Multi-respiration mechanical state monitoring method and device for electrical impedance tomography

Abstract

The invention relates to a multi-respiration mechanical state monitoring method and device for electrical impedance tomography. The method comprises the following steps: acquiring an analog physiological signal of a user based on a multi-channel acquisition unit; performing data processing and analog-to-digital conversion on the analog physiological signal to obtain a digital physiological signal; the digital physiological signals are packaged, and obtained packaged digital physiological data are sent to an electrical impedance tomography device, so that the electrical impedance tomography device performs conjoint analysis on the breathing state of the user based on the electrical impedance tomography data collected by the electrical impedance tomography device and the received packaged digital physiological data. A breathing state analysis result is obtained; compared with the prior art, the technical scheme of the invention breaks through the limitation of a specific communication protocol by collecting, processing, packaging and transmitting the analog physiological signal, realizes the universal joint monitoring of the electrical impedance tomography equipment and the respirator, and improves the comprehensiveness and accuracy of the subsequent breathing state analysis.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of medical equipment processing, and in particular to a multi-respiratory mechanics state monitoring method and device for electrical impedance tomography. BACKGROUND

[0002] As an image technology for non-invasive, real-time and dynamic monitoring of lung ventilation and perfusion distribution, the electrical impedance tomography device needs to be used in cooperation with a ventilator to realize joint analysis in clinical application. By acquiring airway pressure, esophageal pressure, gastric pressure and other respiratory mechanics parameters, and combining the image analysis results of the electrical impedance tomography device itself, the respiratory state of a patient is comprehensively evaluated.

[0003] In the prior art, the connection of the electrical impedance tomography device and the ventilator mainly relies on a specific communication protocol, and only a specific brand or model of ventilator can be adapted to complete the transmission and joint analysis of respiratory mechanics parameters.

[0004] However, the electrical impedance tomography device mainly functions as imaging, and has weak structural imaging capability. The monitoring of the electrical impedance tomography device alone cannot meet the demand of clinical quantitative parameters, and must be combined with respiratory mechanics and other quantitative devices for auxiliary diagnosis. However, the existing joint method lacks a standardized solution. The connection of the electrical impedance tomography device and the ventilator relies on a specific communication protocol, and only a specific model of ventilator can be adapted, which limits the universality of the device. If the newly launched ventilator does not integrate the corresponding protocol, it cannot be compatible. At the same time, the traditional electrical impedance tomography device lacks real-time acquisition and processing capability for multi-channel respiratory mechanics signals, the monitoring index is single, and the system integration is low. The electrical impedance tomography device and the ventilator need multiple physical connections, which increases the complexity of clinical operation. SUMMARY

[0005] The present application provides a multi-respiratory mechanics state monitoring method and device for electrical impedance tomography, which breaks through the limitation of a specific communication protocol by simulating physiological signal acquisition, processing and encapsulation transmission, realizes the universal joint monitoring of the electrical impedance tomography device and the ventilator, and improves the comprehensiveness and accuracy of subsequent respiratory state analysis.

[0006] In a first aspect, the present application provides a multi-respiratory mechanics state monitoring method for electrical impedance tomography, comprising: acquiring analog physiological signals of a user based on a multi-channel acquisition unit; performing data processing and analog-to-digital conversion on the analog physiological signals to obtain digital physiological signals; performing encapsulation processing on the digital physiological signals, and sending the obtained encapsulated digital physiological data to an electrical impedance tomography device, so that the electrical impedance tomography device performs joint analysis on the respiratory state of the user based on electrical impedance tomography data collected by itself and the received encapsulated digital physiological data, to obtain a respiratory state analysis result.

[0007] In one possible implementation, the user's simulated physiological signals are acquired based on a multi-channel acquisition unit, specifically including: the multi-channel acquisition unit includes an airway pressure sensor, an esophageal pressure sensor, a gastric pressure sensor, and a flow sensor; based on the airway pressure sensor, the user's simulated airway pressure signal is acquired; based on the esophageal pressure sensor, the user's simulated esophageal pressure signal is acquired; based on the gastric pressure sensor, the user's simulated gastric pressure signal is acquired; based on the flow sensor, the simulated gas flow rate signal provided by the ventilator to the user is acquired; wherein the airway pressure sensor, the esophageal pressure sensor, the gastric pressure sensor, and the flow sensor are respectively connected to the airway pressure monitoring channel, the esophageal pressure monitoring channel, the gastric pressure monitoring channel, and the gas flow rate monitoring channel of the ventilator used by the user.

[0008] In one possible implementation, the simulated physiological signal is processed and converted from analog to digital to obtain a digital physiological signal. Specifically, this includes: performing low-pass filtering on the simulated physiological signal to obtain a filtered simulated physiological signal, adjusting the gain of the filtered simulated physiological signal to obtain an adjusted simulated physiological signal, and performing analog-to-digital conversion on the adjusted simulated physiological signal to obtain a data physiological signal.

[0009] In one possible implementation, the digital physiological signal is encapsulated and the resulting encapsulated digital physiological data is sent to the electrical impedance tomography (EIT) device. Specifically, this includes: synchronizing the digital physiological signal with a timestamp; converting the synchronized digital physiological signal into a target format digital physiological signal; encapsulating the target format digital physiological signal based on a common communication protocol to obtain encapsulated digital physiological data; and sending the encapsulated digital physiological data to the EIT device based on a standard data interface.

[0010] In one possible implementation, the electrical impedance tomography (EIT) device performs a joint analysis of the user's respiratory state based on its own acquired EIT data and the received encapsulated digital physiological data to obtain respiratory state analysis results. Specifically, this includes: acquiring EIT data; wherein the EIT data is obtained by the EIT device itself and includes global impedance, left lung impedance, and right lung impedance; decapsulating the received encapsulated digital physiological data to obtain decapsulated digital physiological data, wherein the decapsulated digital physiological data includes digital airway pressure signals, digital esophageal pressure signals, and digital gas flow rate signals; calculating corrected alveolar pressure data based on the digital airway pressure signals and the digital gas flow rate signals; calculating transpulmonary pressure data based on the digital airway pressure signals and the digital esophageal pressure signals; calculating global tidal volume based on the digital gas flow rate signals; and calculating left and right lung tidal volumes based on the global tidal volume and the EIT data.

[0011] In one possible implementation, after calculating the tidal volume of the left and right lungs, the method further includes: establishing an impedance-volume calibration model based on multiple sets of first global tidal volumes and the first impedance values ​​in the first electrical impedance tomography data corresponding to each of the multiple sets of first global tidal volumes; and performing real-time correction on the tidal volumes of the left and right lungs based on the impedance-volume calibration model to obtain corrected tidal volumes of the left and right lungs. The establishment of the impedance-volume calibration model includes: synchronously recording the initial first global tidal volume and the initial first impedance value corresponding to the initial first global tidal volume; incrementally increasing the initial first global tidal volume by a preset increment to obtain multiple sets of first global tidal volumes and the first impedance values ​​corresponding to each of the multiple sets of first global tidal volumes; calculating the tidal volume change and the impedance change based on the multiple sets of first global tidal volumes and the first impedance values ​​corresponding to each of the multiple sets of first global tidal volumes; and performing linear fitting on the tidal volume change and the impedance change to obtain the impedance-volume calibration model.

[0012] Secondly, this application provides a multi-respiratory biomechanical state monitoring device for electrical impedance tomography (EIT), comprising: a multi-channel acquisition unit, a signal processing and analog-to-digital conversion unit, a main control processing unit, and an EIT device; wherein, the multi-channel acquisition unit is used to acquire simulated physiological signals from a user; the signal processing and analog-to-digital conversion unit is used to perform data processing and analog-to-digital conversion on the simulated physiological signals to obtain digital physiological signals; the main control processing unit is used to encapsulate the digital physiological signals and send the obtained encapsulated digital physiological data to the EIT device; the EIT device is used to perform joint analysis of the user's respiratory state based on the EIT data it has acquired and the received encapsulated digital physiological data to obtain respiratory state analysis results.

[0013] In one possible implementation, the multi-channel acquisition unit is connected to the signal processing and analog-to-digital conversion unit, the signal processing and analog-to-digital conversion unit is connected to the main control processing unit, and the main control processing unit is connected to the electrical impedance tomography device.

[0014] Thirdly, embodiments of this application also provide a computer device, which includes a memory and a processor, wherein the memory stores a computer program, and the processor executes the computer program to implement the above-described method.

[0015] Fourthly, embodiments of this application also provide a computer-readable storage medium storing a computer program that, when executed by a processor, can implement the above-described method.

[0016] This application provides a method and apparatus for monitoring multiple respiratory mechanical states in electrical impedance tomography, which has the following advantages compared with the prior art:

[0017] The system acquires simulated physiological signals from the user using a multi-channel acquisition unit; performs data processing and analog-to-digital conversion on the simulated physiological signals to obtain digital physiological signals; encapsulates the digital physiological signals and sends the encapsulated digital physiological data to a bioelectrical impedance analysis (BIA) device, enabling the BIA device to perform joint analysis of the user's respiratory status based on its own acquired BIA data and the received encapsulated digital physiological data, thus obtaining respiratory status analysis results. Compared with existing technologies, the technical solution of this application, by performing multi-channel acquisition, analog-to-digital conversion, and encapsulation processing on simulated physiological signals, eliminates the reliance on specific ventilators. The reliance on communication protocols allows the electrical impedance tomography (EIT) device to be compatible with different brands and models of ventilators, significantly improving its versatility. Furthermore, the multi-channel acquisition method avoids the need for multiple physical connections between the EIT device and the ventilator, simplifying operation. The standardized signal processing and transmission procedures provide a unified solution for the joint analysis of EIT data and respiratory mechanics parameters, filling the gap in standardization of traditional methods. Finally, the joint analysis of EIT data and the encapsulated digital physiological data significantly improves the accuracy and clinical applicability of respiratory status assessment. Attached Figure Description

[0018] The accompanying drawings, which are incorporated in and form part of this specification, illustrate embodiments consistent with the invention and, together with the description, serve to explain the principles of the invention.

[0019] 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, for those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0020] One or more embodiments are illustrated by way of example with reference numerals in the accompanying drawings. These illustrations do not constitute a limitation on the embodiments. Elements with the same reference numerals in the drawings are denoted as similar elements. Unless otherwise stated, the figures in the drawings are not to be limited by scale.

[0021] Figure 1 This is a flowchart illustrating an embodiment of a method for monitoring the multiple respiratory mechanical states in electrical impedance tomography provided in this application;

[0022] Figure 2 This is a schematic diagram of an embodiment of a multi-breathing mechanical state monitoring device for electrical impedance tomography provided in this application;

[0023] Figure 3 This is another structural schematic diagram of an embodiment of a multi-breathing mechanical state monitoring device for electrical impedance tomography provided in this application;

[0024] Figure 4 This is a schematic diagram of the structure of a computer device provided in this application. Detailed Implementation

[0025] To make the objectives, technical solutions, and advantages of the embodiments of this application clearer, the technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, not all embodiments. Based on the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application.

[0026] The following disclosure provides numerous different embodiments or examples for implementing various structures of this application. To simplify the disclosure, specific examples of components and arrangements are described below. These are merely examples and are not intended to limit the scope of this application. Furthermore, reference numerals and / or letters may be repeated in different examples. Such repetition is for simplification and clarity and does not in itself indicate a relationship between the various embodiments and / or arrangements discussed.

[0027] It should be understood that, when used in this specification and the appended claims, the terms "comprising" and "including" indicate the presence of the described features, integrals, steps, operations, elements and / or components, but do not exclude the presence or addition of one or more other features, integrals, steps, operations, elements, components and / or collections thereof.

[0028] It should also be understood that the terminology used in this specification is for the purpose of describing particular embodiments only and is not intended to limit the scope of the application. As used in this specification and the appended claims, the singular forms “a,” “an,” and “the” are intended to include the plural forms unless the context clearly indicates otherwise.

[0029] It should also be further understood that the term “and / or” as used in this application specification and the appended claims means any combination of one or more of the associated listed items and all possible combinations, and includes such combinations.

[0030] As used in this specification and the appended claims, the term "if" may be interpreted, depending on the context, as "when," "once," "in response to determination," or "in response to detection." Similarly, the phrases "if determined" or "if [described condition or event] is detected" may be interpreted, depending on the context, as "once determined," "in response to determination," "once [described condition or event] is detected," or "in response to detection of [described condition or event]."

[0031] Example 1, see Figure 1 , Figure 1 This is a flowchart illustrating an embodiment of a multi-breathing mechanical state monitoring method for electrical impedance tomography provided in this application, as shown below. Figure 1 As shown, the method includes steps 101-103, as detailed below:

[0032] Step 101: Acquire simulated physiological signals of the user based on the multi-channel acquisition unit.

[0033] In one embodiment, the multi-channel acquisition unit includes an airway pressure sensor, an esophageal pressure sensor, a gastric pressure sensor, and a flow sensor.

[0034] In one embodiment, the airway pressure sensor, the esophageal pressure sensor, the gastric pressure sensor, and the flow sensor are respectively connected to the airway pressure monitoring channel, the esophageal pressure monitoring channel, the gastric pressure monitoring channel, and the gas flow rate monitoring channel of the ventilator used by the user.

[0035] Preferably, the ventilator can be any brand and model of ventilator, without relying on a specific communication protocol.

[0036] In one embodiment, a simulated airway pressure signal of the user is acquired based on an airway pressure sensor; a simulated esophageal pressure signal of the user is acquired based on an esophageal pressure sensor; a simulated gastric pressure signal of the user is acquired based on a gastric pressure sensor; and a simulated gas flow rate signal provided by the ventilator to the user is acquired based on a flow sensor.

[0037] Specifically, the airway pressure sensor is connected to the airway pressure monitoring channel of the ventilator via a dedicated interface. The airway pressure sensor is typically installed near the proximal end of the breathing circuit, such as at the endotracheal intubation port. Based on this connection method, the airway pressure sensor can directly capture the pressure fluctuations in the airway during the user's breathing process. When the ventilator delivers gas to the user and / or the user breathes spontaneously, the pressure changes in the airway are sensed by the airway pressure sensor and converted into an analog airway pressure signal.

[0038] Specifically, the esophageal pressure sensor is connected to the esophageal pressure monitoring channel of the ventilator via an esophageal cuff catheter. The cuff at the tip of the esophageal cuff catheter is inserted into the lower esophagus through the patient's nose or mouth. When the cuff is inflated, it can sense the pressure change in the esophagus, which approximately represents the pressure change in the pleural cavity. The esophageal pressure sensor can sense the cuff pressure and convert it into a simulated esophageal pressure signal.

[0039] Specifically, the gastric pressure sensor is connected to the gastric pressure monitoring channel of the ventilator and is usually inserted into the user's stomach through a gastric tube or a dedicated monitoring catheter; the gastric pressure sensor senses changes in gastric pressure and converts them into analog gastric pressure signals.

[0040] Specifically, the flow sensor is connected to the gas flow rate monitoring channel of the ventilator and is generally installed in the inspiratory or expiratory tubing of the ventilator to directly monitor the volume of gas passing through the inspiratory or expiratory tubing per unit time. When the ventilator is running, the flow sensor converts the gas flow rate into an analog gas flow rate signal.

[0041] In one embodiment, the simulated airway pressure signal, the simulated esophageal pressure signal, the simulated gastric pressure signal, and the simulated gas flow rate signal are used as the simulated physiological signals.

[0042] Step 102: Perform data processing and analog-to-digital conversion on the simulated physiological signal to obtain a digital physiological signal.

[0043] In one embodiment, the simulated physiological signal is low-pass filtered to obtain a filtered simulated physiological signal.

[0044] Specifically, since the simulated physiological signals are susceptible to environmental electromagnetic interference, sensor noise, or circuit fluctuations during acquisition, and may be mixed with high-frequency signals such as equipment motor interference and wire coupling, these noises can mask the true physiological signal characteristics. Therefore, by setting a specific cutoff frequency for the low-pass filter, the simulated physiological signals can be low-pass filtered, allowing low-frequency physiological signals to pass through while suppressing high-frequency noise signals. The final output is a smooth and pure filtered simulated physiological signal, providing a reliable signal basis for subsequent processing.

[0045] In one embodiment, the gain of the filtered simulated physiological signal is adjusted to obtain an adjusted simulated physiological signal.

[0046] Specifically, the filtered simulated physiological signal obtained after filtering may have insufficient amplitude or overload due to the difference in the strength of the original signal; therefore, the gain of the filtered simulated physiological signal needs to be adjusted.

[0047] Specifically, the amplification factor is dynamically adjusted by a programmable gain amplifier according to the signal strength of each analog signal, and the amplitude of the filtered analog physiological signal is adjusted based on the adjusted amplification factor to bring the signal amplitude to the optimal range for subsequent analog-to-digital conversion. For example, the gain can be increased to enhance the signal strength for weak esophageal pressure signals, while the gain can be reduced to avoid signal saturation distortion for stronger airway pressure signals, ultimately resulting in a stable amplitude and a regulated analog physiological signal that is easy to convert later.

[0048] In one embodiment, the modulated simulated physiological signal is converted from analog to digital to obtain a data physiological signal.

[0049] Specifically, the modulated analog physiological signal is converted into a discrete digital signal by a high-precision analog-to-digital converter.

[0050] Specifically, the analog-to-digital converter samples the regulated analog physiological signal at a preset sampling frequency, converting the voltage value of each sampling point into a corresponding binary digital value. For example, a 16-bit analog-to-digital converter can convert an analog signal of 0-5V into a digital value of 0-65535, realizing the quantization of analog signals into digital signals. Moreover, the digital physiological signal obtained after analog-to-digital conversion retains the timing and amplitude characteristics of the original physiological signal, which can be recognized, processed, and transmitted by the main control processing unit, providing a digital foundation for subsequent data encapsulation and joint analysis with electrical impedance tomography equipment.

[0051] Step 103: The digital physiological signal is encapsulated and processed, and the encapsulated digital physiological data is sent to the electrical impedance tomography (EIT) device so that the EIT device can perform joint analysis of the user's respiratory state based on the EIT data it has collected and the encapsulated digital physiological data it has received, and obtain respiratory state analysis results.

[0052] In one embodiment, when the digital physiological signal is encapsulated and the resulting encapsulated digital physiological data is sent to the electrical impedance tomography (EIT) device, the digital physiological signal is time-stamped and the synchronized digital physiological signal is converted into a data format to obtain a target format digital physiological signal; the target format digital physiological signal is encapsulated based on a common communication protocol to obtain encapsulated digital physiological data; and the encapsulated digital physiological data is sent to the EIT device based on a standard data interface.

[0053] Specifically, since there may be slight differences in the timing and transmission delay of signals acquired by multi-channel sensors, direct integration could lead to data timing misalignment, affecting the accuracy of subsequent joint analysis. Therefore, the main control processing unit generates a unified timestamp through an internal unified clock or synchronization signal and adds the unified timestamp to each digital physiological signal. By calibrating the timestamps of data from each acquisition channel, the acquired airway pressure, esophageal pressure, gastric pressure, flow rate, and other signals are strictly aligned in the time dimension. For example, the simulated airway pressure signal at the start of inspiration is marked with the simulated flow rate signal, simulated esophageal pressure signal, and simulated gastric pressure signal at the same time as the timestamp, ensuring that the electrical impedance tomography (EIT) device can accurately correlate various parameters within the same respiratory cycle during joint analysis.

[0054] Specifically, the digital physiological signals after timestamp synchronization may have format differences due to different sensor types and acquisition channels; therefore, data format conversion is required.

[0055] Specifically, the main control processing unit performs data format unification processing on the synchronized digital physiological signals according to a preset standardized format, which can be a custom structured data format or an industry-standard format. This includes, but is not limited to, numerical unit calibration, precision normalization, and field mapping, ultimately generating a target format digital physiological signal with a unified format and clear semantics, laying the foundation for subsequent encapsulation and transmission.

[0056] Specifically, the general communication protocols include, but are not limited to, USB protocol, Ethernet TCP / IP protocol or wireless Bluetooth protocol.

[0057] Specifically, when the main control processing unit encapsulates the target format digital physiological signal based on a general communication protocol, it embeds the target format digital physiological signal into the protocol frame structure, adds a protocol header containing metadata such as device identifier, data type, and length, and adds a tail containing a checksum for data integrity verification, forming encapsulated digital physiological data that conforms to the protocol specifications. For example, when using the TCP / IP protocol, the data is segmented into network data packets, each containing a source address, destination address, data segment, and checksum information, ensuring that the data can be correctly identified and parsed by the electrical impedance tomography device during transmission, thus eliminating dependence on specific device protocols.

[0058] Specifically, the main control processing unit also sends the packaged digital physiological data to the electrical impedance tomography (EIT) device through a standard data interface. The standard data interface includes, but is not limited to, USB, Ethernet, or Bluetooth wireless interfaces. These interfaces are all industry-standard interfaces, eliminating the need for customized physical connections for specific EIT models and simplifying the deployment process.

[0059] Specifically, the standard data interface supports one or more communication methods such as USB communication, Ethernet communication, and wireless communication such as Wi-Fi and Bluetooth.

[0060] Preferably, during the encapsulation of digital physiological data transmission, the data communication unit will also monitor the data transmission status of the interface in real time. If a data transmission interruption or error occurs, a retransmission mechanism will be used to ensure that the data is delivered completely.

[0061] In one embodiment, the electrical impedance tomography (EIT) device performs joint analysis of the user's respiratory state based on its own acquired EIT data and the received encapsulated digital physiological data. When obtaining the respiratory state analysis results, it acquires EIT data. The EIT data is obtained by the EIT device itself and includes global impedance, left lung impedance, and right lung impedance. The received encapsulated digital physiological data is decapsulated to obtain decapsulated digital physiological data, which includes digital airway pressure, digital esophageal pressure, and digital gas flow rate. Based on the digital airway pressure and digital gas flow rate, corrected alveolar pressure data is calculated. Based on the digital airway pressure and digital esophageal pressure, transpulmonary pressure data is calculated. Based on the digital gas flow rate, global tidal volume is calculated. Based on the global tidal volume and the EIT data, left and right lung tidal volumes are calculated.

[0062] Specifically, the electrical impedance tomography device monitors the impedance changes of lung tissue in real time through an electrode array attached to the patient's chest wall, generating electrical impedance tomography data. The electrical impedance tomography data includes, but is not limited to, global impedance, left lung impedance, and right lung impedance. The global impedance reflects the overall ventilation changes of the entire lung, while the left lung impedance and right lung impedance correspond to the local ventilation status of the two lungs, respectively.

[0063] Specifically, after receiving the encapsulated digital physiological data, the electrical impedance tomography (EIT) device first decapsulates the encapsulated digital physiological data based on a preset general communication protocol. During the decapsulation process, the core decapsulated digital physiological data is extracted by stripping the device identifier, data length, and other control information from the protocol header and the checksum from the tail. The decapsulated digital physiological data includes standardized digital airway pressure signals, digital esophageal pressure signals, digital gastric pressure signals, and digital gas flow rate signals.

[0064] Specifically, when calculating corrected alveolar pressure data based on the digital airway pressure signal and the digital gas flow rate signal, airway resistance is obtained. The airway resistance, the digital airway pressure signal, and the digital gas flow rate signal are then substituted into the corrected alveolar pressure data calculation formula to obtain the corrected alveolar pressure data. The corrected alveolar pressure data calculation formula is as follows: Palv≈Paw-(Raw×Vx); where Palv is the corrected alveolar pressure, Paw is the digital airway pressure signal, Raw is the airway resistance, and Vx is the digital gas flow rate signal.

[0065] Specifically, the airway resistance (Raw) is pre-measured using the end-inspiratory occlusion method. Since airway resistance causes a difference between the proximal airway pressure and the actual pressure within the alveoli, the alveolar pressure is corrected by modifying the alveolar pressure calculation formula. This eliminates the interference of airway resistance on pressure transmission, making the calculation results closer to the true pressure within the alveoli, and providing an accurate pressure benchmark for assessing alveolar expansion status.

[0066] Specifically, when calculating transpulmonary pressure data based on the digital airway pressure signal and the digital esophageal pressure signal, the digital airway pressure signal and the digital esophageal pressure signal are substituted into a preset transpulmonary pressure data calculation formula to obtain the transpulmonary pressure data. The preset transpulmonary pressure data calculation formula is: PL = Paw - Pes; where PL is the transpulmonary pressure data, Paw is the digital airway pressure signal, and Pes is the digital esophageal pressure signal.

[0067] Specifically, transpulmonary pressure (PL) data essentially reflects the net expansion pressure borne by the alveolar walls; this parameter is a key indicator for judging whether alveoli are over-expanded (PL too high) or collapsed (PL too low), and directly guides the safe optimization of mechanical ventilation parameters.

[0068] Specifically, when calculating the global tidal volume based on the digital gas flow rate signal, the tidal volume is calculated by integrating the digital gas flow rate signal over time; for example, by acquiring the inhalation time, the product of the inhalation time and the digital gas flow rate signal is calculated, and the product is used as the global tidal volume.

[0069] Specifically, when calculating the tidal volume of the left and right lungs based on the global tidal volume and the electrical impedance tomography data, the global tidal volume, the global impedance, and the left lung impedance from the electrical impedance tomography data are substituted into a preset formula for calculating the left lung tidal volume to obtain the left lung tidal volume; and the global tidal volume, the global impedance, and the right lung impedance from the electrical impedance tomography data are substituted into a preset formula for calculating the right lung tidal volume to obtain the right lung tidal volume; wherein, the formula for calculating the left lung tidal volume is: VT l =VT*(Z l / Z); The formula for calculating the tidal volume of the right lung is: VT r =VT*(Z r / Z); where VT l Left lung tidal volume, VT is global tidal volume, Z is... l Z represents left lung impedance, Z represents global impedance, and VT represents t lung impedance. r Tidal volume of the right lung, Z r The impedance is for the right lung.

[0070] Specifically, the calculation of tidal volume in the left and right lungs is based on the principle that impedance changes are positively correlated with ventilation volume. By allocating global tidal volume through impedance ratio, a quantitative analysis of local ventilation volume in the left and right lungs can be achieved. It can intuitively present the ventilation difference between the two lungs, help identify local ventilation abnormalities such as atelectasis and pneumothorax, and provide a basis for precise clinical intervention.

[0071] In one embodiment, after calculating the tidal volume of the left and right lungs, the method further includes: establishing an impedance-volume calibration model based on multiple sets of first global tidal volumes and the first impedance values ​​in the first electrical impedance tomography data corresponding to each of the multiple sets of first global tidal volumes; and correcting the tidal volume of the left and right lungs in real time based on the impedance-volume calibration model to obtain the corrected tidal volume of the left and right lungs.

[0072] In one embodiment, establishing the impedance-volume calibration model includes: synchronously recording an initial first global tidal volume and an initial first impedance value corresponding to the initial first global tidal volume; incrementally increasing the initial first global tidal volume according to a preset increment to obtain multiple sets of first global tidal volumes and first impedance values ​​corresponding to each of the multiple sets of first global tidal volumes; calculating the tidal volume change and impedance change based on the multiple sets of first global tidal volumes and the first impedance values ​​corresponding to each of the multiple sets of first global tidal volumes; and performing linear fitting processing on the tidal volume change and impedance change to obtain the impedance-volume calibration model.

[0073] Specifically, during the initial ventilation of the patient, the initial first global tidal volume VT0 and the corresponding initial first impedance value Z0 are recorded simultaneously, forming the first set of associated data VT0-Z0. Subsequently, the initial first global tidal volume is incremented according to a preset increment, such as 50 ml each time, to obtain multiple sets of first global tidal volumes. The first global tidal volumes are then output in sequential increments through ventilator control, denoted as VT1, VT2...VT n Where n≥3, and after stabilizing ventilation in each incremental state, the corresponding first impedance value is recorded synchronously, denoted as Z1, Z2…Z n Where n≥3, multiple sets of associated data VT are ultimately obtained. n -Z n This step ensures that the data covers the impedance variation characteristics under different ventilation volumes, providing sufficient samples for model fitting.

[0074] Specifically, based on multiple sets of first global tidal volumes and their corresponding first impedance values, when calculating the tidal volume change and impedance change, the original data is transformed into variables required for model fitting. Specifically, using the initial first global tidal volume VT0 and the initial first impedance value Z0 as benchmarks, the difference between each set of incremental tidal volumes and the baseline global tidal volume is calculated, i.e., the tidal volume change ΔVT. n =VT n -VT0; Simultaneously calculate the difference between the first impedance value and the baseline impedance for each group, i.e., the impedance change ΔZ. n =Z n -Z0.

[0075] Specifically, a mathematical correlation model is established between the changes in tidal volume and impedance by performing linear fitting on the two. For example, the calculated multiple sets of tidal volume changes ΔVT n With the corresponding impedance change ΔZ nAs sample points, linear regression algorithms such as least squares are used for fitting to obtain a linear equation reflecting the relationship between the two: ΔVT=a×ΔZ+b, which is used as the impedance-volume calibration model, where ΔVT is the change in tidal volume, ΔZ is the change in impedance, a is the slope parameter, reflecting the volume change corresponding to a unit change in impedance, and b is the intercept parameter, used to correct system errors.

[0076] Specifically, the tidal volume of the left and right lungs is corrected in real time based on the impedance-volume calibration model. When obtaining the corrected tidal volume of the left and right lungs, the current impedance change of the current respiratory cycle is collected in real time by the electrical impedance tomography device, and the current impedance change is input into the impedance-volume calibration model to calculate the corrected tidal volume change. The global tidal volume is corrected based on the corrected tidal volume change to obtain the corrected global tidal volume. The corrected global tidal volume is then substituted back into the calculation formulas for the left lung tidal volume and the right lung tidal volume to calculate the corrected left lung tidal volume and the corrected right lung tidal volume.

[0077] Example 2, see Figure 2 , Figure 2 This is a schematic diagram of an embodiment of a multi-breathing mechanical state monitoring device for electrical impedance tomography (EIT) provided in this application. Corresponding to the above-described multi-breathing mechanical state monitoring method for EIT, this application also provides a multi-breathing mechanical state monitoring device for EIT. This multi-breathing mechanical state monitoring device for EIT includes modules for executing the above-described multi-breathing mechanical state monitoring method for EIT, and can be configured in a desktop computer, tablet computer, laptop computer, or other terminal. Specifically, the multi-breathing mechanical state monitoring device for EIT includes a multi-channel acquisition unit 201, a signal processing and analog-to-digital conversion unit 202, a main control processing unit 203, and an EIT imaging device 204.

[0078] The multi-channel acquisition unit 201 is used to acquire the user's simulated physiological signals.

[0079] The signal processing and analog-to-digital conversion unit 202 is used to perform data processing and analog-to-digital conversion on the analog physiological signal to obtain a digital physiological signal.

[0080] The main control processing unit 203 is used to encapsulate the digital physiological signal and send the resulting encapsulated digital physiological data to the electrical impedance tomography device.

[0081] The electrical impedance tomography device 204 is used to perform joint analysis of the user's respiratory status based on the electrical impedance tomography data it has collected and the received encapsulated digital physiological data, and to obtain respiratory status analysis results.

[0082] In one embodiment, the multi-channel acquisition unit 201 is connected to the signal processing and analog-to-digital conversion unit 202, the signal processing and analog-to-digital conversion unit 202 is connected to the main control processing unit 203, and the main control processing unit 203 is connected to the electrical impedance tomography device 204.

[0083] In one embodiment, the multi-channel acquisition unit 201 is used to acquire simulated physiological signals of the user, specifically including: the multi-channel acquisition unit 201 includes an airway pressure sensor, an esophageal pressure sensor, a gastric pressure sensor, and a flow sensor; based on the airway pressure sensor, it acquires the user's simulated airway pressure signal; based on the esophageal pressure sensor, it acquires the user's simulated esophageal pressure signal; based on the gastric pressure sensor, it acquires the user's simulated gastric pressure signal; based on the flow sensor, it acquires the simulated gas flow rate signal provided by the ventilator to the user; wherein, the airway pressure sensor, the esophageal pressure sensor, the gastric pressure sensor, and the flow sensor are respectively connected to the airway pressure monitoring channel, the esophageal pressure monitoring channel, the gastric pressure monitoring channel, and the gas flow rate monitoring channel of the ventilator used by the user.

[0084] In one embodiment, the signal processing and analog-to-digital conversion unit 202 is used to perform data processing and analog-to-digital conversion on the analog physiological signal to obtain a digital physiological signal. Specifically, it includes: performing low-pass filtering on the analog physiological signal to obtain a filtered analog physiological signal, and adjusting the gain of the filtered analog physiological signal to obtain an adjusted analog physiological signal; and performing analog-to-digital conversion on the adjusted analog physiological signal to obtain a data physiological signal.

[0085] In one embodiment, the main control processing unit 203 is used to encapsulate the digital physiological signal and send the resulting encapsulated digital physiological data to the electrical impedance tomography (EIT) device. Specifically, this includes: synchronizing the digital physiological signal with a timestamp and converting the synchronized digital physiological signal into a data format to obtain a target format digital physiological signal; encapsulating the target format digital physiological signal based on a common communication protocol to obtain encapsulated digital physiological data; and sending the encapsulated digital physiological data to the EIT device based on a standard data interface.

[0086] In one embodiment, the electrical impedance tomography (EIT) device 204 is used to jointly analyze the user's respiratory state based on the EIT data it has acquired and the received encapsulated digital physiological data to obtain respiratory state analysis results. Specifically, this includes: acquiring EIT data; wherein the EIT data is obtained by the EIT device itself and includes global impedance, left lung impedance, and right lung impedance; decapsulating the received encapsulated digital physiological data to obtain decapsulated digital physiological data, wherein the decapsulated digital physiological data includes digital airway pressure signal, digital esophageal pressure signal, and digital gas flow rate signal; calculating corrected alveolar pressure data based on the digital airway pressure signal and the digital gas flow rate signal; calculating transpulmonary pressure data based on the digital airway pressure signal and the digital esophageal pressure signal; calculating global tidal volume based on the digital gas flow rate signal; and calculating left and right lung tidal volumes based on the global tidal volume and the EIT data.

[0087] In one embodiment, the electrical impedance tomography (EIT) device 204, after calculating the tidal volume of the left and right lungs, further includes: establishing an impedance-volume calibration model based on multiple sets of acquired first global tidal volumes and first impedance values ​​in the first electrical impedance tomography data corresponding to each of the multiple sets of first global tidal volumes; and performing real-time correction on the tidal volumes of the left and right lungs based on the impedance-volume calibration model to obtain corrected tidal volumes of the left and right lungs; wherein, establishing the impedance-volume calibration model includes: synchronously recording the initial first global tidal volume and the initial first impedance value corresponding to the initial first global tidal volume; incrementally increasing the initial first global tidal volume by a preset increment to obtain multiple sets of first global tidal volumes and first impedance values ​​corresponding to each of the multiple sets of first global tidal volumes; calculating the tidal volume change and impedance change based on the multiple sets of first global tidal volumes and the first impedance values ​​corresponding to each of the multiple sets of first global tidal volumes; and performing linear fitting on the tidal volume change and impedance change to obtain the impedance-volume calibration model.

[0088] like Figure 3 As shown, Figure 3 This is another structural schematic diagram of an embodiment of a multi-breathing mechanical state monitoring device for electrical impedance tomography provided in this application.

[0089] In one embodiment, the multi-breathing mechanical state monitoring device for electrical impedance tomography provided in this application further includes: a power module 205, a data storage unit 206, and a data communication module 207.

[0090] In one embodiment, the power output terminal of the power module 205 is connected to the signal processing and analog-to-digital conversion unit 202, the main control unit 203 and the data communication unit 207 respectively, for supplying power to the signal processing and analog-to-digital conversion unit 202, the main control unit 203 and the data communication unit 207; the power input terminal of the power module 205 is connected to the power supply.

[0091] Preferably, the power module 205 has multiple regulated outputs.

[0092] In one embodiment, the data storage unit 206 is bidirectionally connected to the main control processing unit 203.

[0093] In one embodiment, the main control processing unit 203 is connected to the electrical impedance tomography device 204 through the data communication module 207.

[0094] The above-described multi-breathing mechanical state monitoring device for electrical impedance tomography can implement the multi-breathing mechanical state monitoring method for electrical impedance tomography described in the above method embodiments. The options in the above method embodiments are also applicable to this embodiment, and will not be detailed here.

[0095] like Figure 4 As shown, Figure 4 This is a schematic diagram of the structure of a computer device provided in this application; it includes a processor 111, a communication interface 112, a memory 113 and a communication bus 114, wherein the processor 111, the communication interface 112 and the memory 113 communicate with each other through the communication bus 114, and the memory 113 is used to store computer programs.

[0096] In one embodiment of this application, when the processor 111 executes the program stored in the memory 113, it implements the multi-respiratory mechanical state monitoring method for electrical impedance tomography provided in any of the foregoing method embodiments.

[0097] It will be understood by those skilled in the art that all or part of the processes in the methods of the above embodiments can be implemented by a computer program instructing related hardware. The computer program may be stored in a storage medium, which is a computer-readable storage medium. The computer program is executed by at least one processor in the computer system to implement the process steps of the embodiments of the above methods.

[0098] Therefore, embodiments of this application also provide a computer-readable storage medium having a computer program stored thereon, wherein the computer program, when executed by a processor, implements the steps of the method for monitoring the multi-breathing mechanical state of electrical impedance tomography as provided in any of the foregoing method embodiments.

[0099] The storage medium is a physical, non-transient storage medium, such as a USB flash drive, external hard drive, read-only memory (ROM), magnetic disk, or optical disk, or any other physical storage medium capable of storing program code. The computer-readable storage medium can be non-volatile or volatile.

[0100] Those skilled in the art will 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 implementations should not be considered beyond the scope of this application.

[0101] In the several embodiments provided in this application, it should be understood that the disclosed apparatus and methods can be implemented in other ways. For example, the apparatus embodiments described above are merely illustrative. For example, the division of each unit is merely a logical functional division, and there may be other division methods in actual implementation. For example, multiple units or components may be combined or integrated into another system, or some features may be ignored or not executed.

[0102] The steps in the methods of this application embodiment can be adjusted, merged, or deleted according to actual needs. The units in the apparatus of this application embodiment can be merged, divided, or deleted according to actual needs. Furthermore, the functional units in the various embodiments of this application can be integrated into one processing unit, or each unit can exist physically separately, or two or more units can be integrated into one unit.

[0103] If the integrated unit is implemented as a software functional unit and sold or used as an independent product, it can be stored in a storage medium. Based on this understanding, the technical solution of this application, in essence, or the part that contributes to the prior art, or all or part of the technical solution, can be embodied in the form of a software product. This computer software product is stored in a storage medium and includes several instructions to cause a computer device (which may be a personal computer, a terminal, or a network device, etc.) to execute all or part of the steps of the methods described in the various embodiments of this application.

[0104] In the above embodiments, the descriptions of each embodiment have different focuses. For parts that are not described in detail in a certain embodiment, please refer to the relevant descriptions in other embodiments.

[0105] Obviously, those skilled in the art can make various modifications and variations to this application without departing from the spirit and scope of this application. Since these modifications and variations fall within the scope of the claims and their equivalents, this application also intends to include these modifications and variations.

[0106] The above description is merely a specific embodiment of this application, but the scope of protection of this application is not limited thereto. Any person skilled in the art can easily conceive of various equivalent modifications or substitutions within the technical scope disclosed in this application, and these modifications or substitutions should all be covered within the scope of protection of this application. Therefore, the scope of protection of this application should be determined by the scope of the claims. Project task number of this application: 2024ZD0522700.

Claims

1. A method for monitoring multiple respiratory mechanical states in electrical impedance tomography, characterized in that, include: Simulated physiological signals of users are acquired using a multi-channel acquisition unit; The simulated physiological signals are processed and converted from analog to digital to obtain digital physiological signals; The digital physiological signal is encapsulated and processed, and the resulting encapsulated digital physiological data is sent to an electrical impedance tomography (EIT) device, so that the EIT device can perform joint analysis of the user's respiratory state based on its own acquired EIT data and the received encapsulated digital physiological data, and obtain respiratory state analysis results.

2. The method for monitoring multiple respiratory mechanical states in electrical impedance tomography as described in claim 1, characterized in that, The user's simulated physiological signals are acquired using a multi-channel acquisition unit, specifically including: The multi-channel acquisition unit includes an airway pressure sensor, an esophageal pressure sensor, a gastric pressure sensor, and a flow sensor; Based on the airway pressure sensor, the user's simulated airway pressure signal is collected; Based on the esophageal pressure sensor, the user's simulated esophageal pressure signal is collected; Based on the gastric pressure sensor, the user's simulated gastric pressure signal is collected; Based on the flow sensor, the simulated gas flow rate signal provided by the ventilator to the user is acquired; The airway pressure sensor, the esophageal pressure sensor, the gastric pressure sensor, and the flow sensor are respectively connected to the airway pressure monitoring channel, the esophageal pressure monitoring channel, the gastric pressure monitoring channel, and the gas flow rate monitoring channel of the ventilator used by the user.

3. The method for monitoring multiple respiratory mechanical states in electrical impedance tomography as described in claim 1, characterized in that, The simulated physiological signal is processed and converted from analog to digital to obtain a digital physiological signal, specifically including: The simulated physiological signal is subjected to low-pass filtering to obtain a filtered simulated physiological signal, and the gain of the filtered simulated physiological signal is adjusted to obtain an adjusted simulated physiological signal. The simulated physiological signal of regulation is converted from analog to digital to obtain the data physiological signal.

4. The method for monitoring multiple respiratory mechanical states in electrical impedance tomography as described in claim 1, characterized in that, The digital physiological signals are encapsulated and processed, and the resulting encapsulated digital physiological data is sent to an electrical impedance tomography (EIT) device. Specifically, this includes: The digital physiological signal is timestamped and then the synchronized digital physiological signal is converted into a data format to obtain a digital physiological signal in the target format. The target format digital physiological signal is encapsulated and processed based on a common communication protocol to obtain encapsulated digital physiological data. The packaged digital physiological data is then sent to the electrical impedance tomography device based on a standard data interface.

5. The method for monitoring multiple respiratory mechanical states in electrical impedance tomography as described in claim 1, characterized in that, The electrical impedance tomography (EIT) device performs a joint analysis of the user's respiratory status based on its own acquired EIT data and the received encapsulated digital physiological data, obtaining respiratory status analysis results, specifically including: Acquire electrical impedance tomography data; wherein, the electrical impedance tomography data is obtained by the electrical impedance tomography device itself, including global impedance, left lung impedance and right lung impedance; The received encapsulated digital physiological data is decapsulated to obtain decapsulated digital physiological data, wherein the decapsulated digital physiological data includes digital airway pressure signal, digital esophageal pressure signal and digital gas flow rate signal; Based on the digital airway pressure signal and the digital gas flow rate signal, the corrected alveolar pressure data is calculated; Based on the digital airway pressure signal and the digital esophageal pressure signal, calculate the transpulmonary pressure data; Calculate the global tidal volume based on the digital gas flow rate signal; Based on the global tidal volume and the electrical impedance tomography data, the tidal volume of the left and right lungs is calculated.

6. The method for monitoring multiple respiratory mechanical states in electrical impedance tomography as described in claim 1, characterized in that, After calculating the tidal volume of the left and right lungs, it also includes: Based on the acquired multiple sets of first global tidal volumes and the first impedance values ​​in the first electrical impedance tomography data corresponding to each of the multiple sets of first global tidal volumes, an impedance-volume calibration model is established. The tidal volume of the left and right lungs is corrected in real time based on the impedance-volume calibration model to obtain the corrected tidal volume of the left and right lungs. The establishment of the impedance-volume calibration model includes: The initial first global tidal volume and the initial first impedance value corresponding to the initial first global tidal volume are recorded synchronously. The initial first global tidal volume is incremented according to a preset increment to obtain multiple sets of first global tidal volumes and the first impedance values ​​corresponding to each of the multiple sets of first global tidal volumes. Based on multiple sets of first global tidal volumes and the first impedance values ​​corresponding to each of the multiple sets of first global tidal volumes, calculate the tidal volume change and the impedance change. The tidal volume change and the impedance change are linearly fitted to obtain the impedance-volume calibration model.

7. A multi-breathing mechanical state monitoring device for electrical impedance tomography, characterized in that, include: Multi-channel acquisition unit, signal processing and analog-to-digital conversion unit, main control processing unit, and electrical impedance tomography equipment; The multi-channel acquisition unit is used to acquire the user's simulated physiological signals. The signal processing and analog-to-digital conversion unit is used to perform data processing and analog-to-digital conversion on the analog physiological signal to obtain a digital physiological signal. The main control processing unit is used to encapsulate the digital physiological signal and send the resulting encapsulated digital physiological data to the electrical impedance tomography device. The electrical impedance tomography device is used to perform joint analysis of the user's respiratory status based on the electrical impedance tomography data it has acquired and the received encapsulated digital physiological data, and to obtain respiratory status analysis results.

8. The multi-respiratory mechanical state monitoring device for electrical impedance tomography as described in claim 7, characterized in that, The multi-channel acquisition unit is connected to the signal processing and analog-to-digital conversion unit, the signal processing and analog-to-digital conversion unit is connected to the main control processing unit, and the main control processing unit is connected to the electrical impedance tomography device.

9. A computer device, characterized in that, The computer device includes a memory and a processor, wherein the memory stores a computer program, and the processor executes the computer program to implement the method as described in any one of claims 1-7.

10. A computer-readable storage medium, characterized in that, The storage medium stores a computer program that, when executed by a processor, can implement the method as described in any one of claims 1-7.

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