas flow of the therapeutic device.

Preferably, the air-oxygen mixing section comprises a turbine.

On the other hand, an embodiment of the present application further provides a visualization processing method of a visualization respiratory therapy device, the method comprising:

Based on the collected data corresponding to the pipeline verification operation and the delivery flow value of the mixed gas from the flow sensor, the patient interface pressure value of the current patient is determined through a preset pipeline pressure drop model; wherein the pipeline verification operation is that the patient interface is under atmospheric pressure, and multiple levels of step flow gas flow are output in sequence at intervals within a preset time; the collected data at least includes: the step flow values corresponding to the multiple levels of step flow, and the pressure values corresponding to each level of step flow;

Based on the patient interface pressure value and the corresponding delivery flow value within a predetermined number of breaths of the current patient, and a preset pipeline output leakage model, the respiratory flow value of the current patient is determined in real time;

Based on the patient interface pressure value and the respiratory flow value, high-flow oxygen therapy display information of the current patient is determined, and the high-flow oxygen therapy display information is sent to a patient status display screen to display the high-flow oxygen therapy display information.

In one implementation of the present application, a flow output control instruction is generated according to the multi-level step flow, and the flow output control instruction is sent to the flow control device, so that the flow control device sequentially outputs the airflow of the multi-level step flow at intervals within the preset time; wherein the sequentially interval output is the airflow of each level of step flow continuously output within each consecutive predetermined sub-time of the preset time; the predetermined sub-time corresponds to each level of step flow one by one;

Obtain the pressure values corresponding to each level of step flow from the pressure sensor;

Determining the pipeline resistance coefficient of the pipeline pressure drop model based on the pressure values corresponding to the various levels of step flow and the corresponding step flow values;

When the patient interface is connected to the ventilation end of the current patient, the patient interface pressure value of the current patient is determined according to the pipeline pressure drop model and the delivery pressure value and the delivery flow value from the pressure sensor.

In one implementation of the present application, a linear equation group is established according to the pressure values corresponding to the stepped flow rates at each level, the multiple stepped flow values corresponding to the pressure values corresponding to the stepped flow rates at each level, and a preset formula;

The least square solution of the linear equation group is calculated, and the least square solution is used as the pipeline resistance coefficient.

In one implementation of the present application, according to the pipeline output leakage model, the patient interface pressure value of the current patient within a predetermined number of breaths is subjected to absolute value square root processing and sign function operation to obtain an intermediate pressure value;

Performing integration operations on the intermediate amount of the pressure value and the delivery flow value respectively;

Calculate the quotient of the intermediate amount of the pressure value after the integral operation and the delivery flow value after the integral operation, and use the quotient as a leakage model parameter of the pipeline output leakage model;

Based on the leakage model parameters, the patient interface pressure value, the pipeline output leakage model and the delivery flow value, the respiratory flow value of the current patient is determined in real time.

In one implementation of the present application, a respiratory trigger signal of the current patient is identified, and the number of triggering times of the respiratory trigger signal is accumulated;

When the triggering number is greater than or equal to the predetermined number, determining the patient interface pressure value and the corresponding delivery flow value in each breath;

Determining the leakage model parameters based on the predetermined number of patient interface pressure values and the corresponding delivery flow values;

Based on the leakage model parameters, the patient interface pressure value, the pipeline output leakage model and the delivery flow value, the respiratory flow value of the current patient is determined in real time.

In one implementation of the present application, a plurality of intermediate pressure values corresponding to the predetermined number of patient interface pressure values are determined; and

determining a plurality of said delivery flow values corresponding to a plurality of said intermediate pressure quantities;

Performing integral summation operations on a plurality of intermediate pressure values and a plurality of delivery flow values respectively;

Calculate the quotient of the intermediate quantities of the plurality of pressure values after integral summation and the plurality of delivery flow values after integral summation, and use the quotient as a leakage model parameter of the pipeline output leakage model;

Based on the leakage model parameters, the patient interface pressure value, the pipeline output leakage model and the delivery flow value, the respiratory flow value of the current patient is determined in real time.

In one implementation of the present application, when a breathing trigger signal of the current patient is identified, a cumulative starting point breath of the triggering number is determined;

According to the number of interval breaths between the accumulated starting breath and the current breath and the predetermined number, the accumulated starting breath of the triggering number is updated to the Nth breath after the accumulated starting breath; N is a natural number; N is the difference between the number of interval breaths and the predetermined number.

In one implementation of the present application, the high-flow oxygen therapy display information includes at least one or more of the following: patient interface pressure curve, respiratory flow curve, patient capacity curve, respiratory rate, tidal volume, minute ventilation, end-tidal pressure, peak inspiratory flow, and actual inspired oxygen concentration.

In one implementation of the present application, the first airflow capacity and the second airflow capacity corresponding to each breath are determined according to the respiratory flow value of each breath of the current patient and the corresponding delivery flow value; the first airflow capacity is the airflow capacity inhaled from the patient interface for each breath of the current patient; the second airflow capacity is the airflow capacity inhaled from the atmosphere for each breath of the current patient;

Determining the total inhaled capacity according to the respiratory flow value of each breath of the current patient;

Acquire oxygen flow data from an oxygen flow sensor, and determine output oxygen concentration based on the oxygen flow data;

The output oxygen concentration, the first airflow capacity, the second airflow capacity, the preset atmospheric oxygen ratio and the total inhalation capacity are input into a preset inhaled oxygen concentration formula to calculate the actual inhaled oxygen concentration.

On the other hand, the embodiment of the present application further provides a method for using a visualized respiratory therapeutic apparatus, which is applied to the above-mentioned visualized respiratory therapeutic apparatus. The method for using the therapeutic apparatus includes:

A pipeline verification operation step of measuring the pipeline resistance coefficient between the patient interface and the pipeline after replacing the patient interface and/or the pipeline.

Preferably, when measuring the pipeline resistance coefficient, the patient interface is directly connected to the atmosphere.

Preferably, the pipeline verification operation includes the step of testing a multi-level step flow, specifically including: generating a flow output control instruction according to the multi-level step flow, and sending the flow output control instruction to the flow control device, so that the flow control device sequentially outputs the airflow of the multi-level step flow at intervals within the preset time; wherein the sequentially interval output is the airflow of each level of step flow continuously output within each consecutive predetermined sub-time of the preset time; the predetermined sub-time corresponds to each level of step flow one by one;

Obtain the pressure values corresponding to each level of step flow from the pressure sensor;

Based on the pressure values corresponding to the various levels of step flow and the corresponding step flow values, the pipeline resistance coefficient of the pipeline pressure drop model is determined.

Through the above scheme, the visual respiratory therapy instrument and the pipeline pressure drop model are used to calibrate the pipeline resistance coefficient of the therapeutic instrument, and then the pipeline output leakage model is used to determine the user's respiratory flow in real time and obtain the patient interface pressure value, and further analyze and obtain respiratory related parameters. Providing visual respiratory related waveforms and parameters can facilitate medical staff to timely grasp the pipeline wearing status and patient treatment effect during the treatment process based on these data.

At the same time, it provides a more comprehensive decision-making support tool for medical staff to set treatment parameters when using high-flow mode, avoiding blind settings and enabling users to better control the trend of sequential treatment. It realizes that the use needs of patients and medical staff can be flexibly met during the use of HFNC therapeutic device, making HFNC therapeutic device more flexible and intelligent, and improving the user experience.

BRIEF DESCRIPTION OF THE DRAWINGS

The drawings described herein are used to provide a further understanding of the present application and constitute a part of the present application. The illustrative embodiments of the present application and their descriptions are used to explain the present application and do not constitute an improper limitation on the present application. In the drawings:

FIG1 is a schematic diagram of the structure of a visual respiratory therapy device according to an embodiment of the present application;

FIG2 is a flow chart of a visualization processing method of a visualization respiratory therapy apparatus in an embodiment of the present application;

FIG3 is a schematic diagram of the contents displayed on a patient status display screen of a visual respiratory therapy apparatus according to an embodiment of the present application;

FIG. 4 is another flow chart of a visualization processing method of a visualization respiratory therapy device in an embodiment of the present application.

Detailed ways

In order to make the purpose, technical solution and advantages of the present application clearer, the technical solution of the present application will be clearly and completely described below in combination with the specific embodiments of the present application and the corresponding drawings. Obviously, the described embodiments are only part of the embodiments of the present application, not all of the embodiments. Based on the embodiments in the present application, all other embodiments obtained by ordinary technicians in this field without making creative work are within the scope of protection of the present application.

In recent years, high-flow humidified nasal oxygen therapy (HFNC) has been widely used in clinical practice as a new respiratory support technology. The therapeutic equipment to implement this technology mainly includes an air-oxygen mixing device, a heated humidifier, a high-flow nasal cannula, and a connected breathing circuit.

Compared with traditional low-flow oxygen therapy, high-flow oxygen therapy can provide patients with high-flow gas with relatively constant oxygen concentration, temperature and humidity, and oxygen therapy is performed through nasal congestion. Compared with non-invasive ventilation through masks for respiratory support, this treatment method is more comfortable. A large number of clinical trials have shown that high-flow humidified oxygen therapy has clinical value in improving oxygenation, reducing respiratory dead space, improving alveolar ventilation, and facilitating secretion clearance. Therefore, it can be used as a pre- or post-invasive respiratory treatment for invasive or non-invasive ventilation.

As high-flow therapy is clinically recognized, more and more dedicated high-flow treatment devices have appeared on the market. In addition to these dedicated high-flow treatment devices, almost all newly launched ventilators have begun to integrate this treatment mode. However, the current high-flow devices or high-flow modes of integrated ventilators only output a fixed set flow rate (1 to 100L/min) of mixed oxygen (oxygen concentration 21% to 100%) airflow, and cannot monitor and control respiratory-related parameters. The patient's respiratory-related parameters are very important for medical staff. Not only can they understand the treatment effect of high-flow oxygen therapy, but they can also pay attention to whether the patient has abnormal conditions in a timely manner. The inability to monitor and control respiratory-related parameters makes the current equipment unable to flexibly meet the needs of patients and medical staff, and is not flexible and intelligent enough.

Based on this, the embodiments of the present application provide a visual respiratory therapy device, a visual processing method and a usage method, which are used to solve the problem that the current high-flow output device cannot flexibly meet the usage needs of patients and medical staff during the HFNC therapy process, and is not flexible and intelligent enough.

The following describes in detail various embodiments of the present application in conjunction with the accompanying drawings.

FIG1 is a schematic diagram of the structure of a visualized respiratory therapy device according to an embodiment of the present application. The therapy device includes a host 100 , a patient interface 200 , and a patient status display screen 300 .

The host 100 is provided with an air channel 101, an oxygen channel 102, an air-oxygen mixing section 103 and a mixed gas channel 104, and includes a flow sensor 105 for monitoring the flow of the mixed gas and a pressure sensor 106 for monitoring the pressure of the mixed gas. The inlet of the air-oxygen mixing section 103 is connected to the air path of the air channel 101 and the oxygen channel 102, respectively, and the outlet of the air-oxygen mixing section 103 is connected to the air path of the mixed gas channel 104. The patient interface 200 is connected to the air path of the mixed gas channel 104 via a pipeline 107. Among them, the patient interface 200 is a non-sealed patient interface. The host 100 is used to receive and process the monitoring data of the flow sensor 105 and the pressure sensor 106 to output high-flow oxygen therapy display information to the patient status display screen 300. The patient status display screen 300 includes a patient-end pressure dynamic display area and/or a patient inhalation flow dynamic display area, which are used to display high-flow oxygen therapy display information.

The patient status display screen 300 provided in the embodiment of the present application can be a touch screen or a high-definition display screen, and the host 100 can be connected to an external input device. The user can interact with the host through the input device and the patient status display screen.

In one example, the therapeutic apparatus further includes a humidifier 108 . The inlet of the humidifier 108 is in gas communication with the mixed gas channel 104 , and the outlet of the humidifier 108 is in gas communication with the patient interface 200 through the pipeline 107 .

In one example, the patient interface 200 is a nasal cannula, and the tube 107 and the patient interface 200 are an integral or separate structure. The tube 107 and the humidifier 108 are detachably connected.

In actual use, with the development and advancement of technology, the patient interface may not be limited to the nasal cannula. This application takes the insertion of the patient interface into the patient's nasal cavity as an exemplary existence.

In one example, the patient status display screen 300 further includes a patient volume dynamic display area.

In one example, the patient-side pressure dynamic display area, the patient inhalation flow dynamic display area, and the patient capacity dynamic display area are located on the same display interface.

In one example, the oxygen channel 102 further includes an oxygen source interface 1, an oxygen valve 2, and an oxygen flow sensor 3 for monitoring the oxygen flow.

In one example, the therapeutic apparatus further includes an air flow controller 109 .

The airflow controller 109 is connected to the oxygen valve 2 and the air-oxygen mixing unit 103, and is used to generate an airflow control signal according to the adjustment instructions from the user interface (or user terminal) so as to control the oxygen valve 2 and/or the air-oxygen mixing unit 103 to adjust the output oxygen flow, oxygen concentration or mixed gas flow of the therapeutic apparatus.

The user interface can be a user interface composed of the above-mentioned input device and display screen, or a user interface displayed on the user terminal interface after the host establishes a wireless or wired connection with a user terminal, such as a mobile phone, a laptop, etc. The user interface can trigger the generation of an adjustment instruction for adjusting the host.

In one example, the air-oxygen mixing section 103 includes a turbine.

The above-mentioned visualized respiratory therapy device can display relevant information of the patient's breathing in real time. The air channel 101, oxygen channel 102, air-oxygen mixing part 103, mixed gas channel 104, flow sensor 105, and pressure sensor 106 constitute the gas path structure of the therapy device. The patient status display screen 300 can be set to be integrated with the host.

The therapeutic apparatus of the present application, after oxygen from a high-pressure oxygen source enters the therapeutic apparatus, passes through the oxygen source interface 1 of the oxygen channel 102, enters the oxygen valve 2, and after being adjusted by the oxygen valve 2, passes through the oxygen flow sensor 3 to enter the air-oxygen mixing part 103, i.e., the turbine. After air enters the therapeutic apparatus from the atmosphere, it is mixed with oxygen. After the mixed gas is pressurized by the turbine, it passes through the flow sensor 105 and the pressure sensor 106, and then output to the ventilation pipeline, in which there is a humidifier 108 for heating and humidifying the mixed gas. The heated and humidified mixed gas enters the patient's body through the patient interface (nasal catheter).

In addition, the air flow controller 109 can control the oxygen valve 2 to adjust the oxygen flow rate and oxygen concentration, and can also control the air-oxygen mixing part to control the total flow rate of the mixed gas. The total flow rate is equal to the sum of the oxygen flow rate and the air flow rate. If the input oxygen flow rate exceeds the total flow rate, the excess oxygen will be output to the atmosphere through the air inlet.

The total flow target and oxygen concentration target controlled by the airflow controller are set by the user, such as through a human-machine interface composed of an input device and a display screen, or through a human-machine interface of a touch-operated patient status display screen. The user sends the control target to the airflow controller through the human-machine interface and also receives feedback information returned by the airflow controller.

The current high-flow output device cannot flexibly meet the needs of patients and medical staff, and is not flexible and intelligent enough. The main reason is that the therapeutic device cannot monitor the patient's breathing-related parameters, and it cannot visualize the parameter data. Figure 2 is a flow chart of a visualization processing method of a visualization respiratory therapeutic device provided by an embodiment of the present application. The visualization processing method is implemented with a software module in the host of the therapeutic device as the execution subject. The software module can be located on the processor of the host and its storage medium. As shown in Figure 2, the method includes steps S201-S203:

S201, based on the collected data corresponding to the pipeline verification operation and the delivery flow value of the mixed gas from the flow sensor, the patient interface pressure value of the current patient is determined through a preset pipeline pressure drop model.

The pipeline verification operation is that the patient interface is under atmospheric pressure, and multiple step flow airflows are output in sequence at intervals within a preset time. The collected data at least includes: the step flow values corresponding to the multiple step flow rates, and the pressure values corresponding to each step flow rate.

The pipeline verification operation is a verification operation that needs to be performed when changing patients or replacing certain parts of the treatment device or when using it for the first time. During the pipeline verification operation, the patient interface is not connected to the patient's nasal cavity and is in the atmosphere to verify the air resistance of the pipeline. Before the patient wears a nasal cannula for ventilation, first connect the machine to all the pipeline components to be ventilated, including but not limited to bacterial filters, ventilation pipelines, humidifiers, and nasal cannulas, to ensure that the nasal cannula (patient interface) is exposed to the atmosphere and that there are no leaks or blockages at the connections of the pipeline.

In the embodiment of the present application, based on the collected data corresponding to the pipeline verification operation and the delivery flow value of the mixed gas from the flow sensor, the patient interface pressure value of the current patient is determined by a preset pipeline pressure drop model, specifically including:

According to the multi-level step flow, a flow output control instruction is generated, and the flow output control instruction is sent to the flow control device, so that the flow control device outputs the airflow of the multi-level step flow in sequence and at intervals within a preset time.

The airflows of each level of step flow are outputted in sequence and at intervals and are continuously outputted within each consecutive predetermined sub-time of the preset time. The predetermined sub-time corresponds to each level of step flow.

In other words, before the pipeline verification operation is performed, the storage medium of the therapeutic apparatus pre-stores multiple step flow rates such as Qvent1_ca, Qvent2_ca, ..., Qventn_ca, and the flow value of each level of the multiple step flow rates is different. The software can generate a flow output control instruction, and the flow control device sequentially outputs the airflow of the multiple step flow rates at intervals within a preset time. The flow control device can be a partial device composed of an airflow controller and an air-oxygen mixing unit.

Next, the pressure values corresponding to each level of step flow from the pressure sensor are obtained.

For example, the preset time is 2 seconds, each level of step flow lasts for 2 seconds, and the pressure value corresponding to each level of step flow in 2 seconds is recorded until the corresponding pressures Pvent1_ca, Pvent2_ca,..., Pventn_ca of n step flow points are recorded; where n is a natural number.

Then, based on the pressure values corresponding to each level of step flow and the step flow values corresponding thereto, the pipeline resistance coefficient of the pipeline pressure drop model is determined.

Specifically, a linear equation system is established according to the pressure values corresponding to each level of step flow, multiple step flow values corresponding to the pressure values corresponding to each level of step flow, and a preset formula, and the least squares solution of the linear equation system is calculated, and the least squares solution is used as the pipeline resistance coefficient.

The preset formula is as follows:

Pventi_ca＝Rtube×Qventi_ca ²

Among them, Pventi_ca is the pressure value corresponding to the i-th step flow. Rtube represents the pipeline resistance coefficient. Qventi_ca is the i-th step flow value, and each step flow corresponds to a unique pressure value.

The linear equations are as follows:

According to the above linear equations, the following formula can be obtained, and the least squares solution calculated is the pipeline resistance coefficient Rtube.

At this point, the determination of the pipeline resistance coefficient, i.e., air resistance, has been completed. It should be noted that each time a new patient or pipeline is changed, the pipeline calibration operation should be performed again.

When the patient interface is connected to the ventilation end of the current patient, that is, when the patient starts to use the therapeutic device, the patient interface pressure value of the current patient is determined according to the pipeline pressure drop model and the delivery pressure value and delivery flow value from the pressure sensor.

The pipeline pressure drop model is as follows:

Pnose＝Pvent-Rtube×Qvent ²

Among them, Pnose is the patient interface pressure value, Pvent is the delivery pressure value, and Qvent is the delivery flow value.

Step S201 is a step for the therapeutic device to measure the pipeline resistance coefficient in an offline state, and to perform online nasal pressure Pnose according to the pipeline resistance coefficient. Since the patient's interface is not blocked during the high-flow gas delivery process when the patient actually uses the therapeutic device of this application, gas leakage will occur. In order to ensure the accuracy of the patient's respiratory flow value obtained during high-flow oxygen therapy, this application provides the following embodiment step S202.

S202, based on the patient interface pressure value and the corresponding delivery flow value within a predetermined number of breaths of the current patient, and a preset pipeline output leakage model, the current patient's respiratory flow value is determined in real time.

The predetermined number of times is pre-set, such as 3 times, 5 times, etc. The predetermined number of breaths is used to determine the leakage model parameters of the pipeline output leakage model.

In the embodiment of the present application, based on the patient interface pressure value and the corresponding delivery flow value within the current patient's predetermined number of breaths, and the preset pipeline output leakage model, the current patient's respiratory flow value is determined in real time, specifically including:

Firstly, according to the pipeline output leakage model, the absolute value square root processing and sign function operation are performed on the patient interface pressure value of the current patient within a predetermined number of breaths to obtain the intermediate value of the pressure value.

The flow rate Qleak leaking to the atmosphere through the unblocked part of the nasal catheter is proportional to the nasal pressure Pnose. The pipeline output leakage model is as follows:

Among them, Qleak is the flow value leaked into the atmosphere, Kleak is the leakage model parameter, Sgn is a positive and negative function, and in the embodiment of the present application, the Sgn function is negative when Pnose is lower than the atmospheric pressure, and vice versa.

得到压力值中间量。 That is to say, according to the above pipeline output leakage model and the patient interface pressure value of each breath of the current patient within the predetermined number of breaths, solve

Get the intermediate pressure value.

Next, the intermediate pressure value and the delivery flow value are integrated.

That is, the intermediate pressure value and the delivery flow rate value are integrated at the start and end times of breathing, respectively.

Subsequently, the quotient of the intermediate amount of the pressure value after the integral operation and the delivery flow value after the integral operation is calculated, and the quotient is used as a leakage model parameter of the pipeline output leakage model.

Right now,

Wherein, N is a natural number. In the formula corresponding to the above embodiment, N can be 1, which refers to the preset number of times, that is, the quotient of the intermediate amount of the pressure value after the integral operation and the delivery flow value after the integral operation; t0 is the breathing start time, and te is the breathing end time. In actual use, the formula also contains the integral amount of the patient's respiratory flow Qpatient. Since the patient's inhaled air volume is approximately equal to the exhaled air volume per breath, in one breath, the integral amount of the patient's respiratory flow is 0 and is not considered in the above formula.

Next, based on the leakage model parameters, the patient interface pressure value, the pipeline output leakage model and the delivery flow value, the current patient's respiratory flow value is determined in real time.

The leakage model parameters obtained by the preset number of breaths and the real-time measured patient interface pressure value are input into the pipeline output leakage model to obtain the flow value leaked to the atmosphere by the patient for each breath. The current patient's respiratory flow value is calculated based on the difference between the delivered flow value and the flow value, i.e., Qpatient = Qvent - Qleak.

In the embodiment of the present application, based on the patient interface pressure value and the corresponding delivery flow value within the current patient's predetermined number of breaths, and the preset pipeline output leakage model, the current patient's respiratory flow value is determined in real time, specifically including:

Identify the respiratory trigger signal of the current patient and accumulate the number of triggers of the respiratory trigger signal. When the number of triggers is greater than or equal to the predetermined number, determine the patient interface pressure value and the corresponding delivery flow value in each breath. Determine the leakage model parameters based on the predetermined number of patient interface pressure values and the corresponding delivery flow values. Determine the respiratory flow value of the current patient in real time based on the leakage model parameters, the patient interface pressure value, the pipeline output leakage model and the delivery flow value.

In other words, the software module of the therapeutic device can identify the patient's breathing. The identification can be based on the instantaneous change of pressure Pnose or Qpatient exceeding a certain threshold (the falling mutation point of Pnose or the rising mutation point of Qpatient marks the beginning of the patient's inhalation), or it can be combined with the turbine speed or control current change, etc. The present application does not specifically limit the specific method of identification.

The calculation of the leakage model parameters and the respiratory flow value refers to the above embodiment and will not be repeated here.

Wherein, based on a predetermined number of patient interface pressure values and corresponding delivery flow values, leakage model parameters are determined, specifically including:

Determine a plurality of intermediate pressure values corresponding to a predetermined number of patient interface pressure values. And determine a plurality of delivery flow values corresponding to the plurality of intermediate pressure values. Perform integral summation operations on the plurality of intermediate pressure values and the plurality of delivery flow values, respectively. Calculate the quotient of the plurality of intermediate pressure values after the integral summation operation and the plurality of delivery flow values after the integral summation operation, and use the quotient as a leakage model parameter of the pipeline output leakage model. Based on the leakage model parameters, the patient interface pressure value, the pipeline output leakage model and the delivery flow value, determine the respiratory flow value of the current patient in real time.

In other words, N in the above formula for calculating the leakage model parameters of the present application is a preset number, wherein N is more appropriately 3-5 during actual use.

In one embodiment of the present application, after determining the leakage model parameters based on a predetermined number of patient interface pressure values and corresponding delivery flow values, the method further includes:

When a respiratory trigger signal of the current patient is identified, a cumulative starting point breath of the trigger times is determined.

According to the accumulated number of interval breaths between the starting breath and the current breath and the predetermined number, the accumulated starting breath of the triggering number is updated to be the Nth breath after the accumulated starting breath. N is a natural number. N is the difference between the interval breath number and the predetermined number.

Here, N refers to the difference between the number of interval breaths and the predetermined number. For example, the predetermined number is 3, and the Ath breath is taken as the cumulative starting breath. The B and C breaths after the Ath breath reach the predetermined number. At the Dth breath, the software should calculate the leakage model parameters with the A, B, and C breaths, and calculate the respiratory flow value of the Dth breath. The cumulative starting breath is A, and the number of interval breaths from it to the current breath D is 4, which is greater than the predetermined number, and N = 1. The cumulative starting breath of the updated trigger number is the Nth breath after the cumulative starting breath, that is, the cumulative starting breath of the updated trigger number is the first breath B after the A breath. That is, B is taken as the cumulative starting breath.

By updating the accumulated starting breath, the leakage model parameters can be updated in a rolling manner, and each update is based on the delivery pressure value and delivery flow value of the previous predetermined number of breaths. In this way, when the position of the nasal cannula worn by the patient changes, it can also adapt to the change in time.

S203, based on the patient interface pressure value and the respiratory flow value, determine the high-flow oxygen therapy display information of the current patient, and send the high-flow oxygen therapy display information to the patient status display screen to display the high-flow oxygen therapy display information.

In an embodiment of the present application, the software can generate a corresponding patient interface pressure value curve and a respiratory flow curve based on the patient interface pressure value and respiratory flow value obtained in real time. The patient capacity curve can also be obtained by integrating the respiratory flow curve. As shown in Figure 3, the high-flow oxygen therapy display information includes at least one or more of the following: patient interface pressure curve (nasal pressure), respiratory flow curve (patient flow), patient capacity curve, respiratory rate (respiration rate, RR), tidal volume (Tidal volume, VT), minute ventilation volume (minute ventilation volume, MV), Positive End Expiratory Pressure (Positive End Expiratory Pressure, PEEP), peak inspiratory flow (peak inspiratory flow, represented by Fpeak in the figure), and actual inspired oxygen concentration (represented by FiO2_real in the figure). HFT stands for high-flow oxygen therapy.

The actual inspired oxygen concentration can be determined according to the following examples, as follows.

First, according to the respiratory flow value of each breath of the current patient and the corresponding delivery flow value, the first airflow capacity and the second airflow capacity corresponding to each breath are determined. The first airflow capacity is the airflow capacity inhaled from the patient interface for each breath of the current patient. The second airflow capacity is the airflow capacity inhaled from the atmosphere for each breath of the current patient.

Next, the total inhaled volume is determined based on the respiratory flow value of each breath of the current patient.

Then, the oxygen flow rate data from the oxygen flow rate sensor is obtained, and the output oxygen concentration is determined based on the oxygen flow rate data.

Finally, the output oxygen concentration, the first airflow capacity, the second airflow capacity, the preset atmospheric oxygen percentage and the total inhalation capacity are input into the preset inhaled oxygen concentration formula to calculate the actual inhaled oxygen concentration.

The preset inspired oxygen concentration formula is as follows:

FiO2_real = (V1×FiO2_vent+V2×21%)/V3

Among them, FiO2_vent is the output oxygen concentration, V1 is the first airflow capacity, V2 is the second airflow capacity, V3 is the total inhalation capacity, V1 refers to the cumulative capacity of the patient flow in one inhalation where the inhalation flow is lower than the therapeutic device air flow, V2 refers to the cumulative capacity of the patient flow in one inhalation where the inhalation flow exceeds the therapeutic device air flow, and V3 refers to the cumulative capacity of the total patient flow in one inhalation. Among them, the oxygen concentration of the inhaled air is 21%.

In one embodiment of the present application, the respiratory frequency RR is calculated at the time t0 when each inhalation begins (that is, the end time te of the previous breath), and the duration of the previous breath Tie = te-t0, and then the inverse of the duration Tie (in seconds) of a breath is multiplied by 60, which is the current frequency RRi calculated for this breath. The moving average of the previous multiple breathing frequencies can be used as the respiratory frequency RR.

In one embodiment of the present application, at the beginning of each inhalation, the tidal volume VT is reset to zero, and Qpatient is accumulated again to calculate the patient volume Vpatient. At the beginning of the next inhalation, the maximum volume Vmax and the minimum volume Vmin of this inhalation are calculated, and the tidal volume of this breath is VTi = (2×Vmax-Vmin)/2. The moving average of the tidal volumes of the previous multiple breaths can be used as the tidal volume VT.

In one embodiment of the present application, the minute ventilation MV may be updated once in each breath, MV=VT×RR.

In one embodiment of the present application, the end-expiratory pressure PEEP is calculated at the beginning of each inhalation, and the average value of the patient interface pressure value Pnose in the period before this moment (50 milliseconds→100 milliseconds) is used as the monitoring value of PEEP.

In one embodiment of the present application, the inspiratory peak flow rate Fpeak may be the highest point value of the Qpatient waveform detected in each breath, which serves as the inspiratory peak monitoring value Fpeak.

This application can obtain the offline pipeline resistance coefficient through the pipeline pressure drop model constructed above, and then calculate the online patient interface pressure value Pnose, and calculate the leakage model parameters online through the pipeline output leakage model. Based on the two models and their parameter calculation results, the patient interface pressure waveform and patient respiratory flow waveform of the patient treated by the therapeutic device can be monitored in real time, which is convenient for medical staff to timely grasp the pipeline wearing status and patient treatment effect during the treatment process according to the waveform.

The present application can also analyze the patient interface pressure waveform and the patient respiratory flow waveform to obtain several relevant parameters of breathing. Medical staff can accurately titrate high-flow treatment setting parameters, such as flow targets, based on the monitored respiratory parameters. The visual respiratory therapy device provided by the present application provides a more comprehensive decision-making support tool for medical staff to set treatment parameters when using the high-flow mode, avoiding blind settings and enabling users to better control the trend of sequential treatment. This ensures that the use needs of patients and medical staff can be flexibly met during the use of the HFNC therapy device, making the HFNC therapy device more flexible and intelligent, and improving the user experience.

The visualization processing method implemented by the software model of the present application includes the following steps, as shown in FIG4 , specifically including:

S401, calculation of offline pipeline resistance coefficient Rtube;

S402, online nose tip pressure calculation Pnose;

S403, online nasal cannula leakage coefficient calculation Kleak;

S404, patient flow calculation Qpatient;

S405, respiratory parameter calculation RR, VT, MV, PEEP, Fpeak, FiO2_real;

S406, waveform and parameter information display and abnormal information prompt.

The software module can send the obtained waveforms and parameters to the display screen for display, and prompt abnormal information during the patient's breathing process or the operation of the therapeutic device.

The present application also provides a method for using a visualized respiratory therapy apparatus, which is applied to the above-mentioned visualized respiratory therapy apparatus. The method for using the visualized respiratory therapy apparatus includes:

A circuit calibration procedure to measure the circuit resistance coefficient between the patient interface and the circuit after replacing the patient interface and/or the circuit.

Among them, during the pipeline verification operation, when measuring the pipeline resistance coefficient, the patient interface is directly connected to the atmosphere.

The pipeline verification operation also includes the step of test driving a multi-level step flow, specifically including: generating a flow output control instruction according to the multi-level step flow, and sending the flow output control instruction to the flow control device, so that the flow control device sequentially outputs the airflow of the multi-level step flow at intervals within the preset time. Among them, the airflow of each level of step flow output sequentially and at intervals is continuously output within each consecutive predetermined sub-time of the preset time. The predetermined sub-time corresponds to each level of step flow one by one. Obtain the pressure value corresponding to each level of step flow from the pressure sensor. Based on the pressure value corresponding to each level of step flow and the corresponding step flow value, determine the pipeline resistance coefficient of the pipeline pressure drop model.

After the pipeline verification operation is completed, the patient interface can be inserted into the patient's nasal cavity to perform normal use of the therapeutic device. The specific embodiment of the above-mentioned visualization processing method can be referred to, and no further description is given here.

Those skilled in the art will appreciate that the embodiments of this specification may be provided as methods, systems, or computer program products. Therefore, the embodiments of this specification may be in the form of complete hardware embodiments, complete software embodiments, or embodiments in combination with software and hardware. Moreover, the embodiments of this specification may be in the form of a computer program product implemented in one or more computer-usable storage media (including but not limited to disk storage, CD-ROM, optical storage, etc.) that contain computer-usable program code.

This specification is described with reference to the flowchart and/or block diagram of the method, device (system), and computer program product according to the embodiment of this specification. It should be understood that each process and/or box in the flowchart and/or block diagram, as well as the combination of the process and/or box in the flowchart and/or block diagram can be implemented by computer program instructions. These computer program instructions can be provided to a processor of a general-purpose computer, a special-purpose computer, an embedded processor or other programmable data processing device to produce a machine, so that the instructions executed by the processor of the computer or other programmable data processing device produce a device for implementing the functions specified in one process or multiple processes in the flowchart and/or one box or multiple boxes in the block diagram.

These computer program instructions may also be stored in a computer-readable memory that can direct a computer or other programmable data processing device to work in a specific manner, so that the instructions stored in the computer-readable memory produce a manufactured product including an instruction device that implements the functions specified in one or more processes in the flowchart and/or one or more boxes in the block diagram.

These computer program instructions may also be loaded onto a computer or other programmable data processing device so that a series of operational steps are executed on the computer or other programmable device to produce a computer-implemented process, whereby the instructions executed on the computer or other programmable device provide steps for implementing the functions specified in one or more processes in the flowchart and/or one or more boxes in the block diagram.

In a typical configuration, a computing device includes one or more processors (CPU), input/output interfaces, network interfaces, and memory.

Memory may include non-permanent storage in a computer-readable medium, in the form of random access memory (RAM) and/or non-volatile memory, such as read-only memory (ROM) or flash memory (flash RAM). Memory is an example of a computer-readable medium.

Computer readable media include permanent and non-permanent, removable and non-removable media that can be implemented by any method or technology to store information. Information can be computer readable instructions, data structures, program modules or other data. Examples of computer storage media include, but are not limited to, phase change memory (PRAM), static random access memory (SRAM), dynamic random access memory (DRAM), other types of random access memory (RAM), read-only memory (ROM), electrically erasable programmable read-only memory (EEPROM), flash memory or other memory technology, compact disk read-only memory (CD-ROM), digital versatile disk (DVD) or other optical storage, magnetic cassettes, magnetic tape magnetic disk storage or other magnetic storage devices or any other non-transmission media that can be used to store information that can be accessed by a computing device. As defined in this article, computer readable media does not include temporary computer readable media (transitory media), such as modulated data signals and carrier waves.

It should also be noted that the terms "include", "comprises" or any other variations thereof are intended to cover non-exclusive inclusion, so that a process, method, commodity or device including a series of elements includes not only those elements, but also other elements not explicitly listed, or also includes elements inherent to such process, method, commodity or device. In the absence of more restrictions, the elements defined by the sentence "comprises a ..." do not exclude the existence of other identical elements in the process, method, commodity or device including the elements.

This specification may be described in the general context of computer-executable instructions executed by a computer, such as program modules. Generally, program modules include routines, programs, objects, components, data structures, etc. that perform specific tasks or implement specific abstract data types. This specification may also be practiced in distributed computing environments where tasks are performed by remote processing devices connected through a communication network. In a distributed computing environment, program modules may be located in local and remote computer storage media, including storage devices.

Each embodiment in this specification is described in a progressive manner, and the same or similar parts between the embodiments can be referred to each other, and each embodiment focuses on the differences from other embodiments. In particular, for the therapeutic device and the use method embodiments, since they are basically similar to the method embodiments, the description is relatively simple, and the relevant parts can be referred to the partial description of the method embodiments.

The above is a description of a specific embodiment of the present specification. Other embodiments are within the scope of the appended claims. In some cases, the actions or steps recorded in the claims can be performed in an order different from that in the embodiments and still achieve the desired results. In addition, the processes depicted in the accompanying drawings do not necessarily require the specific order or continuous order shown to achieve the desired results. In some embodiments, multitasking and parallel processing are also possible or may be advantageous.

The above description is only one or more embodiments of this specification and is not intended to limit this specification. For those skilled in the art, one or more embodiments of this specification may have various changes and variations. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of one or more embodiments of this specification shall be included in the scope of the claims of this specification.

Claims (20)

A visual respiratory therapeutic device, characterized in that the therapeutic device comprises a host, a patient interface, and a patient status display screen; The main unit is provided with an air channel, an oxygen channel, an air-oxygen mixing portion and a mixed gas channel, and includes a flow sensor for monitoring the flow of the mixed gas and a pressure sensor for monitoring the pressure of the mixed gas; The inlet of the air-oxygen mixing part is connected to the air channel and the oxygen channel respectively, and the outlet of the air-oxygen mixing part is connected to the mixed gas channel; The patient interface is connected to the mixed gas channel through a pipeline; wherein the patient interface is a non-sealed patient interface; The host is used to receive and process the monitoring data of the flow sensor and the pressure sensor to output high-flow oxygen therapy display information to the patient status display screen; The patient status display screen includes a patient-end pressure dynamic display area and/or a patient inhalation flow dynamic display area, which are used to display the high-flow oxygen therapy display information. The visualized respiratory therapy device according to claim 1, characterized in that the therapy device further comprises a humidifier; The humidifier inlet is in gas communication with the mixed gas channel, and the humidifier outlet is in gas communication with the patient interface. The visualized respiratory therapy device according to claim 2 is characterized in that the patient interface is a nasal cannula, and the pipeline and the patient interface are an integrated or separate structure; the pipeline and the humidifier are detachably connected. The visualization respiratory therapy device according to claim 1 is characterized in that the patient status display screen also includes a patient capacity dynamic display area. The visualized respiratory therapy apparatus according to claim 4 is characterized in that the patient-end pressure dynamic display area, the patient inhalation flow dynamic display area, and the patient capacity dynamic display area are located on the same display interface. The visualized respiratory therapy apparatus according to claim 1 is characterized in that the oxygen channel also includes an oxygen source interface, an oxygen valve and an oxygen flow sensor for monitoring the oxygen flow. The visualized respiratory therapy apparatus according to claim 6, characterized in that the apparatus further comprises: an airflow controller; The airflow controller is connected to the oxygen valve and the air-oxygen mixing unit, and is used to generate an airflow control signal according to an adjustment instruction from a user interface, so as to control the oxygen valve and/or the air-oxygen mixing unit to adjust the output oxygen flow, oxygen concentration or mixed gas flow of the therapeutic device. The visualized respiratory therapy apparatus according to claim 7, characterized in that the air-oxygen mixing section comprises a turbine. A visualization processing method for a visualization respiratory therapeutic apparatus, characterized in that the method comprises: Based on the collected data corresponding to the pipeline verification operation and the delivery flow value of the mixed gas from the flow sensor, the patient interface pressure value of the current patient is determined through a preset pipeline pressure drop model; wherein the pipeline verification operation is that the patient interface is under atmospheric pressure, and multiple levels of step flow gas flow are output in sequence at intervals within a preset time; the collected data at least includes: the step flow values corresponding to the multiple levels of step flow, and the pressure values corresponding to each level of step flow; Based on the patient interface pressure value and the corresponding delivery flow value within a predetermined number of breaths of the current patient, and a preset pipeline output leakage model, the respiratory flow value of the current patient is determined in real time; Based on the patient interface pressure value and the respiratory flow value, high-flow oxygen therapy display information of the current patient is determined, and the high-flow oxygen therapy display information is sent to a patient status display screen to display the high-flow oxygen therapy display information. The method according to claim 9 is characterized in that, based on the collected data corresponding to the pipeline verification operation and the delivery flow value of the mixed gas from the flow sensor, the patient interface pressure value of the current patient is determined by a preset pipeline pressure drop model, specifically comprising: Generate a flow output control instruction according to the multi-level step flow, and send the flow output control instruction to the flow control device, so that the flow control device sequentially and intermittently outputs the airflow of the multi-level step flow within the preset time; wherein the sequentially and intermittently outputted airflow of each level of step flow is continuously output within each consecutive predetermined sub-time of the preset time; and the predetermined sub-time corresponds to each level of step flow in a one-to-one manner; Obtain the pressure values corresponding to each level of step flow from the pressure sensor; Determining the pipeline resistance coefficient of the pipeline pressure drop model based on the pressure values corresponding to the various levels of step flow and the corresponding step flow values; When the patient interface is connected to the ventilation end of the current patient, the patient interface pressure value of the current patient is determined according to the pipeline pressure drop model and the delivery pressure value and the delivery flow value from the pressure sensor. The method according to claim 10 is characterized in that, based on the pressure values corresponding to the various levels of step flow and the step flow values corresponding thereto, determining the pipeline resistance coefficient of the pipeline pressure drop model specifically includes: Establishing a linear equation group according to the pressure values corresponding to the stepped flow rates at each level, the multiple stepped flow values corresponding to the pressure values corresponding to the stepped flow rates at each level, and a preset formula; The least square solution of the linear equation group is calculated, and the least square solution is used as the pipeline resistance coefficient. The method according to claim 9 is characterized in that the respiratory flow value of the current patient is determined in real time based on the patient interface pressure value and the corresponding delivery flow value and a preset pipeline output leakage model within a predetermined number of breaths of the current patient, specifically comprising: According to the pipeline output leakage model, performing absolute value square root processing and sign function operation on the patient interface pressure value within a predetermined number of breaths of the current patient to obtain an intermediate pressure value; Performing integration operations on the intermediate amount of the pressure value and the delivery flow value respectively; Calculate the quotient of the intermediate amount of the pressure value after the integral operation and the delivery flow value after the integral operation, and use the quotient as a leakage model parameter of the pipeline output leakage model; Based on the leakage model parameters, the patient interface pressure value, the pipeline output leakage model and the delivery flow value, the respiratory flow value of the current patient is determined in real time. The method according to claim 12 is characterized in that, based on the patient interface pressure value and the corresponding delivery flow value and a preset pipeline output leakage model within a predetermined number of breaths of the current patient, the respiratory flow value of the current patient is determined in real time, and specifically further comprises: Identify the breathing trigger signal of the current patient, and accumulate the number of triggering times of the breathing trigger signal; When the triggering number is greater than or equal to the predetermined number, determining the patient interface pressure value and the corresponding delivery flow value in each breath; Determining the leakage model parameters based on the predetermined number of patient interface pressure values and the corresponding delivery flow values; Based on the leakage model parameters, the patient interface pressure value, the pipeline output leakage model and the delivery flow value, the respiratory flow value of the current patient is determined in real time. The method according to claim 13, characterized in that determining the leakage model parameters based on the predetermined number of patient interface pressure values and the corresponding delivery flow values specifically comprises: Determining a plurality of intermediate pressure values corresponding to the predetermined number of patient interface pressure values; and determining a plurality of said delivery flow values corresponding to a plurality of said intermediate pressure quantities; Performing integral summation operations on a plurality of intermediate pressure values and a plurality of delivery flow values respectively; Calculate the quotient of the intermediate quantities of the plurality of pressure values after integral summation and the plurality of delivery flow values after integral summation, and use the quotient as a leakage model parameter of the pipeline output leakage model; Based on the leakage model parameters, the patient interface pressure value, the pipeline output leakage model and the delivery flow value, the respiratory flow value of the current patient is determined in real time. The method according to claim 13, characterized in that after determining the leakage model parameters based on the predetermined number of patient interface pressure values and the corresponding delivery flow values, the method further comprises: When a breathing trigger signal of the current patient is identified, determining a cumulative starting point breath of the trigger times; According to the accumulated number of interval breathings between the starting breathing and the current breathing and the predetermined number, the accumulated starting breathing of the triggering number is updated to the Nth breathing after the accumulated starting breathing; N is a natural number; N is the difference between the interval breathing number and the predetermined number. The method according to claim 9 is characterized in that the high-flow oxygen therapy display information includes at least one or more of the following: patient interface pressure curve, respiratory flow curve, patient capacity curve, respiratory rate, tidal volume, minute ventilation, end-tidal pressure, peak inspiratory flow, and actual inspired oxygen concentration. The method according to claim 16, characterized in that the method further comprises: Determine a first airflow capacity and a second airflow capacity corresponding to each breath according to the respiratory flow value of each breath of the current patient and the corresponding delivery flow value; the first airflow capacity is the airflow capacity inhaled from the patient interface for each breath of the current patient; the second airflow capacity is the airflow capacity inhaled from the atmosphere for each breath of the current patient; Determining the total inhaled capacity according to the respiratory flow value of each breath of the current patient; Acquire oxygen flow data from an oxygen flow sensor, and determine output oxygen concentration based on the oxygen flow data; The output oxygen concentration, the first airflow capacity, the second airflow capacity, the preset atmospheric oxygen ratio and the total inhalation capacity are input into a preset inhaled oxygen concentration formula to calculate the actual inhaled oxygen concentration. A method for using a visualized respiratory therapy apparatus, characterized in that it is applied to the visualized respiratory therapy apparatus according to any one of claims 1 to 8, and the method for using the respiratory therapy apparatus comprises: A pipeline verification operation step of measuring the pipeline resistance coefficient between the patient interface and the pipeline after replacing the patient interface and/or the pipeline. The method for using the therapeutic apparatus according to claim 18 is characterized in that when measuring the pipeline resistance coefficient, the patient interface is directly connected to the atmosphere. The method for using the therapeutic apparatus according to claim 18 is characterized in that the pipeline verification operation includes the step of testing a multi-level step flow rate, specifically including: generating a flow output control instruction according to the multi-level step flow rate, and sending the flow output control instruction to the flow control device, so that the flow control device sequentially outputs an airflow of a multi-level step flow rate at intervals within a preset time; wherein the sequentially interval output of the airflow of each level of step flow rate is continuously output within each consecutive predetermined sub-time of the preset time; the predetermined sub-time corresponds one-to-one to each level of step flow rate; Obtain the pressure values corresponding to each level of step flow from the pressure sensor; Based on the pressure values corresponding to the various levels of step flow and the step flow values corresponding thereto, the pipeline resistance coefficient of the pipeline pressure drop model is determined.

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