A respiratory monitoring system, method, device, and storage medium
By drawing lung impedance waveforms and combining tidal volume and respiratory rate to determine minute ventilation, the problems of harm to the human body and low accuracy of existing respiratory monitoring technologies are solved, and efficient and accurate respiratory monitoring is achieved.
Patent Information
- Authority / Receiving Office
- CN · China
- Patent Type
- Patents(China)
- Current Assignee / Owner
- CORESPIRON(HENAN) CO LTD
- Filing Date
- 2023-07-11
- Publication Date
- 2026-05-19
AI Technical Summary
Existing respiratory measurement technologies have problems such as causing harm to patients or being cumbersome and easily affected, while optical imaging monitoring has low accuracy and is prone to false alarms.
By plotting lung impedance waveforms and combining tidal volume and respiratory rate to determine minute ventilation, respiratory monitoring can be performed using lung impedance data, avoiding harm to the human body and improving monitoring accuracy and efficiency.
It achieves improved accuracy and efficiency of respiratory monitoring without harming the human body, and reduces the impact of interference factors and false alarms.
Smart Images
Figure CN116889390B_ABST
Abstract
Description
Technical Field
[0001] This invention relates to the field of computer technology, and in particular to a respiratory monitoring system, method, device and storage medium. Background Technology
[0002] Breathing is one of the four vital signs in medicine. The most intuitive values are minute ventilation (MV), tidal volume (TV), and respiratory rate (RR). Minute ventilation is determined based on tidal volume and respiratory rate. As a comprehensive value, minute ventilation can directly observe the ventilation of the lungs. A low minute ventilation indicates that the lungs are inhaling too little air, which is insufficient to maintain the normal functioning of physiological signs.
[0003] Existing technologies for measuring respiratory values mainly focus on two aspects. One is monitoring the volume of gas involved in respiration. This method has significant drawbacks: patients need to be intubated or wear a breathing mask for gas volume measurement. The former is invasive and can harm the patient, while the latter is cumbersome and susceptible to various factors. The other method is optical imaging monitoring. This involves illuminating blood with light and observing the resulting images to determine the blood oxygen content, thus assessing respiratory status. However, this method has lower accuracy and is easily affected by various factors, leading to false respiratory readings. Summary of the Invention
[0004] In view of this, the purpose of this invention is to provide a respiratory monitoring system, method, device, and storage medium that can link lung impedance data with respiration and determine minute ventilation through tidal volume and respiratory rate for respiratory monitoring, thereby improving the accuracy and efficiency of respiratory monitoring without harming the human body. The specific solution is as follows:
[0005] In a first aspect, this application provides a respiratory monitoring system, comprising:
[0006] The waveform plotting module is used to plot lung impedance waveforms in real time based on the lung impedance data of the monitored subject collected in real time and the acquisition time corresponding to the lung impedance data.
[0007] A respiratory rate determination tool is used to determine the respiratory rate based on the number of peaks and troughs within a preset time period in the lung impedance waveform.
[0008] The tidal volume calculation tool is used to determine the average value of lung impedance data based on several target lung impedance data corresponding to the current breath in the lung impedance waveform, and to find the baseline tidal volume value corresponding to the average value of lung impedance data and the basic information of the monitored person from a preset database. Then, the preset tidal volume calculation formula is used to calculate the tidal volume corresponding to the current breath by using the average value of lung impedance data and the baseline tidal volume value.
[0009] The respiratory monitoring module is used to determine the minute ventilation based on the tidal volume corresponding to the current breath and the respiratory rate, and to perform respiratory monitoring on the monitored subject based on the minute ventilation.
[0010] Optionally, the system further includes:
[0011] The data acquisition interface is used to acquire the impedance data of the monitored object in real time through the impedance acquisition circuit.
[0012] The data filtering unit is used to filter the cardiac impedance data in the impedance data using a preset stroke volume calculation formula to obtain the lung impedance data of the monitored person in real time.
[0013] Optionally, the data acquisition interface includes:
[0014] The co-directional signal acquisition unit is used to connect a signal that meets a preset high-frequency condition to the body of the monitored person and acquire several co-directional signals acquired in real time from several corresponding signal acquisition points; the co-directional signal is two analog voltage signals acquired from two corresponding signal acquisition points on the human body; the distance between the two corresponding signal acquisition points is greater than at least half the length of the lung.
[0015] The analog-to-digital conversion unit is used to perform differential amplification on each of the in-phase signals using a differential amplifier circuit to obtain differential voltage signals, and to convert each of the differential voltage signals into digital voltage signals through full-wave rectification.
[0016] The impedance conversion submodule is used to sequentially limit and amplify each of the digital voltage signals to obtain amplified voltage signals, and to use the MCU to convert each of the amplified voltage signals to obtain the impedance data of the monitored object.
[0017] Optionally, the impedance conversion submodule includes:
[0018] The limit processing unit is used to perform limit processing on each of the digital voltage signals using a multiplication circuit based on an adjustable potentiometer and a multiplier, so as to obtain each limit-up voltage signal.
[0019] An amplification processing unit is used to amplify each of the limit voltage signals using a programmable gain amplifier to obtain each amplified voltage signal.
[0020] The impedance data conversion unit is used to perform statistical processing on each of the amplified voltage signals by the MCU to obtain a statistical voltage signal, and to convert the statistical voltage signal using a preset impedance conversion formula to obtain the impedance data of the monitored object.
[0021] Optionally, the respiratory rate determination tool includes:
[0022] A respiratory rate determination unit is used to determine the respiratory rate based on the number of peaks and troughs within a preset time period in the lung impedance waveform.
[0023] A respiratory rate determination unit is used to determine the corresponding respiratory rate based on the number of breaths and the preset time.
[0024] Optionally, the system further includes:
[0025] The information collection interface is used to obtain basic information of several volunteers, collect lung impedance data of the several volunteers, and collect tidal volume of the several volunteers at the same time through a ventilator.
[0026] The database construction unit is used to construct several corresponding relationships based on the basic information of the volunteers, the lung impedance data of the volunteers, and the tidal volume of the volunteers at the same time to obtain a preset database.
[0027] Optionally, the tidal volume calculation tool includes:
[0028] The average value determination unit is used to determine the average value of lung impedance data based on several target lung impedance data corresponding to the current breath in the lung impedance waveform diagram.
[0029] The baseline value lookup unit is used to look up the baseline tidal volume value corresponding to the average value of the lung impedance data and the baseline information of the monitored person from a preset database; the baseline information includes height, weight, gender and age;
[0030] The vector determination unit is used to determine a preset number of vectors based on the average value of the lung impedance data and the peak lung impedance data and trough lung impedance data corresponding to the current breath.
[0031] The tidal volume calculation unit is used to calculate the average value of the lung impedance data, the baseline value of the tidal volume, and the preset number of vectors using a preset tidal volume calculation formula, so as to obtain the tidal volume corresponding to the current breath.
[0032] Secondly, this application provides a respiratory monitoring method, including:
[0033] Lung impedance waveforms are plotted in real time based on the lung impedance data of the monitored subjects collected in real time and the acquisition time corresponding to the lung impedance data.
[0034] The respiratory rate is determined based on the number of peaks and troughs within a preset time period in the lung impedance waveform.
[0035] Based on several target lung impedance data corresponding to the current breath in the lung impedance waveform, the average lung impedance data is determined, and the baseline tidal volume value corresponding to the average lung impedance data and the basic information of the monitored person is found from the preset database. Then, the tidal volume corresponding to the current breath is calculated by using the preset tidal volume calculation formula to calculate the average lung impedance data and the baseline tidal volume value.
[0036] Minute ventilation is determined based on the tidal volume corresponding to the current breath and the respiratory rate, and respiratory monitoring is performed on the subject based on the minute ventilation.
[0037] Thirdly, this application provides an electronic device, comprising:
[0038] Memory, used to store computer programs;
[0039] A processor for executing the computer program to implement the aforementioned respiratory monitoring method.
[0040] Fourthly, this application provides a computer-readable storage medium for storing a computer program that, when executed by a processor, implements the aforementioned respiratory monitoring method.
[0041] In this application, a waveform plotting module is used to plot a lung impedance waveform in real time based on the lung impedance data of the monitored subject collected in real time and the acquisition time corresponding to the lung impedance data; a respiratory rate determination tool is used to determine the respiratory rate based on the number of peaks and troughs within a preset time period in the lung impedance waveform; a tidal volume calculation tool is used to determine the average value of lung impedance data based on several target lung impedance data corresponding to the current breath in the lung impedance waveform, and to find the baseline tidal volume value corresponding to the average value of lung impedance data and the basic information of the monitored subject from a preset database, and then calculate the tidal volume corresponding to the current breath using a preset tidal volume calculation formula; and a respiratory monitoring module is used to determine the minute ventilation based on the tidal volume corresponding to the current breath and the respiratory rate, and to perform respiratory monitoring on the monitored subject based on the minute ventilation. Therefore, this application links the lung impedance data of the monitored subject with respiration. The lung impedance waveform can reflect the respiratory trajectory of the monitored subject in real time. Based on the real-time lung impedance waveform, the respiratory rate and the tidal volume corresponding to the current breath can be determined. The minute ventilation determined based on the tidal volume and respiratory rate corresponding to the current breath can be used to monitor the subject's respiration. This can improve the accuracy and efficiency of respiratory monitoring without harming the human body and alleviate the problems of susceptibility to other interference factors and false alarms. Attached Figure Description
[0042] To more clearly illustrate the technical solutions in the embodiments of the present invention or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on the provided drawings without creative effort.
[0043] Figure 1 This is a schematic diagram of the device structure of a respiratory monitoring system disclosed in this application;
[0044] Figure 2 This application discloses a lung impedance waveform.
[0045] Figure 3 This is a flowchart of a respiratory monitoring method disclosed in this application;
[0046] Figure 4 This is a structural diagram of an electronic device disclosed in this application. Detailed Implementation
[0047] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.
[0048] Existing technologies for measuring respiratory values mainly focus on two aspects. One is monitoring the volume of gas involved in respiration. This requires intubation or a breathing mask for measurement; the former is invasive and can harm the patient, while the latter is cumbersome and susceptible to various factors. The other method is optical imaging, which involves irradiating blood with light and observing the resulting images to determine the blood oxygen content, thus assessing respiratory status. However, this method has low accuracy and is easily affected by various factors, leading to false respiratory reports. Therefore, this application provides a respiratory monitoring system that links lung impedance data with respiration and determines minute ventilation through tidal volume and respiratory rate for respiratory monitoring. This system can improve the accuracy and efficiency of respiratory monitoring without harming the human body.
[0049] See Figure 1 As shown, an embodiment of the present invention discloses a respiratory monitoring system, comprising:
[0050] The waveform drawing module 11 is used to draw a lung impedance waveform in real time based on the lung impedance data of the monitored subject collected in real time and the acquisition time corresponding to the lung impedance data.
[0051] In this embodiment, the respiratory monitoring system further includes: a data acquisition interface for real-time acquisition of impedance data of the monitored subject through an impedance acquisition circuit; and a data filtering unit for filtering cardiac impedance data in the impedance data using a preset stroke volume calculation formula to obtain real-time lung impedance data of the monitored subject. Considering that the heart has diastolic and systolic phases, commonly known as cardiac cycles, during its operation, cardiac impedance waveforms are generated during the alternation of these cycles. However, this signal can interfere with the acquisition of lung impedance signals. Therefore, continuous cardiac impedance data needs to be removed from the total impedance data to ensure that subsequent respiratory parameter calculations are not erroneous due to cardiac noise. Therefore, the impedance data of the monitored subject is first acquired in real-time through the impedance acquisition circuit. Then, the impedance data is filtered using the Kubicek formula by recording the cardiac cycle to remove irrelevant impedance data generated by heartbeats. The remaining impedance data is the real-time lung impedance data of the monitored subject. Then, based on the real-time acquired lung impedance data of the monitored subjects and the corresponding acquisition time, a lung impedance waveform is plotted in real time. The lung impedance waveform is shown below. Figure 2 As shown in the figure. In this way, the respiratory trajectory of the monitored person can be reflected in real time through the lung impedance waveform, which has excellent real-time performance in characterizing the monitored person's breathing. Moreover, doctors can make a relatively accurate and timely judgment on the monitored person's breathing status through the respiratory trajectory.
[0052] The respiratory rate determination tool 12 is used to determine the respiratory rate based on the number of peaks and troughs within a preset time period in the lung impedance waveform.
[0053] In this embodiment, the respiratory rate determination tool 12 includes: a respiratory count determination unit, used to determine the respiratory count based on the number of peaks and troughs within a preset time period in the lung impedance waveform; and a respiratory rate determination unit, used to determine the corresponding respiratory rate based on the respiratory count and the preset time period. Considering that respiratory movements are accompanied by periodic changes in thoracic cavity volume, which inevitably cause regular changes in lung impedance values, and that the resistivity of gas is much greater than that of other tissues, and even greater than that of blood, inhalation causes an increase in thoracic cavity volume, leading to an increase in lung gas volume and thus an increase in lung impedance. Exhalation causes a decrease in thoracic cavity volume, leading to a decrease in lung gas volume and thus a decrease in lung impedance. Therefore, lung impedance values can indirectly reflect the working condition of the lungs. Furthermore, as... Figure 2As shown, in the lung impedance waveform, the arrival of a peak at a trough is considered the end of one expiration, and the arrival of a trough at a peak is considered the end of one inhalation. Two such arrivals indicate the completion of one respiratory movement. The respiratory rate (RR) is defined as the number of respiratory movements completed in one minute. Specifically, it is calculated by determining the number of breaths within a specific time period based on the number of peaks and troughs, and then calculating the respiratory rate based on the number of breaths and the specific time.
[0054] The tidal volume calculation tool 13 is used to determine the average value of lung impedance data based on several target lung impedance data corresponding to the current breath in the lung impedance waveform, and to find the baseline tidal volume value corresponding to the average value of lung impedance data and the basic information of the monitored person from a preset database. Then, the preset tidal volume calculation formula is used to calculate the tidal volume corresponding to the current breath by using the average value of lung impedance data and the baseline tidal volume value.
[0055] In this embodiment, the respiratory monitoring system further includes: an information acquisition interface for acquiring basic information of several volunteers, acquiring lung impedance data of the volunteers, and acquiring tidal volume of the volunteers at the same time using a ventilator; and a database construction unit for constructing several corresponding relationships based on the basic information of the volunteers, the lung impedance data of the volunteers, and the tidal volume of the volunteers at the same time to obtain a preset database. It is understood that acquiring basic information of a large number of volunteers includes, but is not limited to, height, weight, age, and gender. Acquiring lung impedance data of a large number of volunteers, simultaneously connecting a ventilator to collect tidal volume data from a large number of volunteers, and then comparing the lung impedance data and tidal volume according to the acquisition time to form a correspondence between the volunteers' basic information, lung impedance data, and tidal volume at the same time to obtain the preset database.
[0056] In this embodiment, the tidal volume calculation tool includes: an average value determination unit, used to determine the average value of lung impedance data based on several target lung impedance data corresponding to the current breath in the lung impedance waveform; a baseline value lookup unit, used to look up the baseline tidal volume value corresponding to the average lung impedance data and the baseline information of the monitored person from a preset database; the baseline information includes height, weight, gender, and age; a vector determination unit, used to determine a preset number of vectors based on the average lung impedance data and the peak and trough lung impedance data corresponding to the current breath; and a tidal volume calculation unit, used to calculate the average lung impedance data, the baseline tidal volume value, and the preset number of vectors using a preset tidal volume calculation formula to obtain the tidal volume corresponding to the current breath. Understandably, the process begins by averaging multiple target lung impedance data points corresponding to the current breath in the lung impedance waveform to obtain the average lung impedance data R. Then, using the average lung impedance data R and the subject's baseline information, including height, weight, age, and gender, a corresponding baseline tidal volume value (TVbase) is retrieved from a pre-set database. Further, the average lung impedance data R is subtracted from the peak and trough lung impedance data corresponding to the current breath, resulting in four vectors: R1 (two positive) and R2 (two negative), R3 (two negative). Finally, a pre-set tidal volume calculation formula is used to calculate the average lung impedance data R, the baseline tidal volume value (TVbase), and the four vectors R1, R2, R3, and R4 to obtain the tidal volume (TV) corresponding to the current breath. The pre-set tidal volume calculation formula is as follows:
[0057]
[0058] It should be noted that the four vectors R1, R2, R3, and R4 are the offsets of the lung impedance data corresponding to the current breath relative to the average lung impedance data R. Calculating the offsets can yield the change in lung ventilation based on the tidal volume baseline value TVbase. Summing up the change values gives the tidal volume TV corresponding to the current breath.
[0059] The respiratory monitoring module 14 is used to determine the minute ventilation based on the tidal volume corresponding to the current breath and the respiratory rate, and to perform respiratory monitoring on the monitored person based on the minute ventilation.
[0060] In this embodiment, the tidal volume corresponding to the current breath is obtained by multiplying the gas flux of the current breath by the respiratory rate. The minute ventilation corresponding to the current breath is then calculated based on the minute ventilation. The normal minute ventilation is generally 6-9 L. A normal adult in a resting state has a respiratory rate of 12-18 breaths / min, a tidal volume of 500 ml, and a minute ventilation of 6-9 L. A minute ventilation greater than 10 L / min may indicate hyperventilation and respiratory alkalosis; a minute ventilation less than 3 L / min indicates hypoventilation and may indicate respiratory acidosis.
[0061] Therefore, this application links the lung impedance data of the monitored subject with respiration. The lung impedance waveform can reflect the respiratory trajectory of the monitored subject in real time. Based on the real-time lung impedance waveform, the respiratory rate and the tidal volume corresponding to the current breath can be determined. The minute ventilation determined based on the tidal volume and respiratory rate corresponding to the current breath can be used to monitor the subject's respiration. This can improve the accuracy and efficiency of respiratory monitoring without harming the human body and alleviate the problems of susceptibility to other interference factors and false alarms.
[0062] Based on any of the above embodiments, the data acquisition interface includes:
[0063] The co-directional signal acquisition unit is used to connect a signal that meets a preset high-frequency condition to the body of the monitored person and acquire several co-directional signals acquired in real time from several corresponding signal acquisition points; the co-directional signal is two analog voltage signals acquired from two corresponding signal acquisition points on the human body; the distance between the two corresponding signal acquisition points is greater than at least half the length of the lung.
[0064] The analog-to-digital conversion unit is used to perform differential amplification on each of the in-phase signals using a differential amplifier circuit to obtain differential voltage signals, and then convert each of the differential voltage signals into digital voltage signals through full-wave rectification.
[0065] The impedance conversion submodule is used to sequentially limit and amplify each of the digital voltage signals to obtain amplified voltage signals, and to use the MCU to convert each of the amplified voltage signals to obtain the impedance data of the monitored object.
[0066] In this embodiment, the generation of a signal that meets the preset high-frequency conditions can be achieved through a combination of electronic components and circuits. Specifically, the SN74LV4046AN chip can be selected as a specific electronic component. The SN74LV4046AN chip is a device capable of generating various waveform signals. It can adjust the signal using external control resistors and capacitors to generate a signal with a frequency of 50kHz and an amplitude of approximately 5V. After signal generation, the signal undergoes feedback processing by an operational amplifier to control the amplitude between -2.5V and +2.5V. Finally, a resistor circuit reduces the signal to a high-frequency constant current signal with an amplitude of approximately 2V. This high-frequency constant current signal is then connected to the signal output terminal, and a transient suppressor is added at the signal output terminal to ensure that the signal does not exhibit spikes. The signal is then connected to the body of the monitored individual, thereby protecting their safety.
[0067] In this embodiment, a signal meeting a preset high-frequency condition is input into the subject's body to form a loop. The same-direction signal returned from the loop is input into a differential amplifier circuit. Multiple same-direction signals can be used, and each signal refers to two analog voltage signals acquired from two corresponding signal acquisition points on the body. The distance between the two corresponding signal acquisition points should be greater than at least half the length of the lung. Then, the differential amplifier circuit performs differential amplification on each same-direction signal to obtain differential voltage signals from the lungs. Differential processing causes the differential voltage signals to change with lung respiration; amplification is performed because signals that are too small to be observed are not suitable for observation. Then, full-wave rectification converts each differential voltage signal into a digital voltage signal. Each digital voltage signal is then subjected to limiting and amplification operations to obtain amplified voltage signals. Finally, an MCU (Microcontroller Unit) converts each amplified voltage signal into a stable value that reflects subtle changes in lung impedance.
[0068] Therefore, this embodiment uses a differential amplifier circuit to differentially amplify each in-phase signal to avoid the problem of excessively small voltage signal amplitude changes. Furthermore, it uses full-wave rectification to convert each differential voltage signal into a digital voltage signal, making it easier and more intuitive to observe the changes in the voltage signal.
[0069] Based on any of the above embodiments, the impedance conversion submodule includes:
[0070] The limit processing unit is used to perform limit processing on each of the digital voltage signals using a multiplication circuit based on an adjustable potentiometer and a multiplier, so as to obtain each limit-up voltage signal.
[0071] An amplification processing unit is used to amplify each of the limit voltage signals using a programmable gain amplifier to obtain amplified voltage signals.
[0072] The impedance data conversion unit is used to perform statistical processing on each of the amplified voltage signals by the MCU to obtain a statistical voltage signal, and to convert the statistical voltage signal using a preset impedance conversion formula to obtain the impedance data of the monitored object.
[0073] In this embodiment, since MCU microcontrollers typically only accept voltages between 0-5V, the amplitude of the voltage signal input to the MCU must be controlled within this range; otherwise, the voltage signal cannot be accurately converted into impedance data. For any digital voltage signal, a multiplication circuit based on an adjustable potentiometer and a high-precision analog multiplier can be used to limit the signal. Using the digital voltage signal as the numerator and the voltage of the adjustable potentiometer as the denominator, the output is the limit-processed digital voltage signal, i.e., the voltage signal after limit processing. The voltage signal after limit processing exhibits a small amplitude change due to breathing, making subsequent calculations difficult. Therefore, amplification is required. A programmable gain amplifier amplifies the limit-processed voltage signal, resulting in an amplified voltage signal that changes by approximately 2V with breathing. The formula for the programmable gain amplifier is Vvar = (Vinput - Vref) * gain + Vref, where Vinput represents the limit-processed voltage signal, Vref represents the amplifier's reference voltage, gain represents the amplifier's amplification factor, and Vvar represents the amplified voltage signal.
[0074] In this embodiment, each amplified voltage signal is input to the MCU to first perform statistical processing on the amplified voltage signals to obtain a statistically derived voltage signal. This statistical processing includes, but is not limited to, weighting and averaging. Then, a preset impedance transformation formula is used to transform the statistically derived voltage signal to obtain the impedance data of the monitored object. The preset impedance transformation formula is as follows:
[0075] R1 = (Vvar - Vref) / gain
[0076]
[0077] R3=R2 / (PGAcorrection+POW(MPYvalue,MPYcorrection))
[0078] It should be noted that Vvar represents the amplified voltage signal, Vref represents the amplifier's reference voltage, gain represents the amplifier's amplification factor, R1 and R2 represent intermediate parameters, Voffset represents the amplifier's bias voltage, GainDIF represents the differential amplification factor, PGAcorrection and MPYcorrection represent correction factors derived from the PCB (Printed Circuit Board) error, MPYvalue represents the potentiometer's offset index, POW represents the exponent calculation function, and R3 represents the impedance data.
[0079] Therefore, this embodiment utilizes a multiplication circuit based on an adjustable potentiometer and a multiplier to limit each digital voltage signal, preventing the amplitude of the voltage signal input to the MCU from exceeding the range, thus ensuring that the voltage signal input to the MCU can undergo impedance conversion normally. Furthermore, a programmable gain amplifier is used to amplify each limited voltage signal, avoiding the problem of difficulty in subsequent impedance data calculation caused by the small amplitude of the voltage signal change after the limit. In addition, the MCU converts each amplified voltage signal into impedance data so that the impedance data can reflect the breathing status of the monitored person.
[0080] The above embodiments provide a detailed description of the function of each module in this application. They can link lung impedance data with respiration and determine minute ventilation through tidal volume and respiratory rate for respiratory monitoring, thereby improving the accuracy and efficiency of respiratory monitoring without harming the human body. The following embodiments will introduce a respiratory monitoring method. See [link to documentation]. Figure 3 As shown, an embodiment of the present invention discloses a respiratory monitoring method, comprising:
[0081] Step S11: Based on the real-time acquired lung impedance data of the monitored subject and the acquisition time corresponding to the lung impedance data, draw a lung impedance waveform diagram in real time.
[0082] Step S12: Determine the respiratory rate based on the number of peaks and troughs within a preset time period in the lung impedance waveform.
[0083] Step S13: Determine the average value of lung impedance data based on several target lung impedance data corresponding to the current breath in the lung impedance waveform diagram, and find the baseline tidal volume value corresponding to the average value of lung impedance data and the basic information of the monitored person from the preset database. Then, use the preset tidal volume calculation formula to calculate the tidal volume corresponding to the current breath by calculating the average value of lung impedance data and the baseline tidal volume value.
[0084] Step S14: Determine the minute ventilation based on the tidal volume corresponding to the current breath and the respiratory rate, and perform respiratory monitoring on the subject based on the minute ventilation.
[0085] Therefore, this application links the lung impedance data of the monitored subject with respiration. The lung impedance waveform can reflect the respiratory trajectory of the monitored subject in real time. Based on the real-time lung impedance waveform, the respiratory rate and the tidal volume corresponding to the current breath can be determined. The minute ventilation determined based on the tidal volume and respiratory rate corresponding to the current breath can be used to monitor the subject's respiration. This can improve the accuracy and efficiency of respiratory monitoring without harming the human body and alleviate the problems of susceptibility to other interference factors and false alarms.
[0086] Furthermore, embodiments of this application also disclose an electronic device, Figure 4 This is a structural diagram of an electronic device 20 according to an exemplary embodiment. The content of the diagram should not be construed as limiting the scope of this application.
[0087] Figure 4 This is a schematic diagram of the structure of an electronic device 20 provided in an embodiment of this application. Specifically, the electronic device 20 may include: at least one processor 21, at least one memory 22, a power supply 23, a communication interface 24, an input / output interface 25, and a communication bus 26. The memory 22 stores a computer program, which is loaded and executed by the processor 21 to implement the relevant steps in the respiratory monitoring method disclosed in any of the foregoing embodiments. Furthermore, the electronic device 20 in this embodiment may specifically be an electronic computer.
[0088] In this embodiment, the power supply 23 is used to provide operating voltage for each hardware device on the electronic device 20; the communication interface 24 can create a data transmission channel between the electronic device 20 and external devices, and the communication protocol it follows can be any communication protocol applicable to the technical solution of this application, and is not specifically limited here; the input / output interface 25 is used to acquire external input data or output data to the outside world, and its specific interface type can be selected according to specific application needs, and is not specifically limited here.
[0089] In addition, the memory 22, as a carrier for resource storage, can be a read-only memory, random access memory, disk or optical disk, etc. The resources stored thereon can include operating system 221, computer program 222, etc., and the storage method can be temporary storage or permanent storage.
[0090] The operating system 221 is used to manage and control the various hardware devices on the electronic device 20 and the computer program 222, which may be Windows Server, Netware, Unix, Linux, etc. In addition to including a computer program capable of performing the respiratory monitoring method executed by the electronic device 20 as disclosed in any of the foregoing embodiments, the computer program 222 may further include a computer program capable of performing other specific tasks.
[0091] Furthermore, this application also discloses a computer-readable storage medium for storing a computer program; wherein, when the computer program is executed by a processor, it implements the aforementioned disclosed respiratory monitoring method. Specific steps of this method can be found in the corresponding content disclosed in the foregoing embodiments, and will not be repeated here.
[0092] The various embodiments in this specification are described in a progressive manner, with each embodiment focusing on its differences from other embodiments. Similar or identical parts between embodiments can be referred to interchangeably. For the apparatus disclosed in the embodiments, since it corresponds to the method disclosed in the embodiments, the description is relatively simple; relevant parts can be referred to in the method section.
[0093] Those skilled in the art will further recognize that the units and algorithm steps of the various examples described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, computer software, or a combination of both. To clearly illustrate the interchangeability of hardware and software, the components and steps of the various examples have been generally described in terms of functionality in the foregoing description. Whether these functions are implemented in hardware or software depends on the specific application and design constraints of the technical solution. Those skilled in the art can use different methods to implement the described functions for each specific application, but such implementation should not be considered beyond the scope of this application.
[0094] The steps of the methods or algorithms described in conjunction with the embodiments disclosed herein can be implemented directly by hardware, a software module executed by a processor, or a combination of both. The software module can be located in random access memory (RAM), main memory, read-only memory (ROM), electrically programmable ROM, electrically erasable programmable ROM, registers, hard disk, removable disk, CD-ROM, or any other form of storage medium known in the art.
[0095] Finally, it should be noted that in this document, relational terms such as "first" and "second" are used only to distinguish one entity or operation from another, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Furthermore, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, method, article, or apparatus. Without further limitations, an element defined by the phrase "comprising one..." does not exclude the presence of other identical elements in the process, method, article, or apparatus that includes said element.
[0096] The technical solutions provided in this application have been described in detail above. Specific examples have been used to illustrate the principles and implementation methods of this application. The descriptions of the above embodiments are only for the purpose of helping to understand the methods and core ideas of this application. At the same time, for those skilled in the art, there will be changes in the specific implementation methods and application scope based on the ideas of this application. Therefore, the content of this specification should not be construed as a limitation of this application.
Claims
1. A respiratory monitoring system, characterized in that, include: The waveform plotting module is used to plot lung impedance waveforms in real time based on the lung impedance data of the monitored subject collected in real time and the acquisition time corresponding to the lung impedance data. A respiratory rate determination tool is used to determine the respiratory rate based on the number of peaks and troughs within a preset time period in the lung impedance waveform. The tidal volume calculation tool is used to determine the average value of lung impedance data based on several target lung impedance data corresponding to the current breath in the lung impedance waveform, and to find the baseline tidal volume value corresponding to the average value of lung impedance data and the basic information of the monitored person from a preset database. Then, the preset tidal volume calculation formula is used to calculate the tidal volume corresponding to the current breath by using the average value of lung impedance data and the baseline tidal volume value. A respiratory monitoring module is used to determine minute ventilation based on the tidal volume corresponding to the current breath and the respiratory rate, and to perform respiratory monitoring on the monitored subject based on the minute ventilation. The tidal volume calculation tool includes: The average value determination unit is used to determine the average value of lung impedance data based on several target lung impedance data corresponding to the current breath in the lung impedance waveform diagram. The baseline value lookup unit is used to look up the baseline tidal volume value corresponding to the average value of the lung impedance data and the baseline information of the monitored person from a preset database; the baseline information includes height, weight, gender and age; The vector determination unit is used to determine a preset number of vectors based on the average value of the lung impedance data and the peak lung impedance data and trough lung impedance data corresponding to the current breath; the preset number of vectors includes subtracting the average value of the lung impedance data from the peak lung impedance data and trough lung impedance data corresponding to the current breath to obtain four vectors with two positive and two negative values. The tidal volume calculation unit is used to calculate the average value of the lung impedance data, the baseline value of the tidal volume, and the preset number of vectors using a preset tidal volume calculation formula, so as to obtain the tidal volume corresponding to the current breath. The formula for calculating the preset tidal volume is as follows: ； TV represents the tidal volume corresponding to the current breath, TVbase represents the baseline value of the tidal volume, R represents the average value of the lung impedance data, and R1, R2, R3, and R4 all represent vectors.
2. The respiratory monitoring system according to claim 1, characterized in that, Also includes: The data acquisition interface is used to acquire the impedance data of the monitored object in real time through the impedance acquisition circuit. The data filtering unit is used to filter the cardiac impedance data in the impedance data using a preset stroke volume calculation formula to obtain the lung impedance data of the monitored person in real time.
3. The respiratory monitoring system according to claim 2, characterized in that, The data acquisition interface includes: The co-directional signal acquisition unit is used to connect a signal that meets a preset high-frequency condition to the body of the monitored person and acquire several co-directional signals acquired in real time from several corresponding signal acquisition points; the co-directional signal is two analog voltage signals acquired from two corresponding signal acquisition points on the human body; the distance between the two corresponding signal acquisition points is greater than at least half the length of the lung. The analog-to-digital conversion unit is used to perform differential amplification on each of the in-phase signals using a differential amplifier circuit to obtain differential voltage signals, and to convert each of the differential voltage signals into digital voltage signals through full-wave rectification. The impedance conversion submodule is used to sequentially limit and amplify each of the digital voltage signals to obtain amplified voltage signals, and to use the MCU to convert each of the amplified voltage signals to obtain the impedance data of the monitored object.
4. The respiratory monitoring system according to claim 3, characterized in that, The impedance conversion submodule includes: The limit processing unit is used to perform limit processing on each of the digital voltage signals using a multiplication circuit based on an adjustable potentiometer and a multiplier, so as to obtain each limit-up voltage signal. An amplification processing unit is used to amplify each of the limit voltage signals using a programmable gain amplifier to obtain each amplified voltage signal. The impedance data conversion unit is used to perform statistical processing on each of the amplified voltage signals by the MCU to obtain a statistical voltage signal, and to convert the statistical voltage signal using a preset impedance conversion formula to obtain the impedance data of the monitored object.
5. The respiratory monitoring system according to claim 1, characterized in that, The respiratory rate determination tool includes: A respiratory rate determination unit is used to determine the respiratory rate based on the number of peaks and troughs within a preset time period in the lung impedance waveform. A respiratory rate determination unit is used to determine the corresponding respiratory rate based on the number of breaths and the preset time.
6. The respiratory monitoring system according to claim 1, characterized in that, Also includes: The information collection interface is used to obtain basic information of several volunteers, collect lung impedance data of the several volunteers, and collect tidal volume of the several volunteers at the same time through a ventilator. The database construction unit is used to construct several corresponding relationships based on the basic information of the volunteers, the lung impedance data of the volunteers, and the tidal volume of the volunteers at the same time to obtain a preset database.
7. A respiratory monitoring method, characterized in that, include: Lung impedance waveforms are plotted in real time based on the lung impedance data of the monitored subjects collected in real time and the acquisition time corresponding to the lung impedance data. The respiratory rate is determined based on the number of peaks and troughs within a preset time period in the lung impedance waveform. The average lung impedance data is determined based on several target lung impedance data corresponding to the current breath in the lung impedance waveform. The baseline tidal volume value corresponding to the average lung impedance data and the basic information of the monitored person is found from a preset database. Then, the tidal volume corresponding to the current breath is calculated by using a preset tidal volume calculation formula on the average lung impedance data and the baseline tidal volume value. The basic information includes height, weight, gender and age. Minute ventilation is determined based on the tidal volume corresponding to the current breath and the respiratory rate, and respiratory monitoring of the subject is performed based on the minute ventilation. The step of calculating the tidal volume corresponding to the current breath using a preset tidal volume calculation formula by combining the average lung impedance data and the baseline tidal volume value includes: Based on the average value of the lung impedance data and the peak and trough lung impedance data corresponding to the current breath, a preset number of vectors are determined; the preset number of vectors includes subtracting the average value of the lung impedance data from the peak and trough lung impedance data corresponding to the current breath to obtain four vectors, two positive and two negative. The average value of the lung impedance data, the baseline value of the tidal volume, and the preset number of vectors are calculated using a preset tidal volume calculation formula to obtain the tidal volume corresponding to the current breath. The formula for calculating the preset tidal volume is as follows: ； TV represents the tidal volume corresponding to the current breath, TVbase represents the baseline value of the tidal volume, R represents the average value of the lung impedance data, and R1, R2, R3, and R4 all represent vectors.
8. An electronic device, characterized in that, include: Memory, used to store computer programs; A processor for executing the computer program to implement the respiratory monitoring method as described in claim 7.
9. A computer-readable storage medium, characterized in that, Used to store a computer program, which, when executed by a processor, implements the respiratory monitoring method as described in claim 7.