CN108742628B - Respiration detection method - Google Patents
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- 238000001514 detection method Methods 0.000 title claims abstract description 45
- 230000029058 respiratory gaseous exchange Effects 0.000 title abstract description 21
- 238000000034 method Methods 0.000 claims abstract description 15
- 238000012360 testing method Methods 0.000 claims description 30
- 230000002612 cardiopulmonary effect Effects 0.000 claims description 15
- 230000003434 inspiratory effect Effects 0.000 claims description 4
- 239000003550 marker Substances 0.000 claims description 3
- 238000012545 processing Methods 0.000 abstract description 3
- 230000000241 respiratory effect Effects 0.000 description 15
- CURLTUGMZLYLDI-UHFFFAOYSA-N Carbon dioxide Chemical compound O=C=O CURLTUGMZLYLDI-UHFFFAOYSA-N 0.000 description 6
- 238000002564 cardiac stress test Methods 0.000 description 5
- 239000007789 gas Substances 0.000 description 4
- 229910002092 carbon dioxide Inorganic materials 0.000 description 3
- 210000004072 lung Anatomy 0.000 description 3
- 238000003672 processing method Methods 0.000 description 3
- 238000009423 ventilation Methods 0.000 description 3
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 2
- 238000003745 diagnosis Methods 0.000 description 2
- 229910052760 oxygen Inorganic materials 0.000 description 2
- 239000001301 oxygen Substances 0.000 description 2
- 230000036387 respiratory rate Effects 0.000 description 2
- 238000005070 sampling Methods 0.000 description 2
- 230000003068 static effect Effects 0.000 description 2
- 230000009466 transformation Effects 0.000 description 2
- 230000009286 beneficial effect Effects 0.000 description 1
- 239000001569 carbon dioxide Substances 0.000 description 1
- 230000004087 circulation Effects 0.000 description 1
- 238000003759 clinical diagnosis Methods 0.000 description 1
- 238000012937 correction Methods 0.000 description 1
- 230000007547 defect Effects 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 239000000284 extract Substances 0.000 description 1
- 238000001914 filtration Methods 0.000 description 1
- 230000006870 function Effects 0.000 description 1
- 238000013123 lung function test Methods 0.000 description 1
- 230000004060 metabolic process Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 210000005036 nerve Anatomy 0.000 description 1
- 238000007781 pre-processing Methods 0.000 description 1
- 238000009613 pulmonary function test Methods 0.000 description 1
- 230000009467 reduction Effects 0.000 description 1
- 230000000284 resting effect Effects 0.000 description 1
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- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
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- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
- A61B5/082—Evaluation by breath analysis, e.g. determination of the chemical composition of exhaled breath
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- 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
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- 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
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Abstract
The invention provides a breath detection method, which calculates breath index points by processing collected flow data, and comprises the following steps: circularly judging whether the delay data condition is met from the current point to the detection point; judging whether the detection point meets a zero crossing point condition or not; judging whether the detection point meets an inspiration condition or a respiration condition; the inspiration index point and expiration index point are recorded alternately. The method has low complexity and good performance, can be used for storing the breath index points in real time, and reduces the burden of operators; data errors caused by weak breathing fluctuation are effectively prevented; and the inspiration condition and the expiration condition are judged in combination, and are constrained with each other, so that the index points of inspiration and expiration are calculated more accurately.
Description
Technical Field
The invention belongs to the technical field of breath detection, and particularly relates to a breath detection method.
Background
With the application of cardiopulmonary exercise tests in clinical functions such as respiration, circulation, metabolism, and nerves, human breath detection methods are becoming more and more important. The respiratory wave signals from a resting state to a moving state are collected by the cardiopulmonary measuring device, the respiratory index points are detected in real time, and the respiratory characteristic parameters are calculated, so that doctors can obtain a large amount of important information related to patients, diagnosis is facilitated, and efficiency and diagnosis accuracy are improved. The respiration detection method in the market at present mainly adopts an extreme value method and a zero crossing point method, wherein the extreme value method needs to be combined with a threshold value condition to judge a wave crest or a wave trough, and when a waveform has baseline drift, the anti-interference capability is poor, and one respiration can not be accurately positioned. The zero crossing point method calculates one breath by judging positive and negative values of inspiration and expiration, and is easy to judge as multiple breaths when weak fluctuation occurs in one breath.
Patent 201711232535.1 discloses a heart rate and respiration rate data processing method, which extracts the time domain and frequency domain characteristics of the sampled signal according to the characteristics of the human body sign data to reconstruct the signal waveform and corrects the signal waveform by a continuous waveform fitting mode, and comprises the following steps: 1) carrying out noise reduction on data in a sampling period through a filter to obtain preprocessed data; 2) carrying out peak detection on the preprocessed data to obtain a time domain amplitude of a signal, and simultaneously carrying out FFT (fast Fourier transform) on the preprocessed data to obtain frequency domain characteristics of the preprocessed data; 3) reconstructing a waveform by using a signal frequency domain characteristic and a time domain amplitude value by adopting an interpolation method; 4) fitting with the reconstructed waveform of the next sampling period to obtain a corrected waveform of the signal; 5) the corrected waveform is fitted with the waveform after correction to obtain a new reconstructed waveform, the reconstruction is repeated for a plurality of times, the prediction error is gradually reduced, and the precision is gradually improved. Patent 201310750413.7, relates to a respiratory signal processing method, which includes the following steps: s101, preprocessing a respiration signal, realizing signal frequency band selection and obtaining a limited bandwidth signal; s103, performing Teager energy operator transformation on the limited bandwidth signal to obtain the instantaneous amplitude and the instantaneous frequency of the respiratory signal; s105, respectively carrying out time domain and frequency transformation on the instantaneous amplitude and the instantaneous frequency to obtain instantaneous respiration intensity and instantaneous respiration rate; s107, filtering the instantaneous respiration intensity and the instantaneous respiration rate respectively to obtain average respiration intensity and average respiration rate.
The method has the advantages of small prediction error and high precision, and the data processing flow has moderate calculation amount, so that the method is suitable for portable equipment with limited calculation capacity; the respiratory signal processing method has good anti-motion interference capability, can simultaneously obtain and can realize on-line real-time calculation of the respiratory rate and the respiratory intensity. However, no technical scheme is provided for acquiring the expiratory and inspiratory index points in real time, so that parameters such as expiration and inspiration time, oxygen pulse, respiratory rate, ventilation volume and the like of the cardiopulmonary test are calculated.
Technical problem to be solved
The invention aims to overcome the defects of the prior art and provides a respiration detection method which can acquire expiration index points and inspiration index points in real time so as to calculate parameters such as expiration time, inspiration time, respiration frequency and the like.
(II) technical scheme
In order to achieve the purpose, the invention is realized by the following technical scheme:
a method of breath detection comprising the steps of:
s1, initializing the number of detection points to be 0, setting the inspiration mark to be true, and setting the expiration mark to be false;
s2, delaying X pieces of flow data, and detecting;
s3, collecting flow data;
s4, judging whether the latest point to the detection point is larger than X, if not, returning to the step S3, and if so, carrying out the next step;
s5, judging whether the product of the current flow data and the next flow data is smaller than Y, if not, adding 1 to the detection point number, returning to the step S4, circularly continuously judging, and if so, performing the step S6;
s6, judging whether the air suction condition is met, if not, adding 1 to the number of detection points, returning to the step S4, circularly continuously judging, and if so, performing the step S7;
s7, taking absolute values of the current flow data and the next flow data respectively, comparing the absolute values, and taking the index point of the smaller flow data as an inspiration index point;
s8, recording inspiration index points, setting inspiration marks as false and expiration marks as true;
s9, judging whether the expiration condition is met, if not, adding 1 to the detection point number, returning to the step S4, circularly continuously judging, and if so, carrying out the next step;
s10, respectively taking absolute values of the current flow data and the next flow data, comparing the absolute values, and taking the index point of the smaller flow data as an expiratory index point;
s11, recording an expiratory index point, setting an inspiratory sign as true, and setting an expiratory sign as false;
and S12, stopping data acquisition and finishing detection.
Further, in the step S2, X is dynamically adjusted according to the cardiopulmonary test type, and X ranges from 15 to 30.
Further, in the step S5, Y is zero point, Y is dynamically adjusted according to the cardiopulmonary test type, and Y ranges from 0.000001 to 0.0004.
Further, the air suction condition in step S6 is specifically: (1) the inspiration flag is true; (2) judging whether all the X flow data are greater than 0, if so, carrying out the next step, and if not, meeting the air suction condition; (3) and judging whether the maximum value of the X flow data is larger than or equal to Z, if not, not meeting the air suction condition, and if so, meeting the air suction condition.
Further, in the step S6, Z is dynamically adjusted according to the cardiopulmonary test type, Z is a threshold value, and Z ranges from 0.001 to 0.03.
Further, the exhalation conditions in step S9 are specifically: (1) the expiratory marker is true; (2) judging whether all the X flow data are less than 0, if so, carrying out the next step, and if not, meeting the expiration condition; (3) and judging whether the absolute value of the minimum value of the X flow data is larger than or equal to Z, if not, the exhalation condition is not met, and if so, the exhalation condition is met.
Further, in the step S9, Z is dynamically adjusted according to the cardiopulmonary test type, Z is a threshold value, and Z ranges from 0.001 to 0.03.
(III) advantageous effects
The invention has the beneficial effects that: a breath detection method has low complexity and good performance, can be used for storing breath index points in real time and reduces the burden of operators; the judgment of the inspiration condition or the expiration condition effectively prevents data errors caused by weak breathing fluctuation; according to the zero crossing point judgment provided by the invention, the zero point is in a range, and the inspiration condition or expiration condition judgment is combined and mutually constrained, so that the index points of inspiration and expiration are more accurately calculated.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only some embodiments of the present invention, and for those skilled in the art, other drawings can be obtained according to the drawings without creative efforts.
FIG. 1 is a flow chart of the present invention;
FIG. 2 is a result graph of SVC test flow data and its corresponding breath index points;
fig. 3 is a result graph of FVC test flow data and its corresponding breath index points;
FIG. 4 is a result graph of MVV test flow data and its corresponding breath index points;
fig. 5 is a graph of the results of CPET test flow data and its corresponding breath index points.
Detailed Description
In order to make the objects, technical solutions and advantages of the embodiments of the present invention clearer, 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 some, but not all, embodiments of the present invention. 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.
The equipment for detecting the respiratory signals mainly comprises an upper computer and a lower computer, wherein the lower computer is mainly a respiratory gas acquisition device and comprises an ultrasonic flow sensor, a 02 concentration analyzer and a CO2 concentration sensor. An ultrasonic flow sensor is used to test the respiratory gas flow of the human body, a 02 concentration analyzer is used to test the oxygen concentration in the respiratory gas, and a CO2 concentration sensor is used to test the carbon dioxide concentration in the respiratory gas. The upper computer is mainly used for receiving data acquired by the lower computer, displaying respiratory waveforms, and calculating related parameters of the heart and lung for clinical diagnosis.
The premise of cardiopulmonary parameter calculation is that a respiratory index point is accurately positioned, and the respiratory index point is calculated by processing acquired flow data, and the method comprises the following steps: circularly judging whether the delay data condition is met from the current point to the detection point; judging whether the detection point meets a zero crossing point condition or not; judging whether the detection point meets an inspiration condition or a respiration condition; the inspiration index point and expiration index point are recorded alternately.
With reference to fig. 1, a breath detection method includes the following steps:
s1, initializing the number of detection points to be 0, setting the inspiration mark to be true, and setting the expiration mark to be false;
s2, delaying X pieces of flow data, and detecting; x is dynamically adjusted according to the cardiopulmonary test type, and the range of X is 15-30;
s3, collecting flow data:
s4, judging whether the latest point to the detection point is larger than X, if not, returning to the step S3, and if so, carrying out the next step;
s5, judging whether the product of the current flow data and the next flow data is smaller than Y, if not, adding 1 to the detection point number, returning to the step S4, circularly continuously judging, and if so, performing the step S6; y is zero point, Y is dynamically adjusted according to the cardiopulmonary test type, and the range of Y is 0.000001-0.0004;
s6, judging whether the air suction condition is met, if not, adding 1 to the number of detection points, returning to the step S4, circularly continuously judging, and if so, performing the step S7; the suction conditions in step S6 are specifically: (1) the inspiration flag is true; (2) judging whether all the X flow data are greater than 0, if so, carrying out the next step, and if not, meeting the air suction condition; (3) judging whether the maximum value of the X flow data is larger than or equal to Z, if not, not meeting the air suction condition, and if so, meeting the air suction condition; z is dynamically adjusted according to the cardiopulmonary test type, wherein Z is a threshold value, and the range of Z is 0.001-0.03;
s7, taking absolute values of the current flow data and the next flow data respectively, comparing the absolute values, and taking the index point (the number of detection points or the number of detection points plus 1) of the smaller flow data as an inspiration index point;
s8, recording inspiration index points, setting inspiration marks as false and expiration marks as true;
s9, judging whether the expiration condition is met, if not, adding 1 to the detection point number, returning to the step S4, circularly continuously judging, and if so, carrying out the next step; the exhalation conditions in step S9 are specifically: (1) the expiratory marker is true; (2) judging whether all the X flow data are less than 0, if so, carrying out the next step, and if not, meeting the expiration condition; (3) judging whether the absolute value of the minimum value of the X flow data is larger than or equal to Z, if not, the expiration condition is not met, and if so, the expiration condition is met; z is dynamically adjusted according to the cardiopulmonary test type, wherein Z is a threshold value, and the range of Z is 0.001-0.03;
s10, respectively taking absolute values of the current flow data and the next flow data, comparing the absolute values, and taking the index point (the number of detection points or the number of detection points plus 1) of the smaller flow data as an expiration index point;
s11, recording an expiratory index point, setting an inspiratory sign as true, and setting an expiratory sign as false;
and S12, stopping data acquisition and finishing detection.
The respiration detection method mainly aims at lung function tests, including static lung capacity (SVC) tests, Forced Vital Capacity (FVC) tests, Maximum Ventilation Volume (MVV) tests and cardio-pulmonary exercise tests (CPET) tests. The X, Y, Z values used for each test are shown in table 1.
TABLE 1 pulmonary function test parameter Table
Static lung volume (SVC), Forced Vital Capacity (FVC) and maximum ventilation (MVV) tests are performed by using the method of the present invention, FIG. 2 shows SVC test flow data and a result graph of a breath index point corresponding thereto, FIG. 3 shows the FVC test flow data and a result graph of a breath index point corresponding thereto, FIG. 4 shows the MVV test flow data and a result graph of a breath index point corresponding thereto, and FIG. 5 shows the CPET test flow data and a result graph of a breath index point corresponding thereto. As can be seen from fig. 2 to 5, the zero-crossing point method calculates a breath by judging the positive and negative values of inspiration and expiration, and when weak fluctuation occurs in a breath, no misjudgment occurs.
In summary, the breath detection method is low in complexity and good in performance, and can be used for storing breath index points in real time and reducing the burden of operators; the judgment of the inspiration condition or the expiration condition effectively prevents data errors caused by weak breathing fluctuation; according to the zero crossing point judgment provided by the invention, the zero point is in a range, and the inspiration condition or expiration condition judgment is combined and mutually constrained, so that the index points of inspiration and expiration are more accurately calculated.
The above examples are only intended to illustrate the technical solution of the present invention, but not to limit it; although the present invention has been described in detail with reference to the foregoing embodiments, it will be understood by those of ordinary skill in the art that: the technical solutions described in the foregoing embodiments may still be modified, or some technical features may be equivalently replaced; and such modifications or substitutions do not depart from the spirit and scope of the corresponding technical solutions of the embodiments of the present invention.
Claims (5)
1. A method of breath detection, comprising the steps of:
s1, initializing the number of detection points to be 0, setting the inspiration mark to be true, and setting the expiration mark to be false;
s2, delaying X pieces of flow data, and detecting;
s3, collecting flow data;
s4, judging whether the latest point to the detection point is larger than X, if not, returning to the step S3, and if so, carrying out the next step;
s5, judging whether the product of the current flow data and the next flow data is smaller than Y, if not, adding 1 to the detection point number, returning to the step S4, circularly continuously judging, and if so, performing the step S6;
s6, judging whether the air suction condition is met, if not, adding 1 to the number of detection points, returning to the step S4, circularly continuously judging, and if so, performing the step S7;
s7, taking absolute values of the current flow data and the next flow data respectively, comparing the absolute values, and taking the index point of the smaller flow data as an inspiration index point;
s8, recording inspiration index points, setting inspiration marks as false and expiration marks as true;
s9, judging whether the expiration condition is met, if not, adding 1 to the detection point number, returning to the step S4, circularly continuously judging, and if so, carrying out the next step;
s10, respectively taking absolute values of the current flow data and the next flow data, comparing the absolute values, and taking the index point of the smaller flow data as an expiratory index point;
s11, recording an expiratory index point, setting an inspiratory sign as true, and setting an expiratory sign as false;
s12, stopping collecting data and finishing detection;
the air suction condition in the step S6 is specifically: (1) the inspiration flag is true; (2) judging whether all the X flow data are greater than 0, if so, carrying out the next step, and if not, meeting the air suction condition; (3) judging whether the maximum value of the X flow data is larger than or equal to Z, if not, not meeting the air suction condition, and if so, meeting the air suction condition;
the exhalation conditions in step S9 are specifically: (1) the expiratory marker is true; (2) judging whether all the X flow data are less than 0, if so, carrying out the next step, and if not, meeting the expiration condition; (3) and judging whether the absolute value of the minimum value of the X flow data is larger than or equal to Z, if not, the exhalation condition is not met, and if so, the exhalation condition is met.
2. A breath detection method as recited in claim 1, wherein: in the step S2, X is dynamically adjusted according to the cardiopulmonary test type, and the range of X is 15-30.
3. The breath detection method of claim 1, wherein Y is zero in step S5, Y is dynamically adjusted according to the cardiopulmonary test type, and Y ranges from 0.000001 to 0.0004.
4. The method according to claim 1, wherein Z in step S6 is dynamically adjusted according to the type of cardiopulmonary test, Z is a threshold value, and Z ranges from 0.001 to 0.03.
5. The method according to claim 1, wherein Z in step S9 is dynamically adjusted according to the type of cardiopulmonary test, Z is a threshold value, and Z ranges from 0.001 to 0.03.
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