CN114931371A - Method and device for measuring lung function index, electronic device and storage medium - Google Patents
Method and device for measuring lung function index, electronic device and storage medium Download PDFInfo
- Publication number
- CN114931371A CN114931371A CN202210570153.4A CN202210570153A CN114931371A CN 114931371 A CN114931371 A CN 114931371A CN 202210570153 A CN202210570153 A CN 202210570153A CN 114931371 A CN114931371 A CN 114931371A
- Authority
- CN
- China
- Prior art keywords
- lung function
- preset
- radar
- index
- signal
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
- A61B5/087—Measuring breath flow
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
- A61B5/091—Measuring volume of inspired or expired gases, e.g. to determine lung capacity
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
- A61B5/7225—Details of analog processing, e.g. isolation amplifier, gain or sensitivity adjustment, filtering, baseline or drift compensation
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Engineering & Computer Science (AREA)
- Medical Informatics (AREA)
- Surgery (AREA)
- Biophysics (AREA)
- Pathology (AREA)
- Physiology (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Veterinary Medicine (AREA)
- Molecular Biology (AREA)
- Physics & Mathematics (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Pulmonology (AREA)
- Signal Processing (AREA)
- Artificial Intelligence (AREA)
- Computer Vision & Pattern Recognition (AREA)
- Psychiatry (AREA)
- Power Engineering (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Abstract
The invention discloses a method and a device for measuring lung function indexes, electronic equipment and a storage medium, wherein the measuring method comprises the following steps: the method comprises the steps of collecting echo data of a target user during an expiration test according to a specified mode based on a preset radar device, processing the echo data to obtain a respiration signal, calculating a first lung function index based on the respiration signal, and correcting the first lung function index based on a preset correction function to obtain a corrected first lung function index. The invention solves the technical problem of inconvenient use caused by that the lung function index of the user can only be measured in a contact way in the related technology.
Description
Technical Field
The invention relates to the technical field of data processing, in particular to a method and a device for measuring lung function indexes, electronic equipment and a storage medium.
Background
Lung diseaseThe method is one of important tests for evaluating chest and lung diseases and respiratory physiology, and has important guiding significance for detecting pathological changes and pathological parts of the lung and the air duct, identifying reasons of dyspnea, evaluating the severity of diseases, prognosis, operation tolerance and the like. An important indicator in pulmonary function tests is the first second Forced expiratory volume in one second (FEV) 1 ) Percentage of occupational vital capacity (FVC), referred to as the one second Rate (FEV) 1 /FVC) which is used primarily to diagnose chronic obstructive pulmonary disease.
In the correlation technique, adopt the pulmonary function detector mostly to detect user's pulmonary function, however, the pulmonary function detector is all contact, requires that the person under test to paste the blow nozzle mouth and blows in order to measure, and it is very inconvenient to use.
In view of the above problems, no effective solution has been proposed.
Disclosure of Invention
The embodiment of the invention provides a method and a device for measuring lung function indexes, electronic equipment and a storage medium, which are used for at least solving the technical problem of inconvenient use caused by that the lung function indexes of a user can only be measured in a contact mode in the related technology.
According to an aspect of an embodiment of the present invention, there is provided a method for measuring a lung function index, including: acquiring echo data of a target user during an expiration test in a specified mode based on a preset radar device, wherein the preset radar device does not need to be in contact with the target user when acquiring the echo data; processing the echo data to obtain a respiration signal; calculating a first lung function indicator based on the respiratory signal; and correcting the first lung function index based on a preset correction function to obtain a corrected first lung function index.
Optionally, the step of acquiring echo data of the target user during the breath test according to a specified mode based on a preset radar device includes: sending a normal breathing instruction under the condition that the preset radar device is located at a position which is away from the preset distance value of the target user and is flush with the chest cavity of the target user; under the condition that the normal breathing of the target user reaches a preset time limit, sending a rapid expiration instruction after deep inspiration, and collecting radar echo data of the target user, wherein the radar echo data is at least data lasting for a first preset time period; characterizing the radar echo data as the echo data.
Optionally, the step of processing the echo data to obtain a respiratory signal includes: transforming the echo data into a distance dimensional complex signal; determining a range gate in which the chest of the target user is located in the distance dimensional complex signal, wherein the range gate represents a range of the user's chest relative to radar; extracting an original phase signal based on the range gate; performing preset unwrapping operation on the original phase signal to obtain an unwrapped phase signal; characterizing the phase signal as the respiration signal.
Optionally, the step of calculating a first lung function indicator based on the respiratory signal comprises: smoothing the respiration signal to obtain a target respiration signal, and determining an expiration starting point based on the target respiration signal; determining a maximum value point of the target respiration signal in a second preset time period based on the expiration starting point; calculating a first relative value based on the exhalation starting point and the maximum value point; determining all sampling points in the target respiration signal within a third preset time period based on the expiration starting point; calculating the amplitude difference between each sampling point in all the sampling points and the sampling point delayed for the preset time to obtain an amplitude difference set; determining a maximum amplitude difference based on the set of amplitude differences; characterizing the maximum amplitude difference as a second relative value; calculating the first lung function indicator based on the first relative value and the second relative value.
Optionally, the step of determining an exhalation starting point based on the target respiratory signal comprises: determining all minimum value points in a fourth preset time period based on the target respiration signal; determining all maxima points in the target respiratory signal; calculating the amplitude difference of the signal amplitude between each minimum value point in all the minimum value points and the most adjacent maximum value point to obtain an amplitude difference set; determining a target minimum value point indicated by the maximum amplitude difference value based on the amplitude difference value set; characterizing the target minimum point as the expiratory onset point.
Optionally, before modifying the first lung function index based on a preset modification function to obtain a modified first lung function index, the method further includes: calculating a first pulmonary function index and a second pulmonary function index based on historical samples in a fifth preset time period; performing linear fitting on the first lung function index and the second lung function index to obtain a linear fitting expression; calculating a linear fit between the first and second pulmonary function indicators; and establishing the preset correction function based on the linear fitting expression and the linear fitting degree.
Optionally, after modifying the first lung function index based on a preset modification function to obtain a modified first lung function index, the method further includes: representing a comparison result of the second lung function index and a preset threshold value as a real result; characterizing a comparison of the first lung function indicator with the preset threshold as a predicted result; calculating an index value of a performance index for performing lung function determination using the corrected first lung function index based on the real result and the predicted result, wherein the performance index at least includes: accuracy, sensitivity, specificity.
Optionally, the preset radar device is a millimeter wave radar.
According to another aspect of the embodiments of the present invention, there is also provided a lung function index measurement apparatus, including: the device comprises an acquisition unit and a control unit, wherein the acquisition unit is used for acquiring echo data of a target user during an expiration test in a specified mode based on a preset radar device, and the preset radar device does not need to be in contact with the target user when acquiring the echo data; the processing unit is used for processing the echo data to obtain a respiratory signal; a calculation unit for calculating a first lung function indicator based on the respiratory signal; and the correcting unit is used for correcting the first lung function index based on a preset correcting function to obtain a corrected first lung function index.
Optionally, the acquisition unit comprises: the first sending module is used for sending a normal breathing instruction under the condition that the preset radar device is located at a position which is away from the preset distance value of the target user and is flush with the chest cavity of the target user; the second sending module is used for sending a rapid expiration instruction after deep inspiration under the condition that the normal breathing of the target user reaches a preset time limit, and collecting radar echo data of the target user, wherein the radar echo data at least lasts for a first preset time period; a first characterization module to characterize the radar echo data as the echo data.
Optionally, the processing unit comprises: the first transformation module is used for transforming the echo data into a distance dimensional complex signal; a first determining module, configured to determine a range gate in the range dimensional complex signal where the chest of the target user is located, wherein the range gate represents a range of the chest of the user relative to a radar; a first extraction module for extracting an original phase signal based on the range gate; the first unwrapping module is used for carrying out preset unwrapping operation on the original phase signal to obtain an unwrapped phase signal; a second characterization module to characterize the phase signal as the respiration signal.
Optionally, the computing unit comprises: the second determining module is used for smoothing the breathing signal to obtain a target breathing signal and determining an exhalation starting point based on the target breathing signal; a third determining module, configured to determine a maximum point of the target respiratory signal within a second preset time period based on the expiratory starting point; a first calculating module for calculating a first relative value based on the expiratory start point and the maximum value point; a fourth determining module, configured to determine all sampling points in the target respiratory signal within a third preset time period based on the expiratory starting point; the second calculation module is used for calculating the amplitude difference between each sampling point in all the sampling points and the sampling point delayed by preset time to obtain an amplitude difference set; a fifth determining module, configured to determine a maximum amplitude difference based on the set of amplitude differences; a third characterization module for characterizing the maximum amplitude difference as a second relative value; a third calculation module for calculating the first lung function indicator based on the first relative value and the second relative value.
Optionally, the second determining module includes: the first determining submodule is used for determining all minimum value points in a fourth preset time period based on the target respiration signal; a second determining submodule, configured to determine all maximum value points in the target respiratory signal; the first calculation submodule is used for calculating the amplitude difference of the signal amplitude between each minimum value point of all the minimum value points and the most adjacent maximum value point to obtain an amplitude difference set; a third determining submodule, configured to determine, based on the set of amplitude difference values, a target minimum value point indicated by a maximum amplitude difference value; a first characterization submodule, configured to characterize the target minimum value point as the expiratory starting point.
Optionally, the measuring device further comprises: the fourth calculating module is used for calculating the first pulmonary function index and the second pulmonary function index based on historical samples in a fifth preset time period before the first pulmonary function index is corrected based on a preset correction function to obtain the corrected first pulmonary function index; the first fitting module is used for performing linear fitting on the first pulmonary function index and the second pulmonary function index to obtain a linear fitting expression; a fifth calculation module for calculating a linear fitness between the first lung function indicator and the second lung function indicator; and the first establishing module is used for establishing the preset correction function based on the linear fitting expression and the linear fitting degree.
Optionally, the measuring device further comprises: a fourth characterization module, configured to, after the first lung function index is corrected based on a preset correction function and the corrected first lung function index is obtained, characterize a comparison result of the second lung function index with a preset threshold as a real result; a fifth characterization module, configured to characterize a comparison result of the comparison between the first lung function index and the preset threshold as a prediction result; a sixth calculating module, configured to calculate, based on the real result and the predicted result, an index value of a performance index for performing lung function determination by using the corrected first lung function index, where the performance index at least includes: accuracy, sensitivity, specificity.
Optionally, the preset radar device is a millimeter wave radar.
According to another aspect of the embodiments of the present invention, there is also provided a computer-readable storage medium, where the computer-readable storage medium includes a stored computer program, and when the computer program runs, the apparatus where the computer-readable storage medium is located is controlled to execute the method for measuring a lung function index.
According to another aspect of embodiments of the present invention, there is also provided an electronic device, including one or more processors and a memory for storing one or more programs, wherein when the one or more programs are executed by the one or more processors, the one or more processors are caused to implement the method for measuring a lung function index described above.
In the disclosure, echo data of a target user during an exhalation test in a specified manner is acquired based on a preset radar device, the echo data is processed to obtain a respiration signal, a first pulmonary function index is calculated based on the respiration signal, and the first pulmonary function index is corrected based on a preset correction function to obtain a corrected first pulmonary function index. In this application, through predetermineeing radar installation, can need not to contact with the user, echo data when this user expiration test of direct acquisition, after handling, obtain respiratory signal, then, calculate the pulmonary function index through respiratory signal, and through the correction function, revise this pulmonary function index, thereby realize the motion condition of probing user's thorax under the condition of contactless user, obtain user's pulmonary function index, and then can only measure user pulmonary function index with contact among the correlation technique, lead to awkward technical problem.
Drawings
The accompanying drawings, which are included to provide a further understanding of the invention and are incorporated in and constitute a part of this application, illustrate embodiment(s) of the invention and together with the description serve to explain the invention without limiting the invention. In the drawings:
FIG. 1 is a flow chart of an alternative method of measuring a lung function index according to an embodiment of the present invention;
FIG. 2 is a schematic diagram of an alternative data acquisition scenario in accordance with an embodiment of the present invention;
FIG. 3 is a schematic illustration of an alternative radar exhalation signal in accordance with an embodiment of the present invention;
FIG. 4 is a graphical illustration of an alternative radar one-second rate indicator and pulmonary function instrument one-second rate indicator fit according to an embodiment of the invention;
FIG. 5 is a graphical illustration of an alternative modified radar one-second rate indicator and pulmonary function instrument one-second rate indicator fit according to an embodiment of the invention;
FIG. 6 is a flowchart of an alternative millimeter-wave radar-based non-contact lung function index measurement method according to an embodiment of the present invention;
fig. 7 is a schematic diagram of an alternative measurement device for lung function index according to an embodiment of the present invention.
Detailed Description
In order to make the technical solutions of the present invention better understood, the technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are only a part of the embodiments of the present invention, and not all of the embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
It should be noted that the terms "first," "second," and the like in the description and claims of the present invention and in the drawings described above are used for distinguishing between similar elements and not necessarily for describing a particular sequential or chronological order. It is to be understood that the data so used is interchangeable under appropriate circumstances such that the embodiments of the invention described herein are capable of operation in sequences other than those illustrated or described herein. Furthermore, the terms "comprises," "comprising," and "having," and any variations thereof, are intended to cover a non-exclusive inclusion, such that a process, method, system, article, or apparatus that comprises a list of steps or elements is not necessarily limited to those steps or elements expressly listed, but may include other steps or elements not expressly listed or inherent to such process, method, article, or apparatus.
The following embodiments of the invention can be applied to the scene of lung function index calculation, and provide a non-contact type lung function index measuring method based on millimeter wave radar. According to the method, radar echo data of a user during expiration in a specified mode can be collected through a millimeter wave radar, the data are processed to extract respiratory signals, then a radar one-second rate index is calculated by using the extracted respiratory signals, then a correction function of the radar one-second rate index is obtained on a small-batch data set by adopting a linear fitting method, and the accuracy, sensitivity and specificity indexes of obstructive breathing disorder judgment by using the millimeter wave radar on the small-batch data set are given.
The present invention will be described in detail with reference to examples.
Example one
According to an embodiment of the present invention, there is provided an embodiment of a method for measuring a lung function index, it is noted that the steps illustrated in the flowchart of the drawings may be performed in a computer system such as a set of computer executable instructions, and that although a logical order is illustrated in the flowchart, in some cases the steps illustrated or described may be performed in an order different than here.
Fig. 1 is a flow chart of an alternative method for measuring a lung function index according to an embodiment of the present invention, as shown in fig. 1, the method comprising the steps of:
and S101, acquiring echo data of a target user during an expiration test according to a specified mode based on a preset radar device, wherein the preset radar device does not need to be in contact with the target user when acquiring the echo data.
And step S102, processing the echo data to obtain a respiratory signal.
Step S103, based on the respiratory signal, calculates a first lung function index.
And step S104, correcting the first lung function index based on a preset correction function to obtain a corrected first lung function index.
Through the steps, echo data of a target user during an expiration test in a specified mode can be collected based on a preset radar device, the echo data are processed to obtain a respiration signal, a first lung function index is calculated based on the respiration signal, the first lung function index is corrected based on a preset correction function, and the corrected first lung function index is obtained. In the embodiment of the invention, the echo data of the user during the breath test can be directly collected without contacting the user through the preset radar device, a breath signal is obtained after processing, then the lung function index is calculated through the breath signal, and the lung function index is corrected through the correction function, so that the motion condition of the chest cavity of the user is detected under the condition of not contacting the user, the lung function index of the user is obtained, and the technical problem of inconvenient use caused by the fact that the user can only measure the lung function index in a contact mode in the related technology is solved.
The following describes the embodiments of the present invention in detail with reference to the above steps.
And S101, acquiring echo data of a target user during an expiration test according to a specified mode based on a preset radar device, wherein the preset radar device does not need to be in contact with the target user when acquiring the echo data. Optionally, the preset radar device is a millimeter wave radar.
In the embodiment of the invention, the preset radar device can be a millimeter wave radar which can receive electromagnetic waves reflected by a user, can detect the motion condition of the chest cavity of the user under the condition of not contacting the user, and further analyzes the lung function condition of the detected person. This embodiment can gather the echo data when the target user carries out expiration test according to the appointed mode through the millimeter wave radar to when gathering echo data, the millimeter wave radar need not to contact with the user, and convenience of customers uses.
Optionally, based on a preset radar device, the method includes the step of collecting echo data of a target user during an exhalation test according to a specified mode, and includes: sending a normal breathing instruction under the condition that the preset radar device is located at a position which is away from the preset distance value of the target user and is flush with the chest cavity of the target user; sending a rapid expiration instruction after deep inspiration under the condition that the normal breathing of a target user reaches a preset time limit, and collecting radar echo data of the target user, wherein the radar echo data is at least data lasting for a first preset time period; the radar echo data is characterized as echo data.
In the embodiment of the present invention, fig. 2 is a schematic diagram of an alternative data acquisition scenario according to an embodiment of the present invention, as shown in fig. 2, a measured person (i.e., a target user) may sit on a chair with a backrest, attach the back to the backrest tightly, place two hands at the back of the body, place a millimeter wave radar at a preset distance (e.g., about 75 cm) in front of the chest of the measured person, adjust the height of the radar to be level with the chest of the measured person, and ensure that the radar transmitting and receiving antennas are opposite to the chest of the measured person.
In the present example, the breath test procedure was as follows: in the case that it is confirmed that the preset radar device is located at a position distant from the preset distance value of the target user and is flush with the chest of the target user, a normal breathing instruction is issued (for example, a sound of "please breathe for 15 seconds normally") and the testee hears the instruction and then breathes normally for a certain period of time (that is, the target user breathes normally within a preset time limit), and in the case that the normal breathing of the target user reaches the preset time limit, a deep breathing instruction is issued (for example, a sound of "please inhale deeply at the fastest speed and exert the maximum force and exhale deeply at the fastest speed and last for 6 seconds after inhaling the foot) and radar echo data of the target user is collected (the radar echo data is at least data lasting for the first preset time period (for example, 10 seconds)), and then the user can breathe normally for several times. In the whole expiration test process of the embodiment, the other parts of the body of the tested person are kept stable, and the millimeter wave radar is used for collecting the radar echo data of the tested person in the expiration test process (namely, the radar echo data can be represented as echo data).
Alternatively, the radar may transmit a Frequency Modulated Continuous Wave (FMCW) signal, the FMCW signal in one period is referred to as a Chirp signal Chirp (i.e., swept cosine signal), the modulation mode of the signal may be set to be a sawtooth wave, and the period of Chirp may be set to be T chirp Second, N continuously transmitted Chirps form a frame with a frame period of T frame And second. Echo signals received by a radar and transmitting signals are mixed to obtain difference frequency signals, and digitized echo data can be obtained after the difference frequency signals are subjected to high-pass filtering, low-noise amplification, ADC (analog-to-digital converter) sampling and other processing.
And step S102, processing the echo data to obtain a respiratory signal.
In the embodiment of the invention, the original echo data collected by the radar can be processed to extract the respiratory signal of the tested person.
Optionally, the step of processing the echo data to obtain a respiratory signal includes: converting the echo data into a distance dimensional complex signal; determining a range gate where the chest of the target user is located in the distance dimensional complex signal, wherein the range gate represents a range of the chest of the user relative to the radar; extracting an original phase signal based on a range gate; performing preset unwrapping operation on the original phase signal to obtain an unwrapped phase signal; the phase signal is characterized as a respiration signal.
In the embodiment of the present invention, fast time processing may be performed to convert radar raw echo data into a distance dimension (i.e., to convert echo data into a distance dimension complex signal), then a range gate where a user's chest is located in the radar echo data (i.e., a range gate where the chest of a target user in the distance dimension complex signal is located is determined, the range gate represents a distance range of the user's chest with respect to the radar), and a distance resolution represents a minimum distance (or may be folded into time) interval that two targets can be separated in the radar echo, then an original phase signal is extracted along the range gate (i.e., the original phase signal is extracted based on the range gate), and the extracted original phase signal is unwrapped to obtain an unwrapped phase signal, which is a respiratory signal (i.e., the original phase signal is subjected to a preset unwrapping operation to obtain an unwrapped phase signal, and characterizing the phase signal as a respiration signal) including information related to the respiratory motion of the subject, as follows:
firstly, processing such as direct current removal and Fast Fourier Transform (FFT) is carried out on echo signals received in each Chirp to obtain distance dimension complex signals, and original phase signals containing respiratory motion information of a measured person are extracted by using the distance dimension complex signals corresponding to the first Chirp of each frame, wherein the processing specifically comprises the following steps: firstly, removing static clutter in a distance dimensional complex signal along a frame time dimension, then searching a power strongest point in a limited distance range along the distance dimension, taking a corresponding distance gate as an alternative distance gate for extracting a respiratory signal, calculating the median of all the alternative distance gates in the whole acquisition time for ensuring the reliability of the selected respiratory signal extraction distance gate, taking the median as a final respiratory signal extraction distance gate, then extracting the phase angle of the selected distance gate in the distance dimensional complex signal corresponding to the first Chirp of each frame to obtain an original phase signal containing respiratory motion of a measured person, and performing unwrapping operation on the original phase signal to obtain the respiratory signal.
Step S103, calculating a first lung function index based on the respiratory signal.
Optionally, the step of calculating a first lung function indicator based on the respiratory signal comprises: smoothing the breathing signal to obtain a target breathing signal, and determining an exhalation starting point based on the target breathing signal; determining a maximum value point of the target respiration signal in a second preset time period based on the expiration starting point; calculating a first relative value based on the expiratory start point and the maximum point; determining all sampling points in the target respiration signal within a third preset time period based on the expiration starting point; calculating the amplitude difference between each sampling point in all the sampling points and the sampling point delayed for the preset time to obtain an amplitude difference set; determining a maximum amplitude difference based on the amplitude difference set; characterizing the largest amplitude difference as a second relative value; based on the first relative value and the second relative value, a first lung function indicator is calculated.
In an embodiment of the invention, the expiration start point may be first determined in the target respiration signal, fig. 3 is a schematic diagram of an alternative radar expiration test signal according to an embodiment of the invention, as shown in fig. 3, the radar expiration test signal is a curve with time t/s as abscissa (from 0 to 10 in fig. 3, the abscissa with interval unit set to 1), and distance d/cm as ordinate (from-1 to 3 in fig. 3, the ordinate with interval unit set to 0.5).
In this embodiment, the radar FEV may be calculated according to the expiratory start point 1 Relative value (second relative value) and radar FVC relative value (first relative value) to obtain radar one-second rate estimated value (radar FEV) 1 the/FVC index, which may be referred to as the first pulmonary function index in this embodiment), is as follows:
the relative value of the radar FVC can be calculated first, based on the obtained starting point t of expiration start Then, find the maximum point s (t) in the second preset time period (e.g. in 6 seconds) thereafter top ) The relative value of the radar FVC is calculated by the following formula (1):
FVC REL ＝s(t top )-s(t start ) (1)；
recalculating radar FEV 1 Can assume that the number of sampling points of the respiratory signal within 1 second is f s Based on the starting point t of expiration start The amplitude difference from the point delayed by a preset time (which may be set to 1 second in the present embodiment) is calculated by the following formula (2):
Δ 0 ＝s(t start +f s )-s(t start ) (2)；
similarly, for the expiratory start point t start The same operation is performed for all points within a third preset time period (e.g., 1 second), which is calculated by the following formula (3):
Δ k ＝s(t start +k+f s )-s(t start +k)，k＝0，1，...，f s -1 (3)；
selecting the largest amplitude difference as the radar FEV 1 Relative value of (i), i.e.
The radar one-second rate index can be obtained by the following formula (4):
optionally, the step of determining an exhalation starting point based on the target respiration signal comprises: determining all minimum value points in a fourth preset time period based on the target respiration signal; determining all maximum points in the target respiratory signal; calculating the amplitude difference value of the signal amplitude between each minimum value point in all the minimum value points and the most adjacent maximum value point after the minimum value point to obtain an amplitude difference value set; determining a target minimum value point indicated by the maximum amplitude difference value based on the amplitude difference value set; the target minimum point is characterized as the expiratory onset.
In the embodiment of the present invention, gaussian smoothing may be performed on the expiratory signal in the first preset time period to obtain a smoothed signal s (t) (i.e. a target respiratory signal), where t represents a discrete time point index, all minimum value points in a preset time period (e.g. in the previous 4 seconds) before the signal s (t), and all maximum value points in the signal s (t) are found, and for each minimum value point s (t), the minimum value points s (t) are obtained min，i ) Then find the nearest maximum point s (t) max，i ) The difference in signal amplitude between two points (i.e., the amplitude difference in signal amplitude between each minimum point and the closest maximum point after it) is calculated by the following formula (5):
Δh i ＝s(t max，i )-s(t min，i ) (5)；
selecting the minimum value point corresponding to the index i which maximizes the amplitude difference as the starting point t of expiration start That is to say that,
t start ＝t min，m where m is argmax i Δh i 。
Optionally, before the first lung function index is modified based on a preset modification function and the modified first lung function index is obtained, the method further includes: calculating a first pulmonary function index and a second pulmonary function index based on historical samples in a fifth preset time period; performing linear fitting on the first lung function index and the second lung function index to obtain a linear fitting expression; calculating a linear fitness between the first pulmonary function index and the second pulmonary function index; and establishing a preset correction function based on the linear fitting expression and the linear fitting degree.
In the embodiment of the invention, the radar one-second rate index (FEV) obtained for a small batch of samples (namely historical samples in a fifth preset time period) 1 /FVC) RADAR (i.e., first lung function index) and pulmonary function Meter one second Rate index (FEV) 1 /FVC) TRUE (i.e., the second lung function index) and calculating the degree of linear fit R 2 The method is used as a standard for evaluating the linear correlation between the radar and the accuracy of radar measurement, and specifically comprises the following steps:
according to the small-batch data set, the obtained linear fitting expression is as follows:
(FEV 1 /FVC) RADAR ＝1.018*(FEV 1 /FVC) TRUE -0.0806；
calculated linear degree of fit R 2 ＝0.8645。
The correction function (i.e. the preset correction function) of the radar one-second rate index obtained according to the linear fitting result is:
(FEV 1 /FVC) REV ＝[(FEV 1 /FVC) RADAR +0.0806]/1.018；
wherein (FEV) 1 /FVC) REV Is the corrected radar one-second rate index (i.e. the first lung function index after correction). In this embodiment, the corrected radar one-second rate index may be recorded as 100% when it exceeds 100%.
FIG. 4 is a schematic diagram of alternative radar one-second rate indicator and pulmonary function instrument one-second rate indicator fitting results according to an embodiment of the inventionAs shown in FIG. 4, with FEV 1 the/FVC byLung Instrument (i.e., one-second Rate index of pulmonary function Instrument) is plotted on the abscissa (0 to 100 in FIG. 4, and the unit of interval is set to 20 on the abscissa) at FEV 1 (i.e., radar one second rate index) as ordinate (ordinate from 0 to 100 in FIG. 4, interval unit set to 10), FEV was fitted 1 the/FVC Radar-lung function instrument contrast curve, where the asterisk indicates DataPoint (i.e., data point), the horizontal line indicates fittedcurre (i.e., fitted curve), and the point indicates Radar ═ LungInstrument.
FIG. 5 is a graphical representation of an alternative modified radar one-second rate indicator and pulmonary function instrument one-second rate indicator fit, as shown in FIG. 5, at FEV, in accordance with an embodiment of the present invention 1 the/FVC byLung Instrument (i.e., one-second Rate index of pulmonary function Instrument) is plotted on the abscissa (e.g., the abscissa of FIG. 5 from 0 to 100 with 20 interval units) at FEV 1 the/FVC byRaar (i.e., the radar one-second rate index) is plotted on the ordinate (e.g., on the ordinate from 0 to 100 in FIG. 5 with 10 units of interval units), and FEV is fitted 1 the/FVC Radar-lung function instrument contrast curve (after correction), where the asterisk indicates DataPoint (i.e., data point), the horizontal line indicates FittedCurve (i.e., fitted curve), and the point indicates Radar ═ lung instrument.
And step S104, correcting the first lung function index based on a preset correction function to obtain a corrected first lung function index.
In the embodiment of the present invention, the first lung function index may be corrected by using the obtained correction function, so as to obtain a corrected first lung function index.
Optionally, after the first lung function index is modified based on a preset modification function, and the modified first lung function index is obtained, the method further includes: representing a comparison result of the second lung function index and a preset threshold value as a real result; representing a comparison result of the first lung function index and a preset threshold value as a prediction result; calculating an index value of a performance index for performing lung function determination using the corrected first lung function index based on the true result and the predicted result, wherein the performance index at least includes: accuracy, sensitivity, specificity.
In the inventionIn an embodiment, a comparison result of the second pulmonary function index compared with the preset threshold may be characterized as a real result, a comparison result of the first pulmonary function index compared with the preset threshold may be characterized as a predicted result, and under the condition that the preset threshold is 70%, the obstructive ventilatory disturbance may be determined, specifically: index FEV of lung function instrument in one second 1 (iv) obstructive ventilatory disturbance is determined for cases with/FVC < 70%, and corrected radar one second Rate index (FEV) 1 /FVC) REV Determining obstructive airway obstruction as prediction result, and determining lung function instrument one second rate index (FEV) 1 /FVC) TRUE And (4) judging whether the result of the obstructive ventilatory disturbance is a real result, and calculating the indexes of accuracy, sensitivity and specificity.
Table 1 shows an optional classification of determination results of obstructive ventilatory disorder in this embodiment, as shown in table 1:
TABLE 1
Wherein TP represents the number of truly non-obstacle and predicted non-obstacle, FP represents the number of truly non-obstacle and predicted non-obstacle, TN represents the number of truly non-obstacle and predicted non-obstacle, and FN represents the number of truly non-obstacle and predicted non-obstacle.
Based on the real result and the predicted result, a specific calculation formula for calculating the index value of the performance index for performing the lung function determination using the corrected first lung function index is as follows:
the accuracy is as follows:
sensitivity (barrier-free recall):
specificity (impaired recall):
this is described in detail below in connection with an alternative embodiment.
Fig. 6 is a flowchart of an alternative millimeter-wave radar-based non-contact lung function index measurement method according to an embodiment of the present invention, and as shown in fig. 6, the method includes the following steps:
(1) and (3) collecting radar echo data of the human body in the expiration test according to a specified mode by using a millimeter wave radar.
The testee sits on a chair with a backrest, the back of the chair is tightly attached to the backrest, two hands of the chair are placed on the rear side of the body of the testee, the millimeter wave radar is arranged at a position about 75 cm in front of the chest of the testee, the height of the radar is adjusted to enable the radar to be flush with the chest of the testee, and the radar transmitting and receiving antenna is guaranteed to be over against the chest of the testee. The breath test procedure was as follows: after hearing the instruction of 'normal breathing', the testee breathes normally for a period of time, then after hearing the instruction of 'deep inhalation and then rapid exhalation', the testee breathes deeply at the fastest speed, breathes deeply at the fastest speed after inhaling the feet and lasts for 6 seconds (called 6 seconds exhalation), and then breathes normally for a plurality of times. The tested person keeps other parts of the body stable in the whole expiration test process, and the millimeter wave radar is used for collecting radar echo data within 10 seconds after the instruction of 'breathing in deeply and breathing out quickly' is sent out by the tested person.
(2) A respiration signal is extracted from the radar echo data.
And processing the original echo data acquired by the radar and extracting the respiratory signal of the tested person.
(3) And calculating a radar one-second rate index by using the extracted respiratory signal.
Firstly, performing Gaussian smoothing on an original respiration signal of a 10-second segment to obtain a smoothed signal s (t), wherein t represents a discrete time point index, finding all minimum value points in the first 4 seconds of the signal s (t), and then finding outAll maxima in signal s (t), for each minima s (t) min，i ) Then find the nearest maximum point s (t) max，i ) The difference in the amplitudes of the signals at the two points, i.e.,
Δh i ＝s(t max，i )-s(t min，i )。
selecting the minimum value point corresponding to the index i which maximizes the amplitude difference as the starting point t of 6 seconds expiration start That is to say that,
t start ＝t min，m where m is argmax i Δh i 。
Second, calculating the radar FEV 1 the/FVC index. Firstly, calculating the relative value of the radar FVC, and for the 6-second expiration starting point t obtained in the first step start Find the maximum point s (t) within 6 seconds thereafter top ) The relative value of the radar FVC, i.e.,
FVC REL ＝s(t top )-s(t start )；
secondly, calculating the radar FEV 1 The relative value of (a) is set as f sampling points of the respiratory signal in 1 second s For the 6 second expiratory start in the first step t start The amplitude difference from the point after 1 second, that is,
Δ 0 ＝s(t start +f s )-s(t start )；
similarly, for a 6 second exhalation onset t start The same operation was performed for all points in the last 1 second, and the calculation formula was as follows:
Δ k ＝s(t start +k+f s )-s(t start +k)，k＝0，1，...，f s -1；
selecting the largest amplitude difference of 1 second as the radar FEV 1 The relative values of (a) to (b), i.e.,
Thus, a radar one-second rate index can be obtained:
(4) and calculating a correction function of the radar one-second rate index by taking the lung function instrument one-second rate index as a standard.
Radar one-second Rate index (FEV) obtained for Small batch samples 1 /FVC) RADAR One second Rate index (FEV) of Lung function Instrument 1 /FVC) TRUE Performing linear fitting, and calculating the degree of linear fitting R 2 It is used as a standard for evaluating the linear correlation between the two and the accuracy of radar measurement.
According to the small-batch data set, the obtained linear fitting expression is as follows:
(FEV 1 /FVC) RADAR ＝1.018*(FEV 1 /FVC) TRUE -0.0806，R 2 ＝0.8645；
the correction function of the radar one-second rate index obtained according to the linear fitting result is as follows:
(FEV 1 /FVC) REV ＝[(FEV 1 /FVC) RADAR +0.0806]/1.018；
wherein (FEV) 1 /FVC) REV The corrected radar one-second rate index is obtained.
In this embodiment, the lung function instrument can be used as the one-second rate index FEV 1 (iv) obstructive ventilatory disturbance is determined for cases with/FVC < 70%, and corrected radar one second Rate index (FEV) 1 /FVC) REV Determining obstructive airway obstruction as prediction result, and determining lung function instrument one second rate index (FEV) 1 /FVC) TRUE And (4) judging whether the result of the obstructive ventilatory disturbance is a real result, and calculating index values such as accuracy, sensitivity, specificity and the like.
In the embodiment of the invention, radar echo data of a user during expiration test in a specified mode can be collected through a millimeter wave radar, the data is processed to extract a respiratory signal, then a radar one-second rate index is calculated by using the extracted respiratory signal, then a linear fitting method is adopted to obtain a correction function of the radar one-second rate index, and the accuracy, sensitivity and specificity indexes of obstructive ventilation disorder judgment by using the millimeter wave radar are given, so that the aim of detecting the motion condition of the user chest under the condition of not contacting the user and obtaining the lung function index of the user can be realized.
Example two
The device for measuring a lung function index provided in this embodiment includes a plurality of implementation units, and each implementation unit corresponds to each implementation step in the first embodiment.
Fig. 7 is a schematic diagram of an alternative measurement apparatus for lung function index according to an embodiment of the present invention, and as shown in fig. 7, the measurement apparatus may include: an acquisition unit 70, a processing unit 71, a calculation unit 72, a correction unit 73, wherein,
the acquisition unit 70 is used for acquiring echo data of a target user during an expiration test in a specified manner based on a preset radar device, wherein the preset radar device does not need to be in contact with the target user during the acquisition of the echo data;
the processing unit 71 is configured to process the echo data to obtain a respiration signal;
a calculation unit 72 for calculating a first lung function index based on the breathing signal;
the correcting unit 73 is configured to correct the first lung function index based on a preset correction function, so as to obtain a corrected first lung function index.
The measuring device can acquire echo data of a target user during an expiration test in a specified mode through the acquisition unit 70 based on a preset radar device, process the echo data through the processing unit 71 to obtain a respiration signal, calculate a first pulmonary function index through the calculation unit 72 based on the respiration signal, and correct the first pulmonary function index through the correction unit 73 based on a preset correction function to obtain a corrected first pulmonary function index. In the embodiment of the invention, the preset radar device can directly collect echo data of a user during breath test without contacting the user, a breath signal is obtained after processing the echo data, then the lung function index is calculated through the breath signal, and the lung function index is corrected through a correction function, so that the motion condition of the chest cavity of the user is detected under the condition of not contacting the user, the lung function index of the user is obtained, and the technical problem of inconvenient use caused by the fact that the lung function index of the user can only be measured in a contact mode in the related technology is solved.
Optionally, the collecting unit includes: the first sending module is used for sending a normal breathing instruction under the condition that the preset radar device is located at a position which is away from a preset distance value of a target user and is flush with the chest cavity of the target user; the second sending module is used for sending a rapid expiration instruction after deep inspiration under the condition that the normal breathing of the target user reaches a preset time limit, and collecting radar echo data of the target user, wherein the radar echo data at least are data lasting for a first preset time period; the first characterization module is used for characterizing the radar echo data into echo data.
Optionally, the processing unit includes: the first conversion module is used for converting the echo data into a distance dimensional complex signal; the first determination module is used for determining a range gate where the chest cavity of the target user is located in the range dimensional complex signal, wherein the range gate represents the range of the chest cavity of the user relative to the radar; a first extraction module for extracting an original phase signal based on a range gate; the first unwrapping module is used for carrying out preset unwrapping operation on the original phase signal to obtain an unwrapped phase signal; and a second characterization module for characterizing the phase signal as a respiration signal.
Optionally, the computing unit includes: the second determination module is used for smoothing the breathing signal to obtain a target breathing signal and determining an expiration starting point based on the target breathing signal; the third determination module is used for determining a maximum value point of the target breathing signal in a second preset time period based on the expiration starting point; a first calculating module, configured to calculate a first relative value based on the expiratory start point and the maximum value point; the fourth determination module is used for determining all sampling points in a third preset time period in the target breathing signal based on the expiration starting point; the second calculation module is used for calculating the amplitude difference between each sampling point in all the sampling points and the sampling point delayed by the preset time to obtain an amplitude difference set; a fifth determining module, configured to determine a maximum amplitude difference based on the amplitude difference set; a third characterization module for characterizing the maximum amplitude difference as a second relative value; a third calculation module for calculating the first lung function indicator based on the first relative value and the second relative value.
Optionally, the second determining module includes: the first determining submodule is used for determining all minimum value points in a fourth preset time period based on the target respiration signal; the second determining submodule is used for determining all maximum value points in the target respiratory signal; the first calculation submodule is used for calculating the amplitude difference of the signal amplitude between each minimum value point in all the minimum value points and the most adjacent maximum value point to obtain an amplitude difference set; a third determining submodule, configured to determine, based on the amplitude difference set, a target minimum value point indicated by the maximum amplitude difference; and the first characterization submodule is used for characterizing the target minimum value point as an expiratory starting point.
Optionally, the measuring device further includes: the fourth calculation module is used for calculating the first lung function index and the second lung function index based on historical samples in a fifth preset time period before the first lung function index is corrected based on the preset correction function to obtain the corrected first lung function index; the first fitting module is used for performing linear fitting on the first lung function index and the second lung function index to obtain a linear fitting expression; a fifth calculation module for calculating a linear fitness between the first lung function index and the second lung function index; and the first establishing module is used for establishing a preset correction function based on the linear fitting expression and the linear fitting degree.
Optionally, the measuring device further comprises: the fourth characterization module is used for modifying the first lung function index based on a preset modification function to obtain a modified first lung function index, and then characterizing a comparison result of the second lung function index and a preset threshold value as a real result; the fifth characterization module is used for characterizing a comparison result of the first lung function index and a preset threshold value as a prediction result; a sixth calculating module, configured to calculate, based on the real result and the predicted result, an index value of a performance index for performing lung function determination using the corrected first lung function index, where the performance index at least includes: accuracy, sensitivity, specificity.
Optionally, the preset radar device is a millimeter wave radar.
The measuring device may further include a processor and a memory, and the acquiring unit 70, the processing unit 71, the calculating unit 72, the correcting unit 73, and the like are stored in the memory as program units, and the processor executes the program units stored in the memory to implement corresponding functions.
The processor comprises a kernel, and the kernel calls the corresponding program unit from the memory. The kernel can be set to be one or more than one, and the first lung function index is corrected based on a preset correction function by adjusting kernel parameters to obtain a corrected first lung function index.
The memory may include volatile memory in a computer readable medium, Random Access Memory (RAM) and/or nonvolatile memory such as Read Only Memory (ROM) or flash memory (flash RAM), and the memory includes at least one memory chip.
The present application further provides a computer program product adapted to perform a program for initializing the following method steps when executed on a data processing device: the method comprises the steps of collecting echo data of a target user during an expiration test according to a specified mode based on a preset radar device, processing the echo data to obtain a respiration signal, calculating a first pulmonary function index based on the respiration signal, and correcting the first pulmonary function index based on a preset correction function to obtain a corrected first pulmonary function index.
According to another aspect of the embodiments of the present invention, there is also provided a computer-readable storage medium, which includes a stored computer program, wherein when the computer program runs, the apparatus where the computer-readable storage medium is located is controlled to execute the above-mentioned method for measuring a lung function index.
According to another aspect of embodiments of the present invention, there is also provided an electronic device, including one or more processors and a memory for storing one or more programs, wherein the one or more programs, when executed by the one or more processors, cause the one or more processors to implement the above-mentioned lung function index measurement method.
The above-mentioned serial numbers of the embodiments of the present invention are merely for description and do not represent the merits of the embodiments.
In the above embodiments of the present invention, the descriptions of the respective embodiments have respective emphasis, and for parts that are not described in detail in a certain embodiment, reference may be made to related descriptions of other embodiments.
In the embodiments provided in the present application, it should be understood that the disclosed technology can be implemented in other ways. The above-described embodiments of the apparatus are merely illustrative, and for example, the division of the units may be a logical division, and in actual implementation, there may be another division, for example, multiple units or components may be combined or integrated into another system, or some features may be omitted, or not executed. In addition, the shown or discussed coupling or direct coupling or communication connection between each other may be an indirect coupling or communication connection through some interfaces, units or modules, and may be electrical or in other forms.
The units described as separate parts may or may not be physically separate, and parts displayed as units may or may not be physical units, may be located in one place, or may be distributed on a plurality of units. Some or all of the units can be selected according to actual needs to achieve the purpose of the solution of the embodiment.
In addition, functional units in the embodiments of the present invention may be integrated into one processing unit, or each unit may exist alone physically, or two or more units are integrated into one unit. The integrated unit may be implemented in the form of hardware, or may also be implemented in the form of a software functional unit.
The integrated unit, if implemented in the form of a software functional unit and sold or used as a stand-alone product, may be stored in a computer readable storage medium. Based on such understanding, the technical solution of the present invention may be embodied in the form of a software product, which is stored in a storage medium and includes instructions for causing a computer device (which may be a personal computer, a server, or a network device) to execute all or part of the steps of the method according to the embodiments of the present invention. And the aforementioned storage medium includes: a U-disk, a Read-Only Memory (ROM), a Random Access Memory (RAM), a removable hard disk, a magnetic or optical disk, and other various media capable of storing program codes.
The foregoing is only a preferred embodiment of the present invention, and it should be noted that, for those skilled in the art, various modifications and decorations can be made without departing from the principle of the present invention, and these modifications and decorations should also be regarded as the protection scope of the present invention.
Claims (11)
1. A method for measuring a lung function index, comprising:
acquiring echo data of a target user during a breath test in a specified mode based on a preset radar device, wherein the preset radar device does not need to be in contact with the target user during the acquisition of the echo data;
processing the echo data to obtain a respiration signal;
calculating a first lung function indicator based on the respiratory signal;
and correcting the first lung function index based on a preset correction function to obtain a corrected first lung function index.
2. The measuring method according to claim 1, wherein the step of collecting echo data of the target user when performing the exhalation test in a specified manner based on a preset radar device comprises:
sending a normal breathing instruction under the condition that the preset radar device is located at a position which is away from the preset distance value of the target user and is flush with the chest cavity of the target user;
sending a rapid expiration instruction after deep inspiration under the condition that the normal breathing of the target user reaches a preset time limit, and collecting radar echo data of the target user, wherein the radar echo data is at least data lasting for a first preset time period;
characterizing the radar echo data as the echo data.
3. The method of claim 1, wherein the step of processing the echo data to obtain a respiration signal comprises:
transforming the echo data into a distance dimensional complex signal;
determining a range gate in which the chest of the target user is located in the distance dimensional complex signal, wherein the range gate represents a range of the user's chest relative to radar;
extracting an original phase signal based on the range gate;
performing preset unwrapping operation on the original phase signal to obtain an unwrapped phase signal;
characterizing the phase signal as the respiration signal.
4. The measurement method according to claim 1, wherein the step of calculating a first lung function indicator based on the respiration signal comprises:
smoothing the respiration signal to obtain a target respiration signal, and determining an expiration starting point based on the target respiration signal;
determining a maximum value point of the target respiration signal in a second preset time period based on the expiration starting point;
calculating a first relative value based on the expiratory start point and the maximum point;
determining all sampling points in the target respiration signal within a third preset time period based on the expiration starting point;
calculating the amplitude difference between each sampling point in all the sampling points and the sampling point delayed for the preset time to obtain an amplitude difference set;
determining a maximum amplitude difference based on the set of amplitude differences;
characterizing the maximum amplitude difference as a second relative value;
calculating the first lung function indicator based on the first relative value and the second relative value.
5. The measurement method according to claim 4, wherein the step of determining an exhalation starting point based on the target respiration signal comprises:
determining all minimum value points in a fourth preset time period based on the target respiration signal;
determining all maximum points in the target respiratory signal;
calculating the amplitude difference value of the signal amplitude between each minimum value point in all the minimum value points and the most adjacent maximum value point after the minimum value point to obtain an amplitude difference value set;
determining a target minimum value point indicated by the maximum amplitude difference value based on the amplitude difference value set;
characterizing the target minimum point as the expiratory onset point.
6. The measurement method according to claim 1, before modifying the first lung function indicator based on a preset modification function to obtain a modified first lung function indicator, further comprising:
calculating a first pulmonary function index and a second pulmonary function index based on historical samples in a fifth preset time period;
performing linear fitting on the first pulmonary function index and the second pulmonary function index to obtain a linear fitting expression;
calculating a linear fit between the first and second pulmonary function indicators;
and establishing the preset correction function based on the linear fitting expression and the linear fitting degree.
7. The measurement method according to claim 6, further comprising, after modifying the first lung function indicator based on a preset modification function to obtain a modified first lung function indicator:
representing a comparison result of the second lung function index and a preset threshold value as a real result;
characterizing a comparison of the first lung function indicator with the preset threshold as a predicted result;
calculating an index value of a performance index for performing lung function determination using the corrected first lung function index based on the real result and the predicted result, wherein the performance index at least includes: accuracy, sensitivity, specificity.
8. The measurement method according to any one of claims 1 to 7, characterized in that the preset radar means is a millimeter wave radar.
9. A lung function index measurement device, comprising:
the device comprises an acquisition unit and a control unit, wherein the acquisition unit is used for acquiring echo data of a target user during an expiration test in a specified mode based on a preset radar device, and the preset radar device does not need to be in contact with the target user when acquiring the echo data;
the processing unit is used for processing the echo data to obtain a respiratory signal;
a calculation unit for calculating a first lung function indicator based on the respiratory signal;
and the correcting unit is used for correcting the first lung function index based on a preset correcting function to obtain a corrected first lung function index.
10. A computer-readable storage medium, comprising a stored computer program, wherein the computer program, when executed, controls an apparatus in which the computer-readable storage medium is located to perform the method for measuring a lung function index according to any one of claims 1 to 8.
11. An electronic device, comprising one or more processors and memory for storing one or more programs, wherein the one or more programs, when executed by the one or more processors, cause the one or more processors to implement the method of measuring a lung function index of any one of claims 1 to 8.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202210570153.4A CN114931371A (en) | 2022-05-24 | 2022-05-24 | Method and device for measuring lung function index, electronic device and storage medium |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202210570153.4A CN114931371A (en) | 2022-05-24 | 2022-05-24 | Method and device for measuring lung function index, electronic device and storage medium |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN114931371A true CN114931371A (en) | 2022-08-23 |
Family
ID=82865371
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202210570153.4A Pending CN114931371A (en) | 2022-05-24 | 2022-05-24 | Method and device for measuring lung function index, electronic device and storage medium |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN114931371A (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN116369898A (en) * | 2023-06-06 | 2023-07-04 | 青岛市第五人民医院 | Respiratory data reminding system for critical diseases |
-
2022
- 2022-05-24 CN CN202210570153.4A patent/CN114931371A/en active Pending
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN116369898A (en) * | 2023-06-06 | 2023-07-04 | 青岛市第五人民医院 | Respiratory data reminding system for critical diseases |
| CN116369898B (en) * | 2023-06-06 | 2024-02-20 | 青岛市第五人民医院 | Respiratory data reminding system for critical diseases |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| Jezewski et al. | A novel technique for fetal heart rate estimation from Doppler ultrasound signal | |
| EP3413076B1 (en) | Mri involving the generation of a physiological motion signal using a pilot tone navigator | |
| JP5848469B1 (en) | Biological condition detection device | |
| WO2014205396A1 (en) | Systems and methods for estimating changes in inhalation-exhalation ratios using frequency harmonics | |
| US9345453B2 (en) | Lung ventilation measurements using ultrasound | |
| US11096630B2 (en) | Generating a movement signal of a part of the human or animal body | |
| CA2464029A1 (en) | Non-invasive ventilation monitor | |
| CA2553685A1 (en) | Method and system for analysing respiratory tract air flow | |
| JP2008520384A (en) | Method and system for real time determination of respiratory rate with limited processor resources | |
| EP2465560B1 (en) | Apparatus for the automatic control of ventilation phases based on pneumatic and non-pneumatic signals | |
| CN103800003A (en) | ECG detection method and detector | |
| CN103284743B (en) | Determine the method and device of marker location and patient respiratory curve | |
| WO2016104538A1 (en) | Respiratory status estimation apparatus, portable equipment, wearable device, program, medium, respiratory status estimation method, and respiratory status estimator | |
| EP2368492A1 (en) | A method for estimating parameters indicative of a heart performance, a radar system and a computer program product | |
| US10463311B2 (en) | Multi-channel ballistocardiography with cepstrum smoothing and quality-based dynamic channel selection | |
| CN112842321B (en) | Lung ventilation function detection method, device and medium based on flow-volume loop diagram | |
| CN114931371A (en) | Method and device for measuring lung function index, electronic device and storage medium | |
| KR20170055307A (en) | Heartbeat-signal Processing Method for Ultrasonic Doppler Fetal monitor | |
| KR101827522B1 (en) | Apparatus and method for measuring heart rate through non-contact | |
| US20190269350A1 (en) | Respiratory state estimation apparatus, respiratory state estimation method, and program recording medium | |
| KR101696791B1 (en) | Pulmonary function test apparatus using chest impedance and thereof method | |
| CN111685760B (en) | Human body respiratory frequency calculation method based on radar measurement | |
| CN114052709B (en) | Robust millimeter wave radar vital sign measurement method | |
| RU2677003C2 (en) | Device and method for determining respiration volume signal from image data | |
| KR101778845B1 (en) | Apparatus for calculating systolic blood pressure using the pulse transit time and method thereof |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination |