CN114073534B - Heart function analysis algorithm - Google Patents
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- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
- A61B5/346—Analysis of electrocardiograms
- A61B5/349—Detecting specific parameters of the electrocardiograph cycle
- A61B5/366—Detecting abnormal QRS complex, e.g. widening
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- A61B5/316—Modalities, i.e. specific diagnostic methods
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- A61B5/346—Analysis of electrocardiograms
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- A61B5/352—Detecting R peaks, e.g. for synchronising diagnostic apparatus; Estimating R-R interval
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- A61B5/316—Modalities, i.e. specific diagnostic methods
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Abstract
The invention discloses a cardiac function analysis algorithm, belongs to the technical field of cardiac function analysis, and aims to solve the problems that in the prior art, by manually observing electrocardiographic waveforms, numerical values corresponding to electrocardiographic waveforms are obtained, so that identification accuracy is different and identification speed is low. Based on waveform characteristics, the waveform can be effectively and rapidly identified through an algorithm, and data under a unified rule can be obtained. The method can accurately identify the information of each period of the QRS complex, rapidly acquire a large amount of QRS complex data of the waveform, and avoid the problem of different precision caused by naked eye identification by using unified standards. The invention is suitable for cardiac function analysis algorithm.
Description
Technical Field
The invention belongs to the technical field of cardiac function analysis, and particularly relates to a cardiac function analysis algorithm.
Background
The heart function analysis is used for searching for each period of the electrocardio QRS complex, and comparing the found result with a normal value for heart function examination, electrocardio monitoring and heart rate variability analysis. At present, the electrocardiographic waveform is observed manually to obtain corresponding numerical values, so that the data observed by different people are different, and the recognition speed is affected.
Disclosure of Invention
The invention aims to provide a cardiac function analysis algorithm, which solves the problems of non-uniform identification precision and low identification speed caused by manually observing electrocardiographic waveforms to obtain numerical values corresponding to electrocardiographic waveforms in the prior art.
The technical scheme adopted by the invention is as follows:
a cardiac function analysis algorithm comprising the algorithm steps of:
(1) The influence of small-amplitude waveforms on electrocardiographic analysis is eliminated through smoothing filtering, the size of a window selected by the smoothing filtering is determined according to the obtained small-amplitude clutter width of the waveforms and the sampling rate, the sampling rate is the sampling number of discrete signals extracted from continuous signals in unit time and formed, each data point is firstly averaged with a plurality of data points adjacent to the left and right during the smoothing filtering, and then the average value is used for replacing the data point;
(2) The number of the electrocardio QRS wave groups is obtained through average bidirectional slope, the condition of baseline drift is avoided,
slope step = 0.06 (1/sample rate);
analyzing the slope, wherein all turning point parts are the positions of R points of the electrocardio, and the number of the electrocardio QRS wave groups can be obtained through the number of the turning points;
(3) The average heart rate HR is calculated by the distance between two adjacent R waves, i.e., RR interval
(4) Taking a value in a range of 0.3s to the left and a value in a range of 0.44s to the right through the position of the R point, and judging that a complete QRS complex exists in the range;
PR interval: 0.12-0.20 seconds;
QRS complex: 0.06-0.10 seconds;
QT interval: 0.30-0.44 seconds;
r wave takes the maximum value to the left: 0.20+0.10=0.3 seconds;
r wave takes maximum value to right: 0.44 seconds;
(5) Inquiring the maximum value in the range, correcting the position of the R wave again, and storing;
(6) According to waveform characteristics, Q wave is the first trough of R wave which is encountered leftwards, S wave is the first trough of R wave which is encountered rightwards, and Q wave, R wave and S wave are finally found, wherein searching of trough should avoid clutter influence, and this point is guaranteed to be the lowest point in the range (0.06S-0.10S);
(7) According to PR interval: 0.12-0.20, searching the maximum value in the area from the R point to the left, wherein the point is the P wave;
(8) The first trough of the P wave to the left is the P wave starting point, in order to avoid the influence of small clutter on the normal trough, even if smooth filtering is used, the point needs to be smaller than all points from the right side to the P point;
(9) When the T wave is searched, the maximum value of the R point to the right is the T wave, and the first trough is searched from the left to the right according to the T wave, namely a T wave starting point and a T wave ending point;
(10) Searching from the Q wave to the left through the P wave and the Q wave, wherein the first wave peak is the starting point of the Q wave;
(11) Searching from the S wave to the right through the S wave and the T wave, wherein the first wave crest encountered is the S wave end point;
(12) After the positions of all the points are obtained, the corresponding intervals are calculated according to the following formula:
PR interval= (Q-wave start point-P-wave start point)/sampling rate;
QT interval= (T wave end point-Q wave start point)/sampling rate;
QRS time limit= (S wave end point-Q wave start point)/sampling rate;
ST period= (T-wave start point-S-wave end point)/sampling rate;
p-wave amplitude = P-wave number value-P-wave start point value;
r wave amplitude = R wave number value-Q wave start point value;
t wave amplitude = T wave number value-T wave start point value;
s-wave amplitude = S-wave number value-S-wave end point value;
q wave amplitude = Q wave number value-Q wave start point value;
ST wave amplitude=t wave start point value-S wave end point value.
In summary, due to the adoption of the technical scheme, the beneficial effects of the invention are as follows:
1. in the invention, based on waveform characteristics, the waveform can be effectively and rapidly identified through an algorithm, and data under a unified rule can be obtained. The method can accurately identify the information of each period of the QRS complex, rapidly acquire a large amount of QRS complex data of the waveform, and avoid the problem of different precision caused by naked eye identification by using unified standards.
Drawings
For a clearer description of the technical solutions of embodiments of the present invention, the drawings that are needed in the embodiments will be briefly described below, it being understood that the following drawings only illustrate some embodiments of the present invention and should not be considered limiting in scope, and other related drawings can be obtained according to these drawings without inventive effort for a person skilled in the art, wherein:
FIG. 1 is a schematic flow chart of the present invention;
FIG. 2 is a single waveform analysis diagram of the present invention;
FIG. 3 is a diagram of a plurality of waveform analysis according to the present invention;
fig. 4 is a schematic diagram of the sampling of the present invention.
Detailed Description
For the purpose of making the objects, technical solutions and advantages of the embodiments of the present invention more apparent, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present invention, and it is apparent that the described embodiments are some embodiments of the present invention, but not all embodiments of the present invention. The components of the embodiments of the present invention generally described and illustrated in the figures herein may be arranged and designed in a wide variety of different configurations.
Thus, the following detailed description of the embodiments of the invention, as presented in the figures, is not intended to limit the scope of the invention, as claimed, but is merely representative of selected embodiments of the invention. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.
It should be noted that: reference numerals and letters denote similar items throughout the following figures, and thus once an item is defined in one figure, it need not be further defined and explained in subsequent figures.
In the description of the present invention, it should be noted that, directions or positional relationships indicated by terms such as "center", "upper", "lower", "left", "right", "vertical", "horizontal", "inner", "outer", etc., are directions or positional relationships based on those shown in the drawings, or those that are conventionally put in use of the inventive product, are merely for convenience of description of the present invention, and are not indicative or implying that the apparatus or element to be referred to must have a specific direction, be constructed and operated in a specific direction, and thus should not be construed as limiting the present invention. Furthermore, the terms "first," "second," "third," and the like are used merely to distinguish between descriptions and should not be construed as indicating or implying relative importance.
Furthermore, the terms "horizontal," "vertical," and the like do not denote a requirement that the component be absolutely horizontal or overhang, but rather may be slightly inclined. As "horizontal" merely means that its direction is more horizontal than "vertical", and does not mean that the structure must be perfectly horizontal, but may be slightly inclined.
In the description of the present invention, it should also be noted that, unless explicitly specified and limited otherwise, the terms "disposed," "mounted," "connected," and "connected" are to be construed broadly, and may be, for example, fixedly connected, detachably connected, or integrally connected; the mechanical connection can be made or the electrical connection can be made; can be directly connected or indirectly connected through an intermediate medium, and can be the communication between the two original parts. The specific meaning of the above terms in the present invention will be understood in specific cases by those of ordinary skill in the art.
A cardiac function analysis algorithm comprising the algorithm steps of:
(1) The influence of small-amplitude waveforms on electrocardiographic analysis is eliminated through smoothing filtering, the size of a window selected by the smoothing filtering is determined according to the obtained small-amplitude clutter width of the waveforms and the sampling rate, the sampling rate is the sampling number of discrete signals extracted from continuous signals in unit time and formed, each data point is firstly averaged with a plurality of data points adjacent to the left and right during the smoothing filtering, and then the average value is used for replacing the data point;
(2) The number of the electrocardio QRS wave groups is obtained through average bidirectional slope, the condition of baseline drift is avoided,
slope step = 0.06 (1/sample rate);
analyzing the slope, wherein all turning point parts are the positions of R points of the electrocardio, and the number of the electrocardio QRS wave groups can be obtained through the number of the turning points;
(3) The average heart rate HR is calculated by the distance between two adjacent R waves, i.e., RR interval
(4) Taking a value in a range of 0.3s to the left and a value in a range of 0.44s to the right through the position of the R point, and judging that a complete QRS complex exists in the range;
PR interval: 0.12-0.20 seconds;
QRS complex: 0.06-0.10 seconds;
QT interval: 0.30-0.44 seconds;
r wave takes the maximum value to the left: 0.20+0.10=0.3 seconds;
r wave takes maximum value to right: 0.44 seconds;
(5) Inquiring the maximum value in the range, correcting the position of the R wave again, and storing;
(6) According to waveform characteristics, Q wave is the first trough of R wave which is encountered leftwards, S wave is the first trough of R wave which is encountered rightwards, and Q wave, R wave and S wave are finally found, wherein searching of trough should avoid clutter influence, and this point is guaranteed to be the lowest point in the range (0.06S-0.10S);
(7) According to PR interval: 0.12-0.20, searching the maximum value in the area from the R point to the left, wherein the point is the P wave;
(8) The first trough of the P wave to the left is the P wave starting point, in order to avoid the influence of small clutter on the normal trough, even if smooth filtering is used, the point needs to be smaller than all points from the right side to the P point;
(9) When the T wave is searched, the maximum value of the R point to the right is the T wave, and the first trough is searched from the left to the right according to the T wave, namely a T wave starting point and a T wave ending point;
(10) Searching from the Q wave to the left through the P wave and the Q wave, wherein the first wave peak is the starting point of the Q wave;
(11) Searching from the S wave to the right through the S wave and the T wave, wherein the first wave crest encountered is the S wave end point;
(12) After the positions of all the points are obtained, the corresponding intervals are calculated according to the following formula:
PR interval= (Q-wave start point-P-wave start point)/sampling rate;
QT interval= (T wave end point-Q wave start point)/sampling rate;
QRS time limit= (S wave end point-Q wave start point)/sampling rate;
ST period= (T-wave start point-S-wave end point)/sampling rate;
p-wave amplitude = P-wave number value-P-wave start point value;
r wave amplitude = R wave number value-Q wave start point value;
t wave amplitude = T wave number value-T wave start point value;
s-wave amplitude = S-wave number value-S-wave end point value;
q wave amplitude = Q wave number value-Q wave start point value;
ST wave amplitude=t wave start point value-S wave end point value.
In the implementation process, the waveform can be effectively and rapidly identified through an algorithm based on waveform characteristics, and data under a unified rule is obtained. The method can accurately identify the information of each period of the QRS complex, rapidly acquire a large amount of QRS complex data of the waveform, and avoid the problem of different precision caused by naked eye identification by using unified standards.
Example 1
A heart function analysis algorithm eliminates the influence of a small-amplitude waveform on electrocardiographic analysis through smoothing filtering, the size of a window selected by the smoothing filtering is determined according to the width of clutter of the small amplitude of the obtained waveform and the sampling rate, the sampling rate is the sampling number of discrete signals extracted from continuous signals in unit time and formed, each data point is firstly averaged with a plurality of data points adjacent to the left and right during the smoothing filtering, and then the average value is used for replacing the data point;
(2) The number of the electrocardio QRS wave groups is obtained through average bidirectional slope, the condition of baseline drift is avoided,
slope step = 0.06 (1/sample rate);
analyzing the slope, wherein all turning point parts are the positions of R points of the electrocardio, and the number of the electrocardio QRS wave groups can be obtained through the number of the turning points;
(3) The average heart rate HR is calculated by the distance between two adjacent R waves, i.e., RR interval
(4) Taking a value in a range of 0.3s to the left and a value in a range of 0.44s to the right through the position of the R point, and judging that a complete QRS complex exists in the range;
PR interval: 0.12-0.20 seconds;
QRS complex: 0.06-0.10 seconds;
QT interval: 0.30-0.44 seconds;
r wave takes the maximum value to the left: 0.20+0.10=0.3 seconds;
r wave takes maximum value to right: 0.44 seconds;
(5) Inquiring the maximum value in the range, correcting the position of the R wave again, and storing;
(6) According to waveform characteristics, Q wave is the first trough of R wave which is encountered leftwards, S wave is the first trough of R wave which is encountered rightwards, and Q wave, R wave and S wave are finally found, wherein searching of trough should avoid clutter influence, and this point is guaranteed to be the lowest point in the range (0.06S-0.10S);
(7) According to PR interval: 0.12-0.20, searching the maximum value in the area from the R point to the left, wherein the point is the P wave;
(8) The first trough of the P wave to the left is the P wave starting point, in order to avoid the influence of small clutter on the normal trough, even if smooth filtering is used, the point needs to be smaller than all points from the right side to the P point;
(9) When the T wave is searched, the maximum value of the R point to the right is the T wave, and the first trough is searched from the left to the right according to the T wave, namely a T wave starting point and a T wave ending point;
(10) Searching from the Q wave to the left through the P wave and the Q wave, wherein the first wave peak is the starting point of the Q wave;
(11) Searching from the S wave to the right through the S wave and the T wave, wherein the first wave crest encountered is the S wave end point;
(12) After the positions of all the points are obtained, the corresponding intervals are calculated according to the following formula:
PR interval= (Q-wave start point-P-wave start point)/sampling rate;
QT interval= (T wave end point-Q wave start point)/sampling rate;
QRS time limit= (S wave end point-Q wave start point)/sampling rate;
ST period= (T-wave start point-S-wave end point)/sampling rate;
p-wave amplitude = P-wave number value-P-wave start point value;
r wave amplitude = R wave number value-Q wave start point value;
t wave amplitude = T wave number value-T wave start point value;
s-wave amplitude = S-wave number value-S-wave end point value;
q wave amplitude = Q wave number value-Q wave start point value;
ST wave amplitude=t wave start point value-S wave end point value.
The above-described embodiments of the present invention. The foregoing description is illustrative of various preferred embodiments of the present invention, and the preferred embodiments of the various preferred embodiments may be used in any combination and stacked on the premise of a certain preferred embodiment, where the embodiments and specific parameters in the embodiments are only for clearly describing the verification process of the present invention, and are not intended to limit the scope of the present invention, and the scope of the present invention is still subject to the claims, and all equivalent structural changes made by applying the descriptions and the drawings of the present invention are included in the scope of the present invention.
Claims (1)
1. A cardiac function analysis algorithm, comprising the algorithm steps of:
(1) The influence of small-amplitude waveforms on electrocardiographic analysis is eliminated through smoothing filtering, the size of a window selected by the smoothing filtering is determined according to the obtained small-amplitude clutter width of the waveforms and the sampling rate, the sampling rate is the sampling number of discrete signals extracted from continuous signals in unit time and formed, each data point is firstly averaged with a plurality of data points adjacent to the left and right during the smoothing filtering, and then the average value is used for replacing the data point;
(2) The number of the electrocardio QRS wave groups is obtained through average bidirectional slope, the condition of baseline drift is avoided,
slope step = 0.06 (1/sample rate);
analyzing the slope, wherein all turning point parts are the positions of R points of the electrocardio, and the number of the electrocardio QRS wave groups can be obtained through the number of the turning points;
(3) The average heart rate HR is calculated by the distance between two adjacent R waves, i.e., RR interval
(4) Taking a value in a range of 0.3s to the left and a value in a range of 0.44s to the right through the position of the R point, and judging that a complete QRS complex exists in the range;
PR interval: 0.12-0.20 seconds;
QRS complex: 0.06-0.10 seconds;
QT interval: 0.30-0.44 seconds;
r wave takes the maximum value to the left: 0.20+0.10=0.3 seconds;
r wave takes maximum value to right: 0.44 seconds;
(5) Inquiring the maximum value in the range, correcting the position of the R wave again, and storing;
(6) According to waveform characteristics, Q wave is the first trough of R wave which is encountered leftwards, S wave is the first trough of R wave which is encountered rightwards, and Q wave, R wave and S wave are finally found, wherein searching of trough should avoid clutter influence, and this point is guaranteed to be the lowest point in the range (0.06S-0.10S);
(7) According to PR interval: 0.12-0.20, searching the maximum value in the area from the R point to the left, wherein the point is the P wave;
(8) The first trough of the P wave to the left is the P wave starting point, in order to avoid the influence of small clutter on the normal trough, even if smooth filtering is used, the point needs to be smaller than all points from the right side to the P point;
(9) When the T wave is searched, the maximum value of the R point to the right is the T wave, and the first trough is searched from the left to the right according to the T wave, namely a T wave starting point and a T wave ending point;
(10) Searching from the Q wave to the left through the P wave and the Q wave, wherein the first wave peak is the starting point of the Q wave;
(11) Searching from the S wave to the right through the S wave and the T wave, wherein the first wave crest encountered is the S wave end point;
(12) After the positions of all the points are obtained, the corresponding intervals are calculated according to the following formula:
PR interval= (Q-wave start point-P-wave start point)/sampling rate;
QT interval= (T wave end point-Q wave start point)/sampling rate;
QRS time limit= (S wave end point-Q wave start point)/sampling rate;
ST period= (T-wave start point-S-wave end point)/sampling rate;
p-wave amplitude = P-wave number value-P-wave start point value;
r wave amplitude = R wave number value-Q wave start point value;
t wave amplitude = T wave number value-T wave start point value;
s-wave amplitude = S-wave number value-S-wave end point value;
q wave amplitude = Q wave number value-Q wave start point value;
ST wave amplitude=t wave start point value-S wave end point value.
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| WO2021169296A1 (en) * | 2020-02-27 | 2021-09-02 | 平安科技（深圳）有限公司 | Method and apparatus for processing electrocardiogram data, computer device, and storage medium |
| CN112257518A (en) * | 2020-09-30 | 2021-01-22 | 西安交通大学第二附属医院 | ECG identity recognition method based on WT and WOA-PNN algorithm |
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