Detailed Description
The following description of the embodiments of the present application will be made clearly and fully with reference to the accompanying drawings, in which it is evident that the embodiments described are some, but not all embodiments of the application. All other embodiments, which can be made by those skilled in the art based on the embodiments of the application without making any inventive effort, are intended to be within the scope of the application.
The flow diagrams depicted in the figures are merely illustrative and not necessarily all of the elements and operations/steps are included or performed in the order described. For example, some operations/steps may be further divided, combined, or partially combined, so that the order of actual execution may be changed according to actual situations.
It is to be understood that the terminology used in the description of the application herein is for the purpose of describing particular embodiments only and is not intended to be limiting 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 as well, unless the context clearly indicates otherwise.
It should also be understood that the term "and/or" as used in the present specification and the appended claims refers to any and all possible combinations of one or more of the associated listed items, and includes such combinations.
Medical devices such as ventilators and anesthesia machines are widely used in surgical treatment of a target subject, and can provide ventilation support for the target subject. In general, ventilation requirements of different target objects are greatly different, and spontaneous breathing intensities are different, so that detection and identification of spontaneous breathing of the target objects are required. Large-intensity spontaneous breathing of the target object is easily detected and identified, but small-intensity spontaneous breathing of the target object is not easily detected and identified. Taking veterinary anesthesia machines as an example, because of cost limitation, the veterinary anesthesia machines on the market at present are generally not provided with a flow sensor at the end of a target object, and for small animals or small weight animals, the target object is difficult to detect and identify due to small-intensity spontaneous breathing.
In order to solve the problems, the application provides breathing ventilation equipment and a spontaneous breathing identification method, so as to improve the accuracy of spontaneous breathing identification of a target object through the breathing ventilation equipment.
By way of example, the respiratory ventilation device may be an anesthesia machine, a respirator, etc., such as a veterinary anesthesia machine, a veterinary respirator. Some embodiments of the present application are described in detail below with reference to the accompanying drawings. The following embodiments and features of the embodiments may be combined with each other without conflict.
Referring to fig. 1, fig. 1 is a schematic block diagram of a respiratory ventilation apparatus according to an embodiment of the present application.
As shown in fig. 1, the respiratory ventilation apparatus 1000 includes a host 100, a gas source interface 200, a respiratory ventilation line 300, a pressure detection unit 400, and a processor 500. Wherein, the air source interface 200 is arranged on the host 100 and is used for connecting an external air source; one side of the respiratory ventilation line 300 is connected to the air source interface 200, and the other side of the respiratory ventilation line 300 is connected to the target object for delivering air provided by an external air source to the target object; the pressure detection unit 400 is disposed on the respiratory ventilation circuit 300 and is used for detecting a pressure value of the gas in the respiratory ventilation circuit 300; the processor 500 is disposed in the host 100, and is configured to obtain a pressure value detected by the pressure detecting unit 400, and estimate a flow rate corresponding to the respiration of the target object according to the pressure value, so as to perform spontaneous respiration identification of the target object according to the estimated flow rate. The greater the estimated flow rate, the greater the intensity of spontaneous respiratory effort of the target subject, and conversely, the lesser the intensity of spontaneous respiratory effort of the target subject.
Illustratively, the respiratory ventilation circuit 300 includes an exhalation circuit 310, an inhalation circuit 320, and a target end ventilation circuit 330. One side of the ventilation pipeline 330 at the target object end is respectively communicated with the exhalation pipeline 310 and the inhalation pipeline 320, and the other side is used for being connected to the target object, and is used for conveying the gas provided by an external gas source to the target object through the inhalation pipeline 320 and outputting the gas exhaled by the target object to the exhalation pipeline 310, and at least part of the gas exhaled by the target object is discharged to the outside of the respiratory ventilation device 1000 through the exhalation pipeline 310. Wherein a portion of the exhalation line 310 and inhalation line 320 are disposed within the host 100, which may be referred to as a machine circuit, and another portion of the lines are disposed outside of the host 100.
The pressure detection unit 400 may be provided on the exhalation line 310, in which case the pressure detection unit 400 is used to detect the pressure value within the exhalation line 310. Alternatively, the pressure detecting unit 400 may be provided on the suction line 320, in which case the pressure detecting unit 400 is used to detect the pressure value in the suction line 320. When the pressure detection unit 400 is provided in the exhalation line 310 or the inhalation line 320, it may be provided in a line segment inside the main unit, that is, in a line segment of the machine circuit part, or in a line segment outside the main unit, that is, in a patient line segment connecting the main unit and the patient. In addition, the pressure detection unit 400 is disposed on the target end ventilation line 330, that is, the pressure detection unit 400 is disposed near the target end, in which case the pressure detection unit 400 is configured to detect a pressure value in the target end ventilation line 330. Illustratively, the pressure detection unit 400 includes, but is not limited to, a pressure sensor or the like.
In some embodiments, the pressure detection unit 400 is configured to: detecting a pressure value in the respiratory ventilation circuit for each detection period; the processor 500 is configured to: acquiring a first pressure value detected by the pressure detection unit in a current detection period and a second pressure value detected in a last detection period; calculating a pressure difference between the first pressure value and the second pressure value; and estimating the flow rate corresponding to the respiration of the target object according to the pressure difference.
Based on the detection period to which the pressure detection unit 400 corresponds, the pressure detection unit 400 detects the pressure value in the respiratory ventilation circuit 300 in each detection period. That is, when the pressure detecting unit 400 is disposed on the exhalation line 310, the pressure detecting unit 400 detects a pressure value in the exhalation line 310 in each detection period; when the pressure detecting unit 400 is disposed on the suction line 320, the pressure detecting unit 400 detects a pressure value in the suction line 320 in each detection period; when the pressure detection unit 400 is provided on the target object side ventilation line 330, the pressure detection unit 400 detects the pressure value in the target object side ventilation line 330 in each detection period.
During the current detection period, the processor 500 acquires the pressure value detected by the pressure detection unit 400 during the current detection period, and acquires the pressure value detected by the pressure detection unit 400 during the last detection period. Illustratively, after the pressure detection unit 400 detects the pressure value in the respiratory ventilation circuit 300 for each detection period, the processor 500 stores the detected pressure value and obtains the stored pressure value detected by the pressure detection unit 400 during the last detection period. For convenience of description, hereinafter, the pressure value detected by the pressure detecting unit 400 at the current detection period is referred to as a first pressure value, and the pressure value detected by the pressure detecting unit 400 at the previous detection period is referred to as a second pressure value.
The processor 500 obtains the first pressure value detected by the pressure detecting unit 400 in the current detection period and the second pressure value detected by the pressure detecting unit 400 in the previous detection period, and calculates the pressure difference between the first pressure value and the second pressure value. For example, if the processor 500 obtains the first pressure value P1 and the second pressure value P0, the pressure difference Δp between the first pressure value P1 and the second pressure value P0 is calculated as: Δp=p1-P0. Then, the processor 500 estimates a flow rate corresponding to the respiration of the target subject according to the calculated pressure difference Δp.
In some embodiments, the processor 500 is configured to: and inputting the pressure difference into a preset flow rate estimation model, and outputting the flow rate corresponding to the respiration of the target object.
The flow velocity estimation model can be set manually through experience, can be obtained after offline training or can be identified in real time online. The flow rate estimation model characterizes the correspondence between the pressure change and the flow of the breathing ventilation circuit 300, which is illustratively a first order model or a higher order model. And inputting the calculated pressure difference delta P into a flow rate estimation model for processing, and outputting the flow rate corresponding to the respiration of the target object.
In some embodiments, the processor 500 is configured to: obtaining pipeline parameters corresponding to the respiratory ventilation pipeline, wherein the pipeline parameters comprise elastic parameters and resistance parameters; and calculating and obtaining the flow rate corresponding to the target object respiration according to the pressure difference and the pipeline parameter.
The circuit parameters corresponding to the respiratory ventilation circuit 300 include, but are not limited to, an elasticity parameter C, a resistance parameter R, and the like. The processor 500 calculates and obtains the flow rate corresponding to the target breathing according to the calculated pressure difference Δp and the pipeline parameters such as the elastic parameter C and the resistance parameter R corresponding to the breathing ventilation pipeline 300. For example, a product value of the pressure difference Δp and the elastic parameter C is calculated, and the product value is determined as the flow rate corresponding to the target subject respiration.
In some embodiments, the processor 500 is configured to: and calculating the acquired pressure difference and the flow rate corresponding to the pipeline parameter according to a preset mapping relation between the pressure difference, the pipeline parameter and the flow rate.
For example, the preset mapping relationship between the pressure difference, the pipeline parameter and the flow rate is: Δp=f×r+v/C, where Δp is the pressure difference, F is the flow rate, R is the resistance parameter, V is the volume change amount, and C is the elastic parameter of the respiratory ventilation line 300. And substituting the calculated pressure difference delta P, the resistance parameter R and the elasticity parameter C of the breathing ventilation pipeline 300 into the mapping relation, and calculating to obtain the flow rate F corresponding to the breathing of the target object.
In some embodiments, the processor 500 is configured to: and carrying out compensation processing on the estimated flow velocity according to a fitting compensation strategy to obtain the corrected flow velocity.
The pressure detection unit 400 is disposed at different positions of the exhalation line 310, the inhalation line 320, the target ventilation line 330, and the like, and the pressure values detected are different, so that the estimated flow rate is different from the actual flow rate. For example, if the pressure detecting unit 400 is disposed on the exhalation line 310/inhalation line 320, the distance from the target end is relatively long, and the estimated flow rate may be smaller than the actual flow rate. Therefore, after the corresponding flow velocity is obtained by calculation and estimation, the estimated flow velocity is compensated according to a preset fitting compensation strategy, for example, when the estimated flow velocity is calculated based on a first-order model, the estimated flow velocity can be linearly compensated to obtain a corrected flow velocity, and the corrected flow velocity is closer to the actual flow velocity, so that the accuracy of autonomous breath recognition of the target object can be further improved.
In some embodiments, the respiratory ventilation apparatus 1000 further comprises a flow detection unit 600, wherein the flow detection unit 600 is disposed within the host 100, and the flow detection unit 600 is configured to detect a flow of the host side. Illustratively, the flow detection unit 600 includes, but is not limited to, a flow sensor or the like. The processor 500 is configured to obtain the flow rate detected by the flow rate detecting unit 600, and correct the estimated flow rate according to the flow rate detected by the flow rate detecting unit 600, to obtain a corrected flow rate.
According to the flow detected by the flow detection unit 600 and the corresponding detection duration, the flow rate at the host side can be calculated and obtained, the estimated flow rate is corrected based on the flow rate at the host side, for example, the estimated flow rate is linearly compensated, so as to obtain the corrected flow rate, and the corrected flow rate is more accurate, thereby further improving the accuracy of autonomous breath recognition of the target object.
The embodiment of the application also provides breathing and ventilating equipment. As shown in fig. 2, the respiratory ventilation apparatus 1000 includes a host 100, an air source interface 200, a respiratory ventilation line 300, a pressure detection unit 400, a processor 500, a drug output device 700, and a human-machine interaction device 800. Wherein, the air source interface 200 is arranged on the host 100 and is used for connecting an external air source; one side of the respiratory ventilation line 300 is connected to the air source interface 200, and the other side of the respiratory ventilation line 300 is connected to the target object for delivering air provided by an external air source to the target object; wherein, the target object end of the breathing ventilation pipeline is not provided with a flow sensor; the anesthetic output device 700 is configured to mix stored anesthetic with input gas and output the mixed gas to the respiratory ventilation line 300, and fresh gas, which may be oxygen, air, laughing gas, etc., is input to the respiratory ventilation line from an external gas source, and the stored anesthetic is mixed with fresh gas provided from the external gas source and output the mixed gas; the human-machine interaction device 800 is configured to set the breathing apparatus 1000 to the first trigger mode and/or the second trigger mode in response to a user operation; the pressure detection unit 400 is disposed on the respiratory ventilation circuit 300, and is configured to detect a pressure value corresponding to the respiratory ventilation circuit 300; the processor 500 is disposed in the host 100, and is configured to perform spontaneous breathing recognition of the target subject according to the estimated flow rate of the target subject's breathing when the breathing ventilation apparatus 1000 is provided with the first trigger mode, and to perform spontaneous breathing recognition of the target subject according to the pressure value detected by the pressure detection unit 400 when the breathing ventilation apparatus 1000 is provided with the second trigger mode.
The host 100, the air source interface 200, the respiratory ventilation line 300, and the pressure detection unit 400 are described in the above embodiments, and are not described herein.
The human-machine interaction device 800 sets the breathing apparatus 1000 to the first trigger mode and/or the second trigger mode in response to a user operation. The first trigger mode corresponds to flow rate trigger, and the second trigger mode corresponds to pressure trigger.
Illustratively, the respiratory ventilation apparatus 1000 includes a display screen, and in actual operation, the ventilation mode setting interface is displayed on the display screen of the respiratory ventilation apparatus 1000. For example, as shown in fig. 3, the ventilation mode setting interface includes parameter setting options corresponding to a plurality of ventilation modes (PCV pressure control ventilation mode, VCV volume control ventilation mode, SIMV synchronous intermittent instruction ventilation mode, etc.), wherein the parameter setting options include tidal volume, respiratory rate, respiratory ratio, positive end expiratory pressure, flow trigger threshold, pressure trigger threshold, etc. The user may perform a corresponding operation based on the ventilation mode setting interface, for example, as shown in fig. 3, a threshold for flow rate triggering may be selectively set in the VCV mode, and the subsequent breathing ventilation device 1000 may perform the identification of spontaneous breathing in the first triggering mode. In an embodiment not shown, the pressure triggered threshold may be selectively set in the VCV mode, and the respiratory ventilation apparatus 1000 may then perform the identification of spontaneous breathing in accordance with the second trigger mode. In one example, the pressure trigger threshold and the flow rate trigger threshold may also be set simultaneously, with the respiratory ventilation apparatus 1000 supporting both triggers in operation.
When the respiratory ventilation apparatus 1000 is set with the first trigger mode, the processor 500 performs spontaneous breath identification of the target subject based on the estimated flow rate of the target subject's breath. Illustratively, the respiratory ventilation apparatus 1000 includes a flow detection unit 600 disposed in the host 100, and the processor 500 may estimate a flow rate of respiration of the target subject according to a pressure value obtained by the pressure detection unit by detecting the flow rate of the host side through the flow detection unit 600, and then perform spontaneous respiratory identification of the target subject according to the flow rate. How to estimate the flow rate of the target subject's breath based on the pressure values is described in connection with fig. 1 and will not be repeated here.
When the respiratory ventilation apparatus 1000 is provided with the second trigger mode, the processor 500 acquires the pressure value detected by the pressure detection unit 400, and estimates a flow rate corresponding to the respiration of the target subject according to the pressure value, so as to perform spontaneous respiration identification of the target subject according to the estimated flow rate. The specific manner in which the processor 500 performs the spontaneous breathing recognition of the target object according to the pressure value detected by the pressure detecting unit 400 may be referred to in the above-mentioned embodiments, and will not be described herein.
It will be appreciated that the above designations for the various components of the respiratory ventilation apparatus 1000 are for identification purposes only and are not intended to limit embodiments of the present application.
The spontaneous breathing recognition method provided by the embodiment of the present application will be described in detail below based on the breathing ventilation apparatus 1000. It should be noted that the breathing ventilation apparatus 1000 in fig. 1 to 2 does not constitute a limitation on the application scenario of the spontaneous breathing identification method.
Referring to fig. 4, fig. 4 is a schematic flowchart of a spontaneous breathing recognition method according to an embodiment of the present application. As shown in fig. 4, the spontaneous breathing recognition method specifically includes step S101 and step S103.
S101, acquiring a pressure value detected by a pressure detection unit, wherein the pressure detection unit is arranged on a breathing ventilation pipeline of breathing ventilation equipment.
Illustratively, a corresponding pressure detection unit, such as a pressure sensor, is provided in the breathing ventilation line of the breathing ventilation device. The respiratory ventilation pipeline comprises an expiration pipeline, an inspiration pipeline and a target object end ventilation pipeline. When the pressure detection unit is arranged on the expiratory pipeline, the pressure value in the expiratory pipeline detected by the pressure detection unit is obtained. When the pressure detection unit is arranged on the air suction pipeline, the pressure value in the air suction pipeline detected by the pressure detection unit is obtained. When the pressure detection unit is arranged on the ventilation pipeline of the target object end, the pressure value in the ventilation pipeline of the target object end detected by the pressure detection unit is obtained.
In some embodiments, the pressure detection unit detects a pressure value within the respiratory ventilation circuit for each detection period. That is, when the pressure detecting unit is disposed on the exhalation line, the pressure detecting unit detects a pressure value in the exhalation line in each detection period; when the pressure detection unit is arranged on the air suction pipeline, the pressure detection unit detects the pressure value in the air suction pipeline in each detection period; when the pressure detection unit is arranged on the ventilation pipeline of the target object end, the pressure detection unit detects the pressure value in the ventilation pipeline of the target object end in each detection period.
S102, estimating the flow velocity corresponding to the respiration of the target object according to the pressure value. Based on the pressure values corresponding to the breathing ventilation pipelines in a plurality of detection periods detected by the pressure detection unit, the flow velocity corresponding to the breathing of the target object is estimated through the change of the pressure values.
In some embodiments, as shown in fig. 5, step S101 may include sub-step S1011 and step S102 may include sub-step S1021 and sub-step S1022.
S1011, acquiring a first pressure value detected by the pressure detection unit in a current detection period and a second pressure value detected in a last detection period;
s1021, calculating the pressure difference between the first pressure value and the second pressure value;
and S1022, estimating the flow rate corresponding to the target object respiration according to the pressure difference.
Illustratively, a first pressure value detected by the pressure detecting unit during a current detection period and a second pressure value detected by the pressure detecting unit during a previous detection period are acquired. Then, a pressure difference between the first pressure value and the second pressure value is calculated. For example, if the first pressure value P1 and the second pressure value P0 are obtained, the pressure difference Δp between the first pressure value P1 and the second pressure value P0 is calculated as: Δp=p1-P0. And then, estimating the flow rate corresponding to the respiration of the target object according to the calculated pressure difference delta P.
In some embodiments, the calculated pressure difference is input into a preset flow rate estimation model, and the flow rate corresponding to the respiration of the target object is output.
The flow rate estimation model characterizes the corresponding relation between the pressure change and the flow of the respiratory ventilation pipeline, and is a first-order model or a high-order model.
In some embodiments, a circuit parameter corresponding to the breathing ventilation circuit is obtained, and the flow rate corresponding to the target subject breathing is obtained by calculation according to the calculated pressure difference and the circuit parameter. The circuit parameters corresponding to the respiratory ventilation circuit include, but are not limited to, an elasticity parameter C, a resistance parameter R, and the like.
The mapping relationship between the preset pressure difference, the pipeline parameter and the flow rate is as follows: Δp=f×r+v/C, where Δp is the pressure difference, F is the flow rate, R is the resistance parameter, V is the volume change, and C is the elastic parameter of the respiratory ventilation line. And substituting the calculated pressure difference delta P, the resistance parameter R of the breathing ventilation pipeline and the elastic parameter C into a mapping relation, and calculating to obtain the flow velocity F corresponding to the breathing of the target object.
In some embodiments, after the flow rate corresponding to the target subject's breath is obtained, the flow rate is corrected. For example, according to the fitting compensation strategy, compensation processing is performed on the estimated flow rate, and a corrected flow rate is obtained. The corrected flow rate is closer to the actual flow rate.
In some embodiments, as shown in fig. 6, step S102 may be followed by step S104 and step S105.
S104, acquiring the flow detected by a flow detection unit arranged in the host of the breathing ventilation equipment.
Illustratively, a flow detection unit, such as a flow sensor, is disposed within a host of the respiratory ventilation apparatus. The flow rate at the host side is detected by a flow rate detection means (flow rate sensor) provided in the host.
S105, correcting the estimated flow rate according to the flow rate to obtain the corrected flow rate.
After the flow detected by the flow detection unit is obtained, the estimated flow velocity is corrected according to the detected flow, and the corrected flow velocity is obtained. For example, according to the flow detected by the flow detecting unit and the corresponding detection duration, the flow rate at the host side can be calculated and obtained, the estimated flow rate is corrected based on the flow rate at the host side, for example, the estimated flow rate is linearly compensated, so as to obtain the corrected flow rate, and the corrected flow rate is more accurate.
S103, carrying out autonomous respiration recognition of the target object according to the flow rate.
The magnitude of the flow rate reflects the intensity of spontaneous breathing effort of the target subject, and the spontaneous breathing identification of the target subject is realized according to the estimated flow rate. The greater the estimated flow rate, the greater the intensity of spontaneous respiratory effort of the target subject, and conversely, the lesser the intensity of spontaneous respiratory effort of the target subject.
Illustratively, the spontaneous breathing identification of the target subject is performed based on the corrected flow rate. Because the corrected flow rate is closer to the real flow rate, the accuracy of autonomous breath recognition of the target object is further improved.
The spontaneous breathing identification method provided by the embodiment is applied to breathing ventilation equipment, a pressure detection unit is arranged on a breathing ventilation pipeline of the breathing ventilation equipment, the flow velocity corresponding to the breathing of the target object is estimated according to the obtained pressure value by obtaining the pressure value detected by the pressure detection unit, and the spontaneous breathing identification of the target object is carried out according to the estimated flow velocity. Therefore, even if the target object end is not provided with a flow sensor, the autonomous respiration of the target object with small intensity can be detected and identified, so that the accuracy of autonomous respiration identification of the target object is improved.
While the application has been described with reference to certain preferred embodiments, it will be understood by those skilled in the art that various changes and substitutions of equivalents may be made and equivalents will be apparent to those skilled in the art without departing from the scope of the application. Therefore, the protection scope of the application is subject to the protection scope of the claims.