CN114869295A - ST offset value calculation method, device, computer equipment and storage medium - Google Patents

Abstract

The present application proposes a method for calculating an ST offset value. The method includes: acquiring an ECG signal, the ECG signal including an ST segment located between the QRS complex and the T wave; extracting the R wave of the ECG signal location; determine the first Q wave start point set and the first S wave end point set in the ECG signal based on the R wave location of the ECG signal and a preset square formula; based on the ECG signal The R wave position and the preset differential formula determine the second Q wave start point set and the second S wave end point set in the ECG signal; according to the first Q wave start point set and the second The Q wave start point set determines the position of the isoelectric point of the ECG signal; the ST point position of the ECG signal is determined according to the first S wave termination point set and the second S wave termination point set; The position of the isoelectric point and the position of the ST point determine the ST offset value of the ECG signal.

Description

ST offset value calculation method, device, computer equipment and storage medium

technical field

The present application relates to the medical field, and in particular, to a method, apparatus, computer equipment and storage medium for calculating an ST offset value.

Background technique

The heart muscle beats by electrical shock waves that travel through the patient's body and can be measured with electrodes attached to the patient's skin. Electrodes on different sides of the heart measure the activity of different parts of the heart muscle. Electrocardiogram (electrocardiogram, ECG) shows the voltage between electrode pairs (leads) in different directions. Therefore, the ECG signal can be used to show the overall heart rate and myocardial weakness in different parts of the myocardium. Electrocardiographic signals can be used to measure and diagnose abnormal heart rhythms, including those caused by damage to the conducting tissue that conducts electrical signals. ECG signals can be measured with a variety of different leads. Typically, the standard 12-lead measurement can be used, but other lead measurements, such as 5-lead or 3-lead, can also be used.

ST-segment (ST elevation myocardial infarctions, STEMI) changes in the ECG signal are common clinical ECG manifestations. When the patient's myocardial ischemia or injury, the ST wave part of the ECG signal in the affected leads will change from Zero potential difference line offset. The changes of ST segment are roughly up and down offset or left and right offset. The upper and lower offset is called "ST segment elevation" and "ST segment depression". The left and right offset is reflected in the change of ST interval length. It is the "elevation" and "depression" of the ST segment. ST segment abnormalities are more common in cardiac diseases such as myocardial ischemia, myocardial infarction, acute pericarditis, etc. ST value is an important indicator to assist medical staff in judging the physiological state of the patient's heart, and is also an indispensable parameter in various types of electrocardiographs. However, the ST segment has various morphological changes, and when the ECG signal has a large interference or has an influence of drift, the accuracy of ST segment identification and judgment in the prior art will be greatly reduced.

SUMMARY OF THE INVENTION

The present application provides an ST offset value calculation method, device, computer equipment and storage medium to solve the technical problem of low calculation accuracy in the existing ST offset value calculation technology.

In a first aspect, a method for calculating an ST offset value is provided, the method comprising:

acquiring an electrocardiographic signal, the electrocardiographic signal including an ST segment between the QRS complex and the T wave;

extracting the R wave site of the ECG signal;

Determine the first Q wave start point set and the first S wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset square formula;

determining the second Q wave start point set and the second S wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset differential formula;

Determine the position of the isoelectric point of the ECG signal according to the first Q wave starting point set and the second Q wave starting point set;

Determine the ST point position of the ECG signal according to the first S-wave termination point set and the second S-wave termination point set;

The ST offset value of the ECG signal is determined according to the position of the isoelectric point and the position of the ST point.

In a second aspect, a device for calculating an ST offset value is provided, the device comprising:

an ECG signal acquisition module for acquiring an ECG signal, the ECG signal including the ST segment located between the QRS complex and the T wave;

An R-wave site extraction module for extracting the R-wave site of the ECG signal;

A first point set determination module, configured to determine the first Q wave start point set and the first S wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset square formula;

A second point set determination module, configured to determine a second Q wave start point set and a second S wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset differential formula;

an isoelectric point determination module, configured to determine the position of the isoelectric point of the ECG signal according to the first Q wave starting point set and the second Q wave starting point set;

ST point determination module, configured to determine the ST point position of the ECG signal according to the first S wave termination point set and the second S wave termination point set;

The ST offset value determination module is configured to determine the ST offset value of the ECG signal according to the position of the isoelectric point and the position of the ST point.

In a third aspect, a computer device is provided, including a memory and a processor, the memory stores a computer program, and when the computer program is executed by the processor, the processor is caused to perform the following steps:

acquiring an electrocardiographic signal, the electrocardiographic signal including an ST segment between the QRS complex and the T wave;

extracting the R wave site of the ECG signal;

Determine the first Q wave start point set and the first S wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset square formula;

determining the second Q wave start point set and the second S wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset differential formula;

Determine the position of the isoelectric point of the ECG signal according to the first Q wave starting point set and the second Q wave starting point set;

Determine the ST point position of the ECG signal according to the first S-wave termination point set and the second S-wave termination point set;

The ST offset value of the ECG signal is determined according to the position of the isoelectric point and the position of the ST point.

In a fourth aspect, a computer-readable storage medium is provided, which stores a computer program, and when the computer program is executed by a processor, causes the processor to perform the following steps:

acquiring an electrocardiographic signal, the electrocardiographic signal including an ST segment between the QRS complex and the T wave;

extracting the R wave site of the ECG signal;

Determine the first Q wave start point set and the first S wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset square formula;

determining the second Q wave start point set and the second S wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset differential formula;

Determine the position of the isoelectric point of the ECG signal according to the first Q wave starting point set and the second Q wave starting point set;

Determine the ST point position of the ECG signal according to the first S-wave termination point set and the second S-wave termination point set;

The ST offset value of the ECG signal is determined according to the position of the isoelectric point and the position of the ST point.

The present application can achieve the following beneficial effects: after obtaining the ECG signal and extracting the R wave position of the ECG signal, the ECG signal is determined based on the R wave position of the ECG signal and a preset square formula The first Q wave start point set and the first S wave end point set in the ECG signal, and the second Q wave start point set in the ECG signal is determined based on the R wave position of the ECG signal and the preset difference formula and the second S wave termination point set; in this scheme, the amplitude characteristics of the ECG signal can be highlighted by square amplification, thereby effectively improving the signal quality, and can more accurately determine the Q wave starting point set and S wave of the ECG signal. Termination point set, thereby improving the accuracy of ST offset value calculation; then determine the position of the isoelectric point of the ECG signal through the first Q wave start point set and the second Q wave start point set, and pass After the first S wave termination point set and the second S wave termination point set determine the ST point position of the ECG signal, the ECG is finally determined according to the isoelectric point position and the ST point position. ST offset value of the signal; after square amplification and differential processing in this scheme, based on the high-precision Q wave start point set and S wave end point set, the equipotential point and ST point can be accurately determined, and can be accurately determined At the same time, the use of differential signals reduces the influence of baseline drift in the ECG signal to a certain extent, reduces the difficulty of medical staff judging the physiological state of the patient's heart, and improves the accuracy of medical staff judgment.

Description of drawings

1 is a schematic connection diagram of a 12-lead system provided by an embodiment of the present application;

FIG. 2 is a schematic diagram of the connection of a limb lead according to an embodiment of the present application;

FIG. 3 is a schematic diagram of connection of a chest lead according to an embodiment of the present application;

4 is an electrocardiographic signal signal of a heartbeat in the electrocardiographic signal of a healthy person provided by an embodiment of the present application;

5A is a schematic diagram of an ST segment elevation provided by an embodiment of the present application;

5B is a schematic diagram of an ST segment depression provided by an embodiment of the present application;

FIG. 6 is a schematic diagram of an ECG signal provided by an embodiment of the present application;

7 is a schematic flowchart of a method for calculating an ST offset value provided by an embodiment of the present application;

8A is a schematic diagram of a search direction of a Q wave starting point and a J point provided by an embodiment of the present application;

8B is a schematic diagram of a search direction of a Q wave starting point and a J point provided by an embodiment of the present application;

9 is a schematic flowchart of a method for calculating an ST offset value provided by an embodiment of the present application;

10 is a schematic diagram of a concentric ring display diagram provided by an embodiment of the present application;

11 is a schematic diagram of displaying an ST offset value provided by an embodiment of the present application;

FIG. 12 is a schematic diagram of displaying an ST offset value provided by an embodiment of the present application;

13 is a schematic diagram of displaying an ST offset value provided by an embodiment of the present application;

14 is a schematic structural diagram of an apparatus for calculating an ST offset value provided by an embodiment of the present application;

FIG. 15 is a schematic structural diagram of a computer device according to an embodiment of the present application.

Detailed ways

The technical solutions in the embodiments of the present application will be described below with reference to the accompanying drawings in the embodiments of the present application.

The ST value is an important indicator for assisting medical staff in judging the physiological state of the patient's heart. The technical solution of the present application can be applied to various medical scenarios in which the ST offset value is obtained through an electrocardiograph, thereby assisting medical staff in judging the physiological state of the patient's heart. . Specifically, the technical solution of the present application is applied to computer equipment, and is suitable for a data processing scenario in which a patient's ECG signal is obtained through ECG leads, and then an ST segment offset value in the patient's ECG signal is calculated.

In practical applications, the technical solution of the present application can be applied to an ECG lead detection scenario with only one lead, or can be applied to an ECG lead detection scenario with multiple leads. It can be understood that in a detection scenario with multiple leads, the technical solution of the present application can be used to calculate the ST offset value of the electrocardiogram of each lead in the multiple leads at the same time, or calculate the ST offset value of the multiple leads independently. The ST offset value of the ECG of any lead in the ganglion.

In order to facilitate the understanding of the technical solution of the present application, the electrocardiogram leads are first introduced. Among them, electrodes are placed in different parts of the human body and connected to the positive and negative poles of the electrocardiograph galvanometer through lead wires. This circuit connection method for recording electrocardiograms is called electrocardiogram lead. In practice, the universal lead system is called the conventional 12-lead system, including limb leads connected to the limbs and chest leads connected to the chest. As shown in Figure 1, Figure 1 is a schematic diagram of the connection of the 12-lead system.

In this embodiment, as shown in FIG. 2 , the limb leads include standard limb leads I, II, and III, and pressure unipolar limb leads aVR, aVL, and aVF.

Among them, the standard limb lead is a bipolar lead, which can reflect the potential difference between the two limbs; the standard lead I is the potential difference between the left and right hands; the standard lead II is the potential difference between the left leg and the right hand ; Standard lead III is the potential difference between the left leg and the left hand; the potential size recorded in the standard lead has the relationship of I+III=II. Compressed unipolar limb leads are two electrodes, only one electrode shows potential, while the potential of the other electrode is equal to zero, and the voltage of the lead site is directly recorded; when the compressed unipolar limb leads are connected, the left hand, right hand, Any one of the left leg is the positive electrode, and the other two combined electrodes are the negative electrode; the aVR positive electrode of the pressurized monopolar limb lead is the right hand, and the combined electrode of the left hand and the left leg is the negative electrode; the pressurized monopolar limb lead The aVL positive electrode is the left hand, and the combined electrode of the right hand and the left leg is the negative electrode; the aVF positive electrode of the pressurized unipolar limb lead is the left leg, and the combined electrode of the left hand and the right hand is the negative electrode.

In this embodiment, the chest leads are unipolar leads, including leads V1 to V6. During detection, the positive electrode should be placed on the specified part of the chest wall; in addition, the three electrodes of the limb lead are connected to the negative electrode through a 5K resistor to form the central electrical terminal. connected negative electrode. As shown in Figure 3, the specific placement of the chest lead detection electrodes is: 1 is V1, located in the fourth intercostal space on the right border of the foot bone; 2 is V2, located in the fourth intercostal space on the left border of the sternum; 3 is V3, located in the V2 The midpoint of the line connecting the two points with V4; 4 is V4, located at the intersection of the left midclavicular line and the 5th intercostal space; 5 is V5, located at the level of V4 on the left anterior axillary line; 6 is V6, located at the level of V4 on the left midaxillary line.

Among them, in routine ECG examination, a total of 12 leads including standard limb leads, pressurized unipolar limb leads and V1 to V6 can meet the needs. If dextrocardia, right ventricular hypertrophy, or myocardial infarction is suspected, leads V7, V8, V9, and V3R should be added. V7 is at the level of V4 at the left posterior axillary line; V8 is at the level of V4 at the left scapular line; V9 is at the left side of the spine Line V4 level; V3R in the corresponding part of V3 on the right chest.

In order to facilitate the understanding of this program, the electrocardiogram will be introduced again. As shown in FIG. 4 , FIG. 4 shows the ECG signal of one heartbeat in the ECG signal of a healthy person, which includes a P wave, a Q wave, an R wave, an S wave and a T wave. The P wave stands for atrial depolarization, where the initial part of the P wave mainly reflects right atrial depolarization, and the terminal part mainly reflects left atrial depolarization. As can be seen from the figure, the Q wave is a downwardly shifted wave after the P wave. A typical Q wave represents a septal depolarization. The R wave is the first upwardly shifted wave after the P wave and represents an early ventricular depolarization. The S wave is the first negatively shifted wave following the R wave and represents late ventricular depolarization. T waves are usually convex, slightly arcuate, and slightly asymmetrical. The T wave represents the repolarization of the ventricle. The QRS complex begins at the beginning of the Q wave and ends at the end of the S wave. The QRS complex represents the ongoing process of ventricular depolarization. Typically, there is little or no electrical activity along the zero potential difference line 110 during the PR and ST segments of the ECG signal. In other words, ST waves are normally zero potential difference.

As shown in FIGS. 5A and 5B , the ST segment may appear vertically elevated ( FIG. 5A ) or depressed ( FIG. 5B ) from the zero potential difference line 110 . The ST segment offset value 120 is used to represent the vertical distance from the zero potential difference line 110 when the ST segment is raised or depressed. ST-segment elevation or depression may be caused by heart injury, ventricular aneurysm, variant angina, pericarditis, myocardial ischemia, or other conditions. According to the description herein, the skilled person can understand that the ST-segment elevation in FIG. 5A and the ST-segment depression in FIG. 5B may still occur for the same patient when detected by different leads.

Taking ST segment depression as an example, as shown in FIG. 6 , FIG. 6 is an ECG signal containing ST segment depression. Among them, (1) is the starting point of the P wave, (2) is the position of the P wave, (3) is the ending point of the P wave, (4) is the ISO point (isopotential point), (5) is the starting point of the Q wave, ( 6) is the position of the R wave, (7) is the position of the S wave, (8) is the end point of the S wave, (9) is the ST point, (10) is the starting point of the T wave, (11) is the position of the T wave, (12) ) is the termination point of the T wave. The ST value in FIG. 6 is the offset value of the ST segment 120, the ISO point is a point on the zero potential difference line 110, and the ST point is a point on the ST segment. In this application, the position of the zero potential difference line, that is, the position of the ISO point, is determined by determining the starting point of the Q wave; the position of the ST point is determined by determining the end point of the S wave; and then the ST offset value is determined .

In one embodiment, as shown in FIG. 7 , the present application proposes a method for calculating an ST offset value, and the method includes:

Step 701: Acquire an ECG signal, where the ECG signal includes an ST segment located between the QRS complex and the T wave.

Wherein, the ECG signal is obtained by detecting the lead system as shown in FIG. 1 , and may also be obtained from a storage device or medium storing ECG signal data. The ECG signal further includes lead type data corresponding to the ECG signal, and the lead type data is used to indicate the lead type from which the ECG signal is detected; the lead type is shown in Figs. One or more of the leads described in FIG. 3 may, for example, be one type of leads in the limb leads connected to the limb and/or one lead type in the chest leads connected to the chest, and also There may be multiple lead types in the limb leads connected to the limb and/or multiple lead types in the chest leads connected to the chest.

Wherein, the ECG signal includes the ST segment located between the QRS complex and the T wave as described in FIG. 4 to FIG. 6 .

Step 702, extracting the R wave position of the ECG signal.

The R wave may be the R wave in the ECG signal as shown in FIG. 6 . The R wave position is used to indicate the position of the R wave, and may specifically be the abscissa Rpos corresponding to the R wave position (6) described in FIG. 6 .

In a specific embodiment, when the ECG signal is acquired, the voltage of each point on the ECG signal can be obtained at the same time. By comparing the voltage of each point on the ECG signal with a preset R-wave reference voltage, the R-wave peak of the ECG signal is obtained, and then the R-wave position of the R-wave peak is obtained. Exemplarily, a point higher than the preset R wave reference voltage may be marked as an R wave peak, or a point lower than the preset R wave reference voltage may be marked as a non-R wave peak.

In this embodiment, by comparing the voltage of each point on the ECG signal with the preset R wave reference voltage, no complicated operation is required, the delay of R wave detection can be effectively reduced, and the R wave detection can be improved. accuracy, so as to accurately determine the R wave site.

In a specific embodiment, before extracting the R-wave site of the ECG signal, the method further includes: determining a signal-to-noise ratio of the ECG signal; if the signal-to-noise ratio is less than a signal-to-noise ratio threshold, re- Perform the step of acquiring the electrocardiographic signal; if the signal-to-noise ratio is not less than the threshold of the signal-to-noise ratio, perform the step of extracting the R-wave position of the electrocardiographic signal.

The signal-to-noise ratio is used to indicate the signal quality of the ECG signal. The higher the signal-to-noise ratio, the less noise in the ECG signal and the higher the signal quality of the ECG signal; The more noise in the ECG signal, the lower the signal quality of the ECG signal.

In a specific embodiment, after the ECG signal is acquired, the ECG signal is converted from a time-domain signal to a frequency-domain signal to obtain a power spectrum corresponding to the ECG signal; Integrate with the amplitude of the low frequency interval to obtain the power P ₁ in the high frequency interval and the power P ₂ in the low frequency interval. It can be understood that the high frequency interval and the low frequency interval can be set according to actual needs. For example, 0Hz- 50Hz is set as the low frequency range, 50Hz-500Hz is set as the high frequency range; by calculating the ratio P ₂ /P ₁ between the power P ₁ in the high frequency range and the power P ₂ in the low frequency range, the signal-to-noise of the ECG signal is determined Compare. The higher the ratio P ₂ /P ₁ , the higher the proportion of high-frequency noise in the ECG signal, the higher the signal quality of the ECG signal; the lower the ratio P ₂ /P ₁ , the higher the signal quality of the ECG signal. The frequency noise ratio is relatively high, and the signal quality of the ECG signal is relatively low.

In this embodiment, if the ratio P ₂ /P ₁ is less than the preset SNR threshold, the ECG signal needs to be acquired again; if the ratio P ₂ /P ₁ is not less than the preset SNR threshold than the threshold, then the calculation of the ST offset value can be performed through the ECG signal.

In this embodiment, determining the signal-to-noise ratio of the ECG signal can ensure the availability of the ECG signal; on the basis of the high-quality ECG signal, the reliability and accuracy of the ST offset value calculation can be greatly improved.

In a specific embodiment, the ST offset value calculation method is applied to an ST offset value calculation circuit, and the circuit includes a notch filter module and a bandpass filter module; the extraction of the R wave position of the ECG signal The method further includes: filtering the ECG signal by the notch filtering module to obtain a first filtered signal; filtering the first filtered signal by the bandpass filtering module to obtain a filtered signal ECG signal.

Wherein, the notch filtering module may be a notch filter for filtering out waves of a specific frequency; the bandpass filtering module may be a bandpass filter for retaining waves in a specific frequency range, for example, it can be are waves with a reserved frequency between 0.05Hz-20Hz. It can be understood that, in practical applications, the connection order between the notch filtering module and the bandpass filtering module is not limited, that is, the ECG signal can be subjected to notch filtering processing first, and then bandpass filtering is performed. processing; it is also possible to perform bandpass filtering processing on the ECG signal first, and then perform notch filtering processing.

In this embodiment, the power frequency signal in the ECG signal can be filtered out through the notch filter module. Wherein, the power frequency signal refers to a signal generated by the operation of the device for acquiring the ECG signal. For example, if the model of the lead system shown in FIG. 1 is 50 Hz during operation, the notch filter module can be a notch filter capable of filtering out 50 Hz waves.

In this embodiment, the notch filter module and the bandpass filter module can effectively avoid the interference of clutter to the signal, improve the signal quality, and further improve the accuracy of the ST offset value calculation.

In a specific implementation, after the R-wave location of the ECG signal is extracted, a larger Q-wave starting point and J-point detection interval can also be determined based on the R-wave location, and the detection intervals are symmetrically distributed in the R wave On both sides of the site, with the R wave site as the center, the left section of the R wave site is used to detect the starting point of the Q wave, and the right section of the R wave site is used to detect the J point. The starting point of the Q wave refers to the starting point of the QRS wave, which may be the starting point of the Q wave (5) as shown in FIG. 6 ; the point J refers to the ending point of the S wave, which may be the ending point of the S wave as shown in FIG. 6 . (8). In practical applications, the detection interval of the start point of the Q wave and the detection interval of the J point can be set according to the actual ECG signal. For example, the detection interval of the starting point of the Q wave may be [Rpos-MS100, Rpos], indicating that the interval size is an interval 100 milliseconds to the left of the R wave point; the detection interval of the J point may be [Rpos, Rpos+MS100 ], indicating that the interval size is the interval 100 milliseconds to the right of the R wave site.

In this embodiment, by setting the detection interval of the start point of the Q wave and the detection interval of the J point, the influence of redundant bands on the detection can be effectively avoided, the amount of detected data can be reduced, and the detection accuracy can be improved.

Step 703: Determine a first Q wave start point set and a first S wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset square formula.

The starting point of the Q wave refers to the above-mentioned starting point of the Q wave, and the ending point of the S wave refers to the above-mentioned J point. After the detection interval of the starting point of the Q wave and the detection interval of the J point are determined, the ECG signal can be amplified to improve the signal quality, and then the starting point of the Q wave and the J point can be determined based on the amplified signal. Specifically, the amplitude characteristic of the ECG signal can be amplified by a square formula, and based on the ECG signal with obvious amplitude characteristic, the first Q wave is determined by taking the R wave position as the center and detecting to the left and right sides. The starting point set and the first S wave ending point set.

In a specific embodiment, the first Q wave start point set and the first S wave end point set in the ECG signal are determined based on the R wave position of the ECG signal and a preset square formula, The method includes: performing square amplification on the ECG signal through a preset square formula to obtain a square amplification signal corresponding to the ECG signal; and determining the cardiac signal from the square amplification signal based on the R wave position. The first set of Q-wave starting points and the first set of S-wave ending points in the electrical signal.

Wherein, the square formula may be: ECGsq(k)=ECG(k) ² .

The search condition can be set as: ECG _sq (k)≤xA, where A is the amplitude in the squared amplified signal, and x is the amplitude coefficient. Specifically, A refers to the R wave amplitude value corresponding to the R wave position, and x can be 1%. In this case, the search condition is: according to the specified search direction, the first m points whose amplitude is less than 1% amplitude. As shown in Fig. 8A, the first set of Q-wave starting points [Qpos_1, . [Jpos_1,...,Jpos_m]. Wherein, m is the number of pointing points, which may be m=10 in an example.

In this embodiment, after the first Q wave starting point set and the first S wave ending point set are determined, it is also possible to determine the number of Q wave starting points in the first Q wave starting point set and the first S wave ending point set Whether the number of J-points in the set meets the preset threshold, and if not, adjust the magnitude of the amplitude coefficient x in the Q-wave starting point and the J-point search conditions. For example, the preset threshold may be 10, and it is determined whether m≥10 is established. If not, the value of x is dynamically adjusted. For example, the adjusted search condition may be: ECG _sq (k)≤(0.1+x)A. It should be noted that after adjusting the search conditions for the Q wave start point and the J point, the first Q wave start point set and the first S wave end point set can be adjusted synchronously, or only one of them can be adjusted. For example, when x=0.01, if the first Q wave starting point set has met the preset threshold, but the first S wave ending point set has not yet reached the preset threshold, then ECG _sq (k)≤(0.1+0.01)A search conditions, and adjust the first Q wave starting point set and the first S wave ending point set so that the number of Q wave starting points in the first Q wave starting point set and the number of Q wave starting points in the first S wave ending point set are the same as those in the first S wave ending point set The number of J points all meet the preset threshold; the first Q wave starting point set that meets the preset threshold can also be reserved and stored, and the search is performed according to the search condition of ECG _sq (k)≤(0.1+x)A, and only the first The S-wave termination point set is adjusted so that the number of J points in the first S-wave termination point set satisfies the preset threshold.

In this embodiment, the amplitude characteristics of the ECG signal can be highlighted by square amplification, and by presetting the search conditions and dynamically adjusting the search conditions, it can ensure that enough first Q wave start points and first S waves are obtained. End point, thus improving the accuracy of ISO point and ST point position.

Step 704: Determine a second Q-wave start point set and a second S-wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset differential formula.

Wherein, the slope characteristic of the ECG signal may be embodied by differential processing, and the second Q wave start point set and the second S wave end point set may be determined based on the differential signal with obvious slope characteristic.

In a specific embodiment, the second Q wave start point set and the second S wave end point set in the ECG signal are determined based on the R wave position of the ECG signal and a preset differential formula, The method includes: performing signal processing on the ECG signal through a preset differential formula to obtain a differential signal corresponding to the ECG signal; and determining the ECG signal from the differential signal based on the R wave position The first set of Q-wave starting points and the first set of S-wave ending points in .

Wherein, the difference formula can be:

ECG _diff (k)=ECG(k)-2*ECG(k-2)+ECG(k-4).

Among them, the search condition can be set as: ECG _diff (k)∈[-t, t], where the difference t is the threshold value of the differential signal search, the smaller the ordinate of the differential signal, the smaller the corresponding ECG signal slope , the smoother the position of the corresponding signal feature point. Specifically, the initial condition may be t=1, and the search condition at this time is n points where the value of the differential signal is [-1, 1]. As shown in Fig. 8B, from the R wave position to the left and right sides, the second Q wave starting point set [QposZ_1,...,QposZ_n1] and the second S wave ending point set that satisfy the search conditions are counted [JposZ_1, ..., JposZ_n2]. Wherein, n1 and n2 are the number of points, exemplarily, n1=10, n2=10.

In this embodiment, after the second Q wave starting point set and the second S wave ending point set are determined, it is also possible to determine the number of Q wave starting points in the second Q wave starting point set and the second S wave ending point set Whether the number of J points meets the preset threshold, and if not, adjust the size of t in the search conditions for the starting point of the Q wave and the J point. For example, the preset threshold can be 10, and it is judged whether n1≥10 and whether n1≥10 is established. If not, the value of t can be adjusted dynamically. For example, t=(1+15%)t can be set, and the adjusted search condition can be:

ECG _diff (k)∈[-(1+15%)t,(1+15%)t].

It should be noted that after adjusting the search conditions for the start point of the Q wave and the point J, the second Q wave start point set and the second S wave end point set can be adjusted synchronously, or only one of them can be adjusted. For example, when t=1, if the second Q wave starting point set has met the preset threshold, but the second S wave ending point set has not reached the preset threshold, the ECG _diff (k)∈[-(1+15 %)t, (1+15%)t] search conditions, and at the same time adjust the second Q wave start point set and the second S wave end point set, so that the Q wave in the second Q wave start point set The number of starting points and the number of J points in the second S wave termination point set both meet the preset threshold; the second Q wave starting point set that meets the preset threshold can also be reserved and stored, according to ECG _diff (k)∈[-(1 The search conditions of +15%)t and (1+15%)t are searched, and only the second S-wave termination point set is adjusted so that the number of J points in the second S-wave termination point set meets the preset threshold.

In this embodiment, the slope characteristic of the ECG signal can be effectively highlighted through differential processing, and by presetting the search conditions and dynamically adjusting the search conditions, it can ensure that enough starting points of the second Q wave and second S waves are obtained. End point, thus improving the accuracy of ISO point and ST point position.

Step 705: Determine the position of the isoelectric point of the ECG signal according to the first Q wave starting point set and the second Q wave starting point set.

The position of the equipotential point refers to the value of the ordinate corresponding to the equipotential point (ISO point), and specifically, may be the value of the ordinate corresponding to the ISO point (4) as shown in FIG. 6 . The equipotential point position may be a point on the zero potential difference line 110 as described in FIGS. 4-5 .

In a specific embodiment, after the first Q-wave starting point set and the second Q-wave starting point set are determined, it is also necessary to judge the rationality of the Q-wave starting point, and eliminate the points with larger errors, Reduce the influence of noise and improve the accuracy of the Q-wave starting point, thereby improving the accuracy of the ST offset value.

In this embodiment, the rationality of the starting point of the Q wave can be judged by the following conditions:

The first Q wave start point set:

Mean_Qpos=mean([Qpos_1,...,Qpos_m])

T1=a|Qpos_m-Qpos_1|

The valid interval of the starting point of the first Q wave is: [Mean_Qpos–T1, Mean_Qpos+T1]

Among them, Mean_Qpos is the average value of m Q wave starting points in the first Q wave starting point set, and T1 is a times the length of the area between the first Q wave starting point and the mth Q wave starting point in the first Q wave starting point set. In practical applications, a can be adjusted according to actual needs, for example, a=0.4.

The second Q wave starting point set:

Mean_QposZ=mean([QposZ_1,...,QposZ_n1])

T3=c|QposZ_n1-QposZ_1|;

The effective interval for the starting point of the second Q wave is: [Mean_QposZ–T3, Mean_QposZ+T3]

Among them, Mean_QposZ is the average value of n1 Q wave starting points in the second Q wave starting point set, and T3 is c times the length of the area between the first Q wave starting point and the n1th Q wave starting point in the second Q wave starting point set. In practical applications, a can be adjusted according to actual requirements, for example, c=0.45.

In this embodiment, after judging the rationality of Q, the first Q wave starting point valid interval and the Q wave starting point in the second Q wave starting point valid interval can be screened respectively to obtain the filtered first Q wave The starting point and the starting point of the second Q wave after screening. Wherein, min|Qpos_i1-QposZ_j1| may be used to screen the Q-wave starting points in the first Q-wave starting point valid interval and the second Q-wave starting point valid interval. Wherein, Qpos_i1 is any Q-wave starting point in the effective interval of the first Q-wave starting point, and QposZ_j1 is any Q-wave starting point in the second Q-wave starting point effective interval. Specifically, the two starting points of the Q wave with the smallest difference are selected as the starting point of the first Q wave after screening and the starting point of the second Q wave after the screening. Then, according to the principle of being close to the R wave, a point closest to the R wave is determined from the starting point of the first Q wave after screening and the starting point of the second Q wave after screening as the starting point of the target Q wave.

In this embodiment, after the starting point of the target Q wave is determined, the position of the isoelectric point can be determined according to the heart rate. Specifically, the position of the equipotential point, that is, the ISO point, is determined according to the following formula.

ISO_pos=Q_POS–t ₁

Move the target Q-wave origin to the left by t ₁ milliseconds according to the above formula, where t ₁ is determined by the heart rate. If the heart rate is greater than 120, t ₁ takes the number of sampling points corresponding to 20 milliseconds; if the heart rate is not greater than 120, then t ₁ takes the number of sampling points corresponding to 30 milliseconds.

In this embodiment, by acquiring the mean value in the set of starting points of the first Q wave, and reducing the length of the region between the starting point of the first Q wave and the starting point of the mth Q wave; and by acquiring the mean value in the set of starting points of the second Q wave mean, and reduce the length of the region between the start of the first Q wave and the start of the n1th Q wave. It can effectively judge the rationality of the starting point of the Q wave, eliminate the points with large errors, reduce the influence of noise, and improve the accuracy of the ST offset value. Through the cyclic screening and the principle of being close to the R wave, the noise can be further removed, the accuracy of the starting point of the Q wave can be improved, and the accuracy of the ST offset value can be further improved.

Step 706: Determine the ST point position of the ECG signal according to the first S wave termination point set and the second S wave termination point set.

Wherein, the position of the ST point may be a point on the ST segment where the ST point (9) as described in FIG. 6 is located.

In a specific embodiment, after the first S-wave termination point set and the second S-wave termination point set are determined, it is also necessary to judge the rationality of point J, eliminate points with large errors, and reduce The influence of noise improves the accuracy of the J point, thereby improving the accuracy of the ST offset value.

In this embodiment, the rationality of point J can be judged by the following conditions:

The first S-wave termination point set:

Mean_Jpos=mean([Jpos_1,...,Jpos_m])

T2=b|Jpos_m-Jpos_1|;

The valid interval of the first J point is: [Mean_Jpos–T2, Mean_Jpos+T2];

Among them, Mean_Jpos is the mean value of m J points in the first S wave starting point set, and T2 is b times the length of the area between the first J point and the mth J point in the first J wave starting point set. In practical applications, b can be adjusted according to actual requirements, for example, b=0.45.

The second S-wave termination point set:

Mean_JposZ=mean([Qpos_1,...,Qpos_n2])

T4=d|JposZ_n2-JposZ_1|

The valid interval of the second J point is: [Mean_JposZ–T4, Mean_JposZ+T4]

Among them, Mean_Jpos is the mean value of n2 J points in the second S wave starting point set, and T4 is d times the length of the area between the first J point and the n2th J point in the second Q wave starting point set. In practical applications, d can be adjusted according to actual requirements, for example, it can be d=0.45.

In this embodiment, after the rationality judgment of J is over, the first J point valid interval and the J points in the second J point valid interval can be screened respectively, and the screened first J point and the screened first J point can be obtained. After the second J point. Wherein, min|Jpos_i1-JposZ_j1| may be used to filter the J points in the first J point valid interval and the second J point valid interval. Among them, Jpos_i1 is any J point in the effective interval of the first J point, and JposZ_j1 is any J point in the effective interval of the second J point. Specifically, two J points with the smallest difference are screened out as the screened first J point and the screened second J point. Then, according to the principle of being close to the R wave, a point closest to the R wave is determined as the target J point from the screened first J point and the screened second J point.

In this embodiment, after the target J point is determined, the ST point position can be determined according to the heart rate. Specifically, the ST point position is determined according to the following formula.

ST_pos=J_POS+t ₂

According to the above formula, move the target J point to the right by the number of sampling points corresponding to t ₂ milliseconds, where t ₂ is determined by the heart rate. If the heart rate is greater than 120, t ₂ takes the number of sampling points corresponding to 60 milliseconds; if the heart rate is not greater than 120, t ₂ takes the number of sampling points corresponding to 80 milliseconds.

In this embodiment, by acquiring the mean value in the set of starting points of the first J wave, and reducing the length of the region between the first J point and the mth J point; and by acquiring the mean value in the set of starting points of the second J wave, And reduce the length of the area between the first J point and the n1th J point. It can effectively judge the rationality of the J point, eliminate the point with large error, reduce the influence of noise, and improve the accuracy of the ST offset value. Through the cyclic screening and the principle of close proximity to the R wave, the noise can be further removed, the accuracy of the J point can be improved, and the accuracy of the ST offset value can be further improved.

Step 707: Determine the ST offset value of the ECG signal according to the position of the isoelectric point and the position of the ST point.

Wherein, after the positions of the equipotential point and the ST point are determined, the difference between the ordinates of the equipotential point position and the ST point position can be calculated in the original signal, and the difference is used as the ST offset value.

The present application proposes a method for calculating an ST offset value: after obtaining an ECG signal and extracting the R-wave position of the ECG signal, the calculation method is determined based on the R-wave position of the ECG signal and a preset square formula. The first Q wave start point set and the first S wave termination point set in the ECG signal, and the second Q wave in the ECG signal is determined based on the R wave position of the ECG signal and a preset difference formula. The wave start point set and the second S wave end point set; in this scheme, the amplitude characteristics of the ECG signal can be highlighted by square amplification, thereby effectively improving the signal quality, and can accurately determine the Q wave start point set and the ECG signal. S wave termination point set, thereby improving the accuracy of ST offset value calculation; and then determining the isoelectric point position of the ECG signal through the first Q wave starting point set and the second Q wave starting point set, And after the ST point position of the ECG signal is determined through the first S wave termination point set and the second S wave termination point set, the heart rate is determined according to the isoelectric point position and the ST point position. The ST offset value of the electrical signal; in this scheme, after square amplification and differential processing, based on the high-precision Q wave start point set and S wave end point set, the position of the equipotential point and the ST point can be accurately determined, and the The ST offset value is accurately determined, and will not be affected by drift in the ECG signal, which reduces the difficulty of medical staff judging the patient's cardiac physiological state and improves the accuracy of medical staff judgment.

In a specific embodiment, as shown in FIG. 9 , after determining the ST offset value of the ECG signal according to the position of the isoelectric point and the position of the ST point, the method further includes:

Step 901, displaying the ST offset value display area, the ST offset value display area includes a concentric ring display diagram; the concentric ring display diagram includes a plurality of concentric circles used to represent different cascaded ST offset values ring.

Wherein, the ST value display area includes a concentric ring display diagram. As shown in Figure 10, the upper part of the concentric ring display diagram is set to lead I, II, III, aVR, aVL, and aVF from the center of the circle to the largest radius, and the lower part is from the center to the largest radius. V1, V2, V3, V4, V5, V6 leads; and the positive value direction is clockwise, the negative value direction is counterclockwise, and the 0-0 line is the dividing line between the positive and negative ST offset values, which is divided by the upper and lower parts. The boundary line and the positive and negative boundary lines are divided together to obtain four fan-shaped regions. Combined with the specified positive value direction, the positive and negative properties of each region can be obtained as shown in Figure 10. In practical applications, it can be explicitly marked by "+" and "-" of different colors.

In practical applications, if a total of 12 leads, including standard limb leads, pressurized unipolar limb leads, and V1 to V6, cannot meet the testing requirements during routine ECG examination. If dextrocardia, right ventricular hypertrophy, myocardial infarction are suspected, and leads V7, V8, V9 and V3R need to be added, the concentric circle display diagram in this scheme can also display 12 leads. Display of leads V7, V8, V9 and V3R.

Step 902: Determine the ratio of the ST offset value to the preset display threshold value according to the preset display threshold value corresponding to the concentric ring display diagram; the preset display threshold value is used to indicate the concentric rings Displays the maximum value of the ST offset value that the graph can display.

Among them, set the maximum value of the ST offset value that can be displayed by a concentric ring display graph. For example, set the maximum range of the ST offset value that can be represented by a half concentric ring to [-A, +A]. On this basis, it can be obtained that the size of the ST offset value represented by each degree of central angle in the half concentric rings is 2*A/180. Therefore, if the ST offset value B is calculated, the ST offset value B can be represented by an annular sector area with a central angle of 2*A*B/180 in the concentric rings. As shown in FIG. 11 , the larger the central angle, the larger the ST offset value (absolute value). As shown in Figure 11, the corresponding leads from top to bottom and the ST offset values in this lead are: aVF(0.8), aVL(-0.5), aVR(0.6), III(-0.7), II (0.7), I (-0.8), V1 (-0.9), V2 (0.6), V3 (-0.6), V4 (-0.4), V5 (-0.6), V6 (0.5).

Step 903 , according to the ratio, display a first annular sector area representing the ST offset value in the concentric circles corresponding to the ST offset value.

Wherein, the concentric rings corresponding to the ST offset value refer to the ST offset value, and the concentric rings correspond to the same lead. For example, the ST offset value for lead V6 is to be represented on the concentric rings that identify lead V6.

Among them, after calculating the ST offset value, the size of the annular sector area used to represent the ST offset value can be determined according to the size of the ST offset value represented by the central angle of each degree, and the size of the annular sector can be determined on the concentric circles. display.

In this embodiment, by using concentric rings to display different rings to identify different leads, the ST offset value in the multi-lead ECG can be clearly displayed according to the type of lead, and the ST offset value can be displayed More intuitive.

In a specific embodiment, after displaying the annular sector area representing the ST offset value in concentric rings corresponding to the ST offset value according to the ratio in a preset display order, the method further includes: Obtain the preset isoelectric point position preset by the user; determine the isoelectric point position offset value of the ECG signal according to the isoelectric point position and the preset isoelectric point position; the isoelectric point position The offset value is used to indicate the difference between the position of the equipotential point and the preset position of the equipotential point; according to the preset display threshold, it is determined that the offset value of the equipotential point position accounts for the preset display threshold Based on the first annular sector area, according to the ratio of the isoelectric point position offset value to the preset display threshold, the concentric ring display corresponding to the ST offset value indicates that the isoelectric point The second annular sector of the position offset value of the potential point.

The preset display threshold is also used to indicate that the concentric ring display graph can display the maximum value of the offset value of the isoelectric point position, and the indicated maximum value of the position offset value of the isoelectric point is equal to the maximum value of the ST offset value .

Among them, when performing real-time ST analysis, the annular sector area can simultaneously reflect the ST offset value, the difference between the current heartbeat isoelectric point position and the preset isoelectric point position, the positive and negative values, and the relative relationship between the two. . As shown in Figure 12, from top to bottom corresponding to aVF (0.8/-0.2), aVL (-0.5/-0.3), aVR (0.6/-0.2), III (-0.7/0.1), II (0.7/0.1 ), I(-0.8/0.1), V1(-0.9/0.2), V2(0.6/-0.2), V3(-0.6/-0.1), V4(-0.4/0.1), V5(-0.5/0.1) , V6 (0.5/-0.2). Taking lead aVF as an example, in the nth heartbeat, the position of the isoelectric point and the ST point are obtained by the calculation method, and the ST offset value is 0.8, and the ordinate value at the ST point is compared with the manually set value. The ordinate value at the position of the equipotential point, the difference between the ordinate value at the equipotential point and the ordinate value at the manually set position of the equipotential point (the offset value of the position of the equipotential point) is -0.2, which can be obtained, The real-time ST offset value in the current heart beat is: 0.8+(-0.2)=0.6mV. In this embodiment, it can be ensured that the end edge of the position offset value of the equipotential point always falls on the region boundary corresponding to the real-time ST offset value, and the change amount of the position offset value of the equipotential point is displayed more obviously, etc. The start edge of the potential point position offset value is defined on the end edge of the ST offset value.

In a specific embodiment, as shown in FIG. 13 , in order to avoid that the ST offset value, the difference between the current heartbeat baseline and the manually set isoelectric point position (equipotential point position offset value) is very small, a ring-shaped sector is caused. If the area is too small, the specific values in the graph are difficult to identify (arrange), ST offset values, and the specific values of the equipotential point position offset values are difficult to distinguish. , the solution proposed in this application can also set a detailed numerical comparison legend next to the concentric ring display diagram, and the legend corresponds to the division area of each lead on the 0-0 axis, which is very intuitive and clearly identifies the current lead. In addition, in different modes, the corresponding indication area can also light up, which is convenient for users to observe; in order to meet the different observation needs of professionals for ST offset value indicators, a separate classification table is also set at the bottom. , the ST offset value is displayed intuitively through the table, which is convenient for users to compare data.

In one embodiment, as shown in FIG. 14, the present application proposes an ST offset value calculation device, and the device includes:

The ECG signal acquisition module 1401 is configured to acquire the ECG signal, where the ECG signal includes the ST segment located between the QRS complex and the T wave.

The R-wave site extraction module 1402 is configured to extract the R-wave site of the ECG signal.

The first point set determination module 1403 is configured to determine the first Q wave start point set and the first S wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset square formula .

The second point set determination module 1404 is configured to determine the second Q wave start point set and the second S wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset difference formula .

The isoelectric point determination module 1405 is configured to determine the position of the isoelectric point of the ECG signal according to the first set of Q-wave starting points and the second set of Q-wave starting points.

The ST point determination module 1406 is configured to determine the ST point position of the ECG signal according to the first S wave termination point set and the second S wave termination point set.

The ST offset value determination module 1407 is configured to determine the ST offset value of the ECG signal according to the position of the isoelectric point and the position of the ST point.

As shown in FIG. 15 , in one embodiment, it is an internal structure diagram of a computer device. The computer equipment may be an ST offset value calculation apparatus, or a terminal or server connected to an ST offset value calculation apparatus. As shown in Figure 15, the computer device includes a processor, memory, and a network interface connected by a system bus. Wherein, the memory includes a non-volatile storage medium and an internal memory. The non-volatile storage medium of the computer device stores an operating system, and also stores a computer program, which, when executed by the processor, enables the processor to implement a method for calculating an ST offset value. A computer program may also be stored in the internal memory, and when executed by the processor, the computer program may cause the processor to execute a method for calculating an ST offset value. The network interface is used to communicate with external devices. Those skilled in the art can understand that the structure shown in FIG. 15 is only a block diagram of a partial structure related to the solution of the present application, and does not constitute a limitation on the computer equipment to which the solution of the present application is applied. Include more or fewer components than shown in the figures, or combine certain components, or have a different arrangement of components.

In one embodiment, a method for calculating an ST offset value provided by the present application may be implemented in the form of a computer program, and the computer program may be executed on a computer device as shown in FIG. 15 . Various program templates constituting the ST offset value calculating means may be stored in the memory of the computer device. For example, the ECG signal acquisition module 1401, the R wave location extraction module 1402, the first point set determination module 1403, the second point set determination module 1404, the isoelectric point determination module 1405, the ST point determination module 1406, the ST offset value Determine block 1407.

A computer device includes a memory and a processor, the memory stores a computer program, and when the computer program is executed by the processor, the processor is caused to perform the following steps: acquiring an electrocardiogram signal, the electrocardiogram The ST segment between the group and the T wave; extract the R wave position of the ECG signal; determine the first Q in the ECG signal based on the R wave position of the ECG signal and a preset square formula Wave start point set and first S wave end point set; determine the second Q wave start point set and the second S wave in the ECG signal based on the R wave position of the ECG signal and a preset difference formula Termination point set; determine the position of the isoelectric point of the ECG signal according to the first Q wave start point set and the second Q wave start point set; according to the first S wave termination point set and the first The two S wave termination point sets determine the ST point position of the ECG signal; the ST offset value of the ECG signal is determined according to the isoelectric point position and the ST point position.

In one embodiment, the determining the first Q-wave starting point set and the first S-wave ending point set in the ECG signal based on the R-wave position of the ECG signal and a preset square formula, including : perform square amplification on the ECG signal by a preset square formula to obtain a square amplification signal corresponding to the ECG signal; determine the ECG signal from the square amplification signal based on the R wave position The first set of Q-wave starting points and the first set of S-wave ending points in the signal.

In one embodiment, before extracting the R-wave site of the ECG signal, the method includes: determining a signal-to-noise ratio of the ECG signal; if the signal-to-noise ratio is less than a signal-to-noise ratio threshold, re-executing the acquisition The step of ECG signal; if the signal-to-noise ratio is not less than the signal-to-noise ratio threshold, the step of extracting the R-wave position of the ECG signal is performed.

In one embodiment, the ST offset value calculation method is applied to a ST offset value calculation circuit, and the circuit includes a notch filter module and a bandpass filter module; the extraction of the R-wave position of the ECG signal Before, it also includes: filtering the ECG signal by the notch filtering module to obtain a first filtered signal; filtering the first filtered signal by the bandpass filtering module to obtain a filtered ECG signal.

In an embodiment, after determining the ST offset value of the ECG signal according to the position of the isoelectric point and the position of the ST point, the method further includes: displaying an ST value display area, and the ST value display area includes: Concentric ring display diagram; the concentric ring display diagram includes a plurality of concentric rings used to represent different cascaded ST offset values; according to the preset display threshold corresponding to the concentric ring display diagram, determine the The ratio of the ST offset value to the preset display threshold value; the preset display threshold value is used to indicate the maximum value of the ST offset value that can be displayed by the concentric ring display diagram; The concentric circles corresponding to the ST offset value display a first annular sector area representing the ST offset value.

In one embodiment, after displaying the annular sector area representing the ST offset value in concentric rings corresponding to the ST offset value in a preset display sequence according to the ratio, the method further includes: acquiring The preset equipotential point position preset by the user; according to the equipotential point position and the preset equipotential point position, the offset value of the equipotential point position of the ECG signal is determined; The shift value is used to indicate the size of the difference between the position of the equipotential point and the preset position of the equipotential point; according to the preset display threshold, it is determined that the offset value of the equipotential point position accounts for a percentage of the preset display threshold. Ratio; based on the first annular sector area, according to the ratio of the isoelectric point position offset value to the preset display threshold value, the concentric ring display corresponding to the ST offset value indicates that the equipotential The second annular sector of the point position offset value.

A computer readable storage medium storing a computer program, when the computer program is executed by a processor, the processor is made to perform the following steps: acquiring an electrocardiogram signal, the electrocardiogram signal including a signal located between a QRS complex and a T wave The ST segment of the ECG signal is extracted; the R wave position of the ECG signal is extracted; the first Q wave starting point set and the first Q wave start point set in the ECG signal are determined based on the R wave position of the ECG signal and the preset square formula. an S wave termination point set; determine the second Q wave start point set and the second S wave termination point set in the ECG signal based on the R wave position of the ECG signal and a preset differential formula; The first Q wave starting point set and the second Q wave starting point set determine the position of the isoelectric point of the ECG signal; according to the first S wave ending point set and the second S wave ending point set Determine the ST point position of the ECG signal; determine the ST offset value of the ECG signal according to the isoelectric point position and the ST point position.

In one embodiment, the determining the first Q-wave starting point set and the first S-wave ending point set in the ECG signal based on the R-wave position of the ECG signal and a preset square formula, including : perform square amplification on the ECG signal by a preset square formula to obtain a square amplification signal corresponding to the ECG signal; determine the ECG signal from the square amplification signal based on the R wave position The first set of Q-wave starting points and the first set of S-wave ending points in the signal.

In one embodiment, before extracting the R-wave site of the ECG signal, the method includes: determining a signal-to-noise ratio of the ECG signal; if the signal-to-noise ratio is less than a signal-to-noise ratio threshold, re-executing the acquisition The step of ECG signal; if the signal-to-noise ratio is not less than the signal-to-noise ratio threshold, the step of extracting the R-wave position of the ECG signal is performed.

In one embodiment, the ST offset value calculation method is applied to a ST offset value calculation circuit, and the circuit includes a notch filter module and a bandpass filter module; the extraction of the R-wave position of the ECG signal Before, it also includes: filtering the ECG signal by the notch filtering module to obtain a first filtered signal; filtering the first filtered signal by the bandpass filtering module to obtain a filtered ECG signal.

In an embodiment, after determining the ST offset value of the ECG signal according to the position of the isoelectric point and the position of the ST point, the method further includes: displaying an ST value display area, and the ST value display area includes: Concentric ring display diagram; the concentric ring display diagram includes a plurality of concentric rings used to represent different cascaded ST offset values; according to the preset display threshold corresponding to the concentric ring display diagram, determine the The ratio of the ST offset value to the preset display threshold value; the preset display threshold value is used to indicate the maximum value of the ST offset value that can be displayed by the concentric ring display diagram; The concentric circles corresponding to the ST offset value display a first annular sector area representing the ST offset value.

In one embodiment, after displaying the annular sector area representing the ST offset value in concentric rings corresponding to the ST offset value in a preset display sequence according to the ratio, the method further includes: acquiring The preset equipotential point position preset by the user; according to the equipotential point position and the preset equipotential point position, the offset value of the equipotential point position of the ECG signal is determined; The shift value is used to indicate the size of the difference between the position of the equipotential point and the preset position of the equipotential point; according to the preset display threshold, it is determined that the offset value of the equipotential point position accounts for a percentage of the preset display threshold. Ratio; based on the first annular sector area, according to the ratio of the isoelectric point position offset value to the preset display threshold value, the concentric ring display corresponding to the ST offset value indicates that the equipotential The second annular sector of the point position offset value.

Those of ordinary skill in the art can understand that all or part of the processes in the methods of the above-mentioned embodiments can be implemented by instructing the relevant hardware through a computer program, and the program can be stored in a computer-readable storage medium, and the program is in During execution, it may include the processes of the embodiments of the above-mentioned methods. Wherein, the storage medium may be a magnetic disk, an optical disk, a read-only memory (Read-Only memory, ROM) or a random access memory (Random Access memory, RAM) or the like.

The above disclosures are only the preferred embodiments of the present application, and of course, the scope of the rights of the present application cannot be limited by this. Therefore, equivalent changes made according to the claims of the present application are still within the scope of the present application.

Claims (10)

1. A method for calculating an ST offset value, wherein the method comprises: acquiring an electrocardiographic signal, the electrocardiographic signal including an ST segment between the QRS complex and the T wave; extracting the R wave site of the ECG signal; Determine the first Q wave start point set and the first S wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset square formula; determining the second Q wave start point set and the second S wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset differential formula; Determine the position of the isoelectric point of the ECG signal according to the first Q wave starting point set and the second Q wave starting point set; Determine the ST point position of the ECG signal according to the first S-wave termination point set and the second S-wave termination point set; The ST offset value of the ECG signal is determined according to the position of the isoelectric point and the position of the ST point. 2 . The method according to claim 1 , wherein the first Q wave starting point set and the The first set of S-wave termination points, including: Perform square amplification on the ECG signal by using a preset square formula to obtain a square amplified signal corresponding to the ECG signal; Based on the R wave position, a first Q wave start point set and a first S wave end point set in the ECG signal are determined from the squared amplified signal. 3 . The method according to claim 1 , wherein determining the second Q wave starting point set in the ECG signal and the The second set of S-wave termination points, including: Perform signal processing on the ECG signal by using a preset differential formula to obtain a differential signal corresponding to the ECG signal; Based on the R wave position, a second Q wave starting point set and a second S wave ending point set in the ECG signal are determined from the differential signal. 4. The method according to claim 1, wherein before extracting the R-wave position of the ECG signal, the method comprises: determining the signal-to-noise ratio of the ECG signal; If the signal-to-noise ratio is less than the signal-to-noise ratio threshold, re-execute the step of acquiring the ECG signal; If the signal-to-noise ratio is not less than the signal-to-noise ratio threshold, the step of extracting the R-wave position of the ECG signal is performed. 5. The method according to claim 1, wherein the ST offset value calculation method is applied to an ST offset value calculation circuit, and the circuit comprises a notch filter module and a bandpass filter module; Before the extracting the R-wave site of the ECG signal, the method further includes: Perform filtering processing on the ECG signal by the notch filtering module to obtain a first filtered signal; The first filtered signal is filtered by the band-pass filtering module to obtain a filtered ECG signal. 6 . The method according to claim 1 , wherein after determining the ST offset value of the ECG signal according to the position of the isoelectric point and the position of the ST point, the method further comprises: 7 . Displaying an ST offset value display area, the ST offset value display area includes a concentric ring display diagram; the concentric ring display diagram includes a plurality of concentric rings used to represent different cascaded ST offset values; Determine the ratio of the ST offset value to the preset display threshold value according to the preset display threshold value corresponding to the concentric ring display image; the preset display threshold value is used to indicate that the concentric ring display image can be The maximum value of the displayed ST offset value; According to the ratio, a first annular sector area representing the ST offset value is displayed in concentric circles corresponding to the ST offset value. 7 . The method according to claim 6 , wherein, according to the ratio, the ring representing the ST offset value is displayed in concentric rings corresponding to the ST offset value in a preset display order. 8 . After the fan-shaped area, it also includes: Obtain the preset isoelectric point position preset by the user; According to the position of the equipotential point and the preset position of the equipotential point, the offset value of the position of the equipotential point of the ECG signal is determined; the offset value of the position of the equipotential point is used to indicate the position of the equipotential point The size of the difference from the preset isoelectric point position; According to the preset display threshold value, determine the ratio of the position offset value of the equipotential point to the preset display threshold value; Based on the first annular sector area, according to the ratio of the isoelectric point position offset value to the preset display threshold value, the concentric circles corresponding to the ST offset value are displayed to indicate the equipotential point position The second annular sector of the offset value. 8. A device for calculating an ST offset value, wherein the device comprises: an ECG signal acquisition module for acquiring an ECG signal, the ECG signal including the ST segment located between the QRS complex and the T wave; An R-wave site extraction module for extracting the R-wave site of the ECG signal; A first point set determination module, configured to determine the first Q wave start point set and the first S wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset square formula; A second point set determination module, configured to determine a second Q wave start point set and a second S wave end point set in the ECG signal based on the R wave position of the ECG signal and a preset differential formula; an isoelectric point determination module, configured to determine the position of the isoelectric point of the ECG signal according to the first Q wave starting point set and the second Q wave starting point set; ST point determination module, configured to determine the ST point position of the ECG signal according to the first S wave termination point set and the second S wave termination point set; The ST offset value determination module is configured to determine the ST offset value of the ECG signal according to the position of the isoelectric point and the position of the ST point. 9. A computer device comprising a memory and a processor, the memory storing a computer program which, when executed by the processor, causes the processor to perform the steps of the method according to claims 1-7 . 10. A computer-readable storage medium storing a computer program which, when executed by a processor, causes the processor to perform the steps of the method of claims 1-7.

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