CN116849678A

CN116849678A - ST offset value calculation method, ST offset value calculation device, computer equipment and storage medium

Info

Publication number: CN116849678A
Application number: CN202310920039.4A
Authority: CN
Inventors: 谢超成; 卜祥南; 何静; 赵锡达; 朱明亮; 尹鹏
Original assignee: Shenzhen Comen Medical Instruments Co Ltd
Current assignee: Shenzhen Comen Medical Instruments Co Ltd
Priority date: 2023-07-25
Filing date: 2023-07-25
Publication date: 2023-10-10

Abstract

The application provides a ST offset value calculation method, which comprises the following steps: acquiring an electrocardiosignal comprising an ST segment located between a QRS complex and a T wave; extracting an R wave locus of the electrocardiosignal; determining a first Q wave start point set and a first S wave end point set in the electrocardiosignal based on an R wave locus of the electrocardiosignal and a preset square formula; determining a second Q wave start point set and a second S wave end point set in the electrocardiosignal based on an R wave locus of the electrocardiosignal and a preset differential formula; determining the isoelectric point position of the electrocardiosignal according to the first Q wave starting point set and the second Q wave starting point set; determining the ST point position of the electrocardiosignal according to the first S wave end point set and the second S wave end point set; and determining an ST offset value of the electrocardiosignal according to the isoelectric point position and the ST point position.

Description

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

Technical Field

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

Background

The electrical shocks pulse the heart muscle, which shocks are conducted through the patient's body and can be measured with electrodes attached to the patient's skin. Electrodes on different sides of the heart can measure the activity at different locations of the heart muscle. An Electrocardiograph (ECG) shows the voltage between pairs of electrodes (leads) in different directions. Thus, the electrocardiographic signal may be used to indicate the overall heart rate and myocardial weakness at different locations of the myocardium. The electrocardiographic signals may be used to measure and diagnose heart rhythm abnormalities, including those arising from damage to conductive tissue through which the electrical signals are conducted. The electrocardiographic signals may be measured with a variety of different leads. Typically, a standard 12-lead measurement can be used, but other lead measurements can be used, such as 5-lead or 3-lead.

ST segment (ST elevation myocardial infarctions, STEMI) changes in the electrocardiographic signals are clinically more common electrocardiographic manifestations, and when a patient's myocardium is ischemic or injured, the ST wave portion of the electrocardiographic signal in the affected lead is shifted from the zero potential difference line. The changes in the ST segment are generally up-down offsets, referred to as "ST elevation" and "ST depression", or left-right offsets, which are reflected in changes in ST interval length, and are of greater clinical concern as "elevation" and "depression" of the ST segment. ST segment abnormality is often found in heart diseases such as myocardial ischemia, myocardial infarction, acute pericarditis, and ST value is an important index for assisting medical staff in judging the physiological state of the heart of a patient, and is also an indispensable important parameter in various electrocardiographs. However, the ST segment has various morphological changes, and when interference in electrocardiosignals is large or drift influence exists, the accuracy of ST segment identification and judgment in the prior art can be greatly reduced.

Disclosure of Invention

The application provides a method, a device, computer equipment and a storage medium for calculating an ST offset value, which are used for solving the technical problem of low calculation accuracy in the existing ST offset value calculation technology.

In a first aspect, there is provided a ST offset value calculation method, the method including:

acquiring an electrocardiosignal comprising an ST segment located between a QRS complex and a T wave;

extracting an R wave locus of the electrocardiosignal;

determining a first Q wave start point set and a first S wave end point set in the electrocardiosignal based on an R wave locus of the electrocardiosignal and a preset square formula;

determining a second Q wave start point set and a second S wave end point set in the electrocardiosignal based on an R wave locus of the electrocardiosignal and a preset differential formula;

determining the isoelectric point position of the electrocardiosignal according to the first Q wave starting point set and the second Q wave starting point set;

determining the ST point position of the electrocardiosignal according to the first S wave end point set and the second S wave end point set;

and determining an ST offset value of the electrocardiosignal according to the isoelectric point position and the ST point position.

In a second aspect, there is provided an ST offset value calculation apparatus including:

The electrocardiosignal acquisition module is used for acquiring electrocardiosignals which comprise an ST segment positioned between a QRS complex and a T wave;

the R wave locus extraction module is used for extracting R wave loci of the electrocardiosignals;

the first point set determining module is used for determining a first Q wave starting point set and a first S wave ending point set in the electrocardiosignal based on the R wave locus of the electrocardiosignal and a preset square formula;

the second point set determining module is used for determining a second Q wave starting point set and a second S wave ending point set in the electrocardiosignal based on the R wave locus of the electrocardiosignal and a preset differential formula;

the equipotential point determining module is used for determining the position of the equipotential point of the electrocardiosignal according to the first Q wave starting point set and the second Q wave starting point set;

the ST point determining module is used for determining the ST point position of the electrocardiosignal according to the first S wave ending point set and the second S wave ending point set;

and the ST offset value determining module is used for determining the ST offset value of the electrocardiosignal according to the isoelectric point position and the ST point position.

In a third aspect, there is provided 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:

extracting an R wave locus of the electrocardiosignal;

In a fourth aspect, there is provided a computer readable storage medium storing a computer program which, when executed by a processor, causes the processor to perform the steps of:

extracting an R wave locus of the electrocardiosignal;

The application can realize the following beneficial effects: acquiring an electrocardiosignal, extracting an R wave locus of the electrocardiosignal, determining a first Q wave start point set and a first S wave end point set in the electrocardiosignal based on the R wave locus of the electrocardiosignal and a preset square formula, and determining a second Q wave start point set and a second S wave end point set in the electrocardiosignal based on the R wave locus of the electrocardiosignal and a preset differential formula; according to the scheme, the amplitude characteristics of the electrocardiosignals can be highlighted through square amplification, so that the signal quality is effectively improved, a Q wave starting point set and an S wave ending point set of the electrocardiosignals can be accurately determined, and the accuracy of ST offset value calculation is further improved; then determining the position of an isoelectric point of the electrocardiosignal through the first Q wave starting point set and the second Q wave starting point set, determining the position of an ST point of the electrocardiosignal through the first S wave ending point set and the second S wave ending point set, and finally determining the ST offset value of the electrocardiosignal according to the position of the isoelectric point and the ST point; after square amplification and differential processing, the equipotential points and the ST points can be accurately determined based on the high-precision Q wave starting point set and the high-precision S wave ending point set, and the ST offset value can be accurately determined.

Drawings

FIG. 1 is a schematic diagram of a 12-lead system according to an embodiment of the present application;

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

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

fig. 4 is an electrocardiographic signal of a primary heartbeat in electrocardiographic signals of a healthy person according to an embodiment of the present application;

FIG. 5A is a schematic view of elevation of the ST segment according to an embodiment of the present application;

FIG. 5B is a schematic illustration of ST-segment depression provided by an embodiment of the present application;

FIG. 6 is an illustration of an electrocardiographic signal according to an embodiment of the present application;

fig. 7 is a flowchart of a method for calculating an ST offset value according to an embodiment of the present application;

FIG. 8A is a schematic diagram of a searching direction of a Q-wave starting point and a J-point according to an embodiment of the present application;

FIG. 8B is a schematic diagram of a searching direction of a Q-wave starting point and a J-point according to an embodiment of the present application;

fig. 9 is a flowchart of a method for calculating an ST offset value according to an embodiment of the present application;

FIG. 10 is a schematic diagram of a concentric ring display according to an embodiment of the present application;

FIG. 11 is a schematic diagram showing an ST offset value according to an embodiment of the present application;

FIG. 12 is a schematic diagram showing an ST offset value according to an embodiment of the present application;

FIG. 13 is a schematic diagram showing an ST offset value according to an embodiment of the present application;

fig. 14 is a schematic structural diagram of an ST offset value calculating apparatus according to 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 Description

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 used as an important index for assisting medical staff in judging the physiological state of the heart of the patient, and the technical scheme of the application can be suitable for obtaining the parameter of the ST offset value through an electrocardiograph, thereby assisting the medical staff in judging various medical scenes of the physiological state of the heart of the patient. Specifically, the technical scheme of the application is applied to computer equipment, and is suitable for a data processing scene of acquiring electrocardiosignals of a patient through electrocardiogram leads and then calculating ST segment offset values in the electrocardiosignals of the patient.

In practical application, the technical scheme of the application can be applied to an electrocardiogram lead detection scene with only one lead, and can also be applied to an electrocardiogram lead detection scene with a plurality of leads. It can be appreciated that in a detection scenario with multiple leads, the technical solution of the present application may be used to calculate the ST offset value of the electrocardiogram of each of the multiple leads simultaneously, or may calculate the ST offset value of the electrocardiogram of any of the multiple leads separately.

For the convenience of understanding the technical scheme of the application, an electrocardiogram lead is introduced. Wherein, electrodes are arranged at different parts of the human body and are connected with the positive electrode and the negative electrode of an electrocardiograph ammeter through lead wires, and the circuit connection method for recording the electrocardiogram is called electrocardiogram lead wires. In practice, the universal lead set is referred to as a conventional 12-lead set, and includes a limb lead connected to a limb and a chest lead connected to a chest. As shown in fig. 1, fig. 1 is a schematic diagram of the connection of a 12-lead system.

In this embodiment, as shown in fig. 2, the limb leads include standard limb leads I, ii, iii and a pressurized monopolar limb lead aVR, aVL, aVF.

Wherein the standard limb leads are bipolar leads capable of reflecting the potential difference between two limbs; standard lead I is the potential difference between the left and right hands; 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 magnitude of the standard lead record has: i+iii=ii. The pressurizing monopole limb lead is characterized in that in two electrodes, only one electrode displays potential, and the potential of the other electrode is equal to zero, and the voltage of the lead part is directly recorded; when the pressurized monopolar limb leads are connected, any one of the left hand, the right hand and the left leg is a positive electrode, and the other two combined electrodes are negative electrodes; the pressurizing monopole limb lead aVR positive electrode is a right hand, and the combined electrode of the left hand and the left leg is a negative electrode; the pressurized unipolar limb lead aVL positive electrode is a left hand, and the combined electrode of the right hand and the left leg is a negative electrode; the pressurized monopolar limb lead aVF positive electrode 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 monopolar leads, including V1-V6 leads. The positive electrode is arranged at a specified position of the chest wall during detection; in addition, 3 electrodes of the limb lead are respectively connected with the negative electrode through a 5K resistor to form a central electric end, and the connection can lead the electric potential at the position to be close to zero electric potential and stable, so the electrode is used as the negative electrode of the lead. As shown in fig. 3, the chest lead detection electrode is specifically placed at the following positions: 1 is V1, and is positioned between the 4 th rib of the right edge of the foot bone; 2 is V2, and is positioned between the 4 th rib of the left edge of the sternum; 3 is V3, and is positioned at the midpoint of the connecting line of the two points V2 and V4; 4 is V4, and is positioned at the intersection of the left collarbone midline and the 5 th rib; 5 is V5, which is positioned at the level of the left anterior axillary line V4; 6 is V6 and is positioned at the level of the left axillary midline V4.

Wherein, during routine electrocardiographic examination, 12 leads of standard limb leads, pressurized monopole limb leads and V1-V6 can meet the requirement. If right heart, right ventricular hypertrophy and myocardial infarction are suspected, V7, V8, V9 and V3R leads are needed to be added, and V7 is at the level of a left posterior axillary line V4; v8 is horizontal at left scapula V4; v9 is horizontal at left ridge bypass V4; V3R is at the corresponding position of V3 in the right chest.

To facilitate understanding of the present solution, an electrocardiogram will be described. As shown in fig. 4, fig. 4 shows an electrocardiographic signal of a single heartbeat among electrocardiographic signals 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 represents an atrial depolarization, with the initial portion of the P-wave primarily reflecting the right atrial depolarization and the terminal portion primarily reflecting the left atrial depolarization. As can be seen from the figure, the Q wave is a downward shifted wave after P-wave. A typical Q wave represents a cardiac-spaced depolarizer. The R-wave is the first upward-shifted wave after P-wave, which represents early ventricular depolarization. The S wave is the first negatively shifted wave after the R wave, which represents late ventricular depolarization. The T wave is generally upwardly convex, slightly arcuate and slightly asymmetric. The T wave represents the repolarization of the ventricles. The QRS complex starts at the start of the Q wave and ends at the end of the S wave. The QRS complex represents the duration 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 electrocardiograph signal. In other words, the ST wave is normally zero potential difference.

As shown in fig. 5A and 5B, the ST segment may appear to be raised (fig. 5A) or depressed (fig. 5B) in the vertical direction 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 lowered. ST elevation or depression may be caused by cardiac injury, ventricular wall tumors, variant angina, pericarditis, myocardial ischemia, or other conditions. As will be appreciated by the skilled artisan from the description herein, elevation of the ST segment in FIG. 5A and depression of the ST segment in FIG. 5B may still occur for the same patient through different lead examinations.

Taking ST depression as an example, as shown in fig. 6, fig. 6 is an electrocardiographic signal containing ST depression. Wherein, (1) is a P wave starting point, (2) is a P wave position, (3) is a P wave ending point, (4) is an ISO point (equipotential point), (5) is a Q wave starting point, (6) is an R wave position, (7) is an S wave position, (8) is an S wave ending point, (9) is an ST point, (10) is a T wave starting point, (11) is a T wave position, and (12) is a T wave ending point. In fig. 6, the ST value is the ST-segment offset value 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 the application, the position of the zero potential difference line, namely the position of an ISO point, is determined by determining the starting point of the Q wave; determining the position of an ST point by determining an S-wave termination point; and further determines the ST offset value.

In one embodiment, as shown in fig. 7, the present application proposes a ST offset value calculation method, which includes:

step 701, an electrocardiographic signal is acquired, the electrocardiographic signal comprising an ST segment located between a QRS complex and a T wave.

The electrocardiograph signal is obtained through detection of a lead system as shown in fig. 1, or can be obtained from a storage device or medium storing electrocardiograph signal data. The electrocardiosignal also comprises lead type data corresponding to the electrocardiosignal, and the lead type data is used for indicating the lead type of the detected electrocardiosignal; the lead type is one or more of the leads described in fig. 1-3, and may be, for example, one of the limb leads connected to the limb and/or one of the chest leads connected to the chest, or may be multiple of the limb leads connected to the limb and/or multiple of the chest leads connected to the chest.

Wherein the electrocardiographic signal comprises an ST segment located between the QRS complex and the T wave as described in fig. 4 to 6.

And step 702, extracting R wave sites of the electrocardiosignals.

Wherein the R-wave may be an R-wave in an electrocardiographic signal as described in fig. 6. The R-wave position point is used to indicate the position of the R-wave, and may specifically be the abscissa Rpos corresponding to the R-wave position (6) shown in fig. 6.

In a specific embodiment, when the electrocardiosignal is acquired, the voltage of each point on the electrocardiosignal can be obtained at the same time. And comparing the voltage of each point on the electrocardiosignal with a preset R wave reference voltage to obtain an R wave crest of the electrocardiosignal, and further obtaining an R wave locus of the R wave crest. For example, 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 electrocardiograph signal with the preset R-wave reference voltage, complex operation is not required, so that the delay of R-wave detection can be effectively reduced, the accuracy of R-wave detection is improved, and thus the R-wave position point is accurately determined.

In a specific embodiment, before the extracting the R-wave position of the electrocardiograph signal, the method further includes: determining a signal-to-noise ratio of the electrocardiosignal; if the signal-to-noise ratio is smaller than the signal-to-noise ratio threshold, re-executing the step of acquiring the electrocardiosignal; and if the signal-to-noise ratio is not smaller than the signal-to-noise ratio threshold, executing the step of extracting the R wave locus of the electrocardiosignal.

The signal-to-noise ratio is used for indicating the signal quality of the electrocardiosignal, and the higher the signal-to-noise ratio is, the less noise in the electrocardiosignal is indicated, and the higher the signal quality of the electrocardiosignal is; the lower the signal-to-noise ratio, the more noise in the electrocardiosignal and the lower the signal quality of the electrocardiosignal.

In a specific embodiment, after the electrocardiosignal is obtained, the electrocardiosignal is converted from a time domain signal to a frequency domain signal, and a power spectrum corresponding to the electrocardiosignal is obtained; then respectively integrating the amplitudes of the high-frequency interval and the low-frequency interval to obtain the power P of the high-frequency interval ₁ Power P with low frequency range ₂ It can be appreciated that the high-frequency interval and the low-frequency interval can be set according to actual requirements, for example, 0Hz-50Hz can be set as a low-frequency interval, and 50Hz-500Hz can be set as a high-frequency interval; by calculating the power P of the high frequency interval ₁ Power P with low frequency range ₂ Ratio P between ₂ /P ₁ To determine a signal to noise ratio of the electrocardiographic signal. Ratio P ₂ /P ₁ The higher the electrocardiosignal is, the lower the high-frequency noise ratio in the electrocardiosignal is, and the signal quality of the electrocardiosignal is higher; ratio P ₂ /P ₁ The lower the electrocardiosignal is, the higher the high-frequency noise in the electrocardiosignal is, and the signal quality of the electrocardiosignal is lower.

In the present embodiment, if the ratio P ₂ /P ₁ If the signal-to-noise ratio is smaller than the preset signal-to-noise ratio threshold, the electrocardiosignals need to be acquired again; if the ratio P ₂ /P ₁ Not smaller thanAnd calculating the ST offset value through the electrocardiosignal if the preset signal to noise ratio threshold value is met.

In the embodiment, the signal to noise ratio of the electrocardiosignal is determined, so that the availability of the electrocardiosignal can be ensured; on the basis of high-quality electrocardiosignals, the reliability and accuracy of ST offset value calculation can be greatly improved.

In a specific embodiment, the ST offset value calculation method is applied to a ST offset value calculation circuit, and the circuit comprises a notch filter module and a band-pass filter module; before the extracting of the R-wave locus of the electrocardiosignal, the method further comprises: the notch filter module is used for carrying out filter processing on the electrocardiosignals to obtain first filter signals; and filtering the first filtering signal through the band-pass filtering module to obtain a filtered electrocardiosignal.

The notch filter module may be a notch filter, for filtering waves with specific frequencies; the band pass filter module may be a band pass filter for retaining waves in a specific frequency range, for example, may be waves with a retaining frequency between 0.05Hz and 20 Hz. It can be appreciated that in practical applications, the connection sequence between the notch filter module and the band-pass filter module is not limited, namely: the electrocardiosignal can be subjected to notch filtering treatment and then subjected to band-pass filtering treatment; the band-pass filtering processing and the notch filtering processing can be performed on the electrocardiosignal.

In this embodiment, the notch filter module may filter out the power frequency signal in the electrocardiograph signal. The power frequency signal is a signal generated by the device for acquiring the electrocardiosignal. For example, if the type of the lead frame shown in fig. 1 is 50Hz, the notch filter module may be a notch filter capable of filtering 50Hz waves.

In this embodiment, the notch filtering module and the band-pass filtering module can effectively avoid interference of clutter on signals, improve signal quality, and further improve accuracy of calculating the ST offset value.

In a specific implementation, after the R-wave position point of the electrocardiograph signal is extracted, a larger Q-wave starting point and a J-point detection interval can be determined based on the R-wave position point, the detection intervals are symmetrically distributed on two sides of the R-wave position point, the left-side interval of the R-wave position point is used for detecting the Q-wave starting point, and the right-side interval of the R-wave position point is used for detecting the J-point. Wherein the start point of the Q wave refers to the start point of the QRS wave, and may be the start point (5) of the Q wave as shown in fig. 6; the J point refers to the S-wave end point, and may be the S-wave end point (8) as described in fig. 6. In practical applications, the detection interval of the Q-wave start point and the detection interval of the J-point may be set according to an actual electrocardiographic signal. For example, the detection interval of the Q-wave origin may be [ Rpos-MS100, rpos ], representing an interval size of 100 milliseconds to the left of the R-wave locus; the detection interval of the J point can be [ Rpos, rpos+MS100], which represents the interval size of the R wave locus to the right 100 milliseconds.

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

Step 703, determining a first Q-wave start point set and a first S-wave end point set in the electrocardiograph signal based on the R-wave position point of the electrocardiograph signal and a preset square formula.

Wherein the Q wave start point refers to the Q wave start point, and the S wave end point refers to the J point. After the detection interval of the Q wave starting point and the detection interval of the J point are determined, the electrocardiosignal can be amplified to improve the signal quality, and then the determination of the Q wave starting point and the J point is carried out based on the amplified signals. Specifically, the amplitude characteristic of the electrocardiosignal can be amplified through a square formula, and based on the electrocardiosignal with obvious amplitude characteristic, the electrocardiosignal is detected by taking an R wave locus as the center and on the left and right sides, and a first Q wave starting point set and a first S wave ending point set are determined.

In a specific embodiment, the determining the first Q-wave start point set and the first S-wave end point set in the electrocardiograph signal based on the R-wave position point of the electrocardiograph signal and a preset square formula includes: square amplification is carried out on the electrocardiosignal through a preset square formula, and a square amplification signal corresponding to the electrocardiosignal is obtained; and determining a first Q wave start point set and a first S wave end point set in the electrocardiosignal from the square amplification signal based on the R wave locus.

Wherein the square formula may be: ECGsq (k) =ecg (k) ² 。

Wherein the search conditions may be set to be ECG _sq (k) And not more than xA, wherein A is the amplitude in the square amplified signal, and x is the amplitude coefficient. Specifically, a refers to an R-wave amplitude value corresponding to an R-wave position point, and x may be 1%, where the search condition is: the first m points with magnitudes less than 1% are found according to the specified search direction. As shown in fig. 8A, the first Q-wave start point set [ qpos_1, ], qpos_m satisfying the search condition, is counted from the detection of the R-wave points on the left and right sides]With the first S-wave termination point set [ jpos_1.,. The.]. Where m is the number of points, and may be, for example, m=10.

In this embodiment, after determining the first Q-wave start point set and the first S-wave end point set, it may further be determined whether the number of Q-wave start points in the first Q-wave start point set and the number of J-points in the first S-wave end point set meet a preset threshold, and if not, the magnitude of the amplitude coefficient x in the Q-wave start point and the J-point search condition is adjusted. For example, the preset threshold may be 10, and if m.gtoreq.10 is true, the value of x is dynamically adjusted, e.g., the adjusted search condition may be ECG _sq (k) And (2) A is less than or equal to (0.1+x). After the Q-wave start point and the J-point search condition are adjusted, the first Q-wave start point set and the first S-wave end point set may be adjusted synchronously, or only one of them may be adjusted. For example, when x=0.01, if the first Q-wave start point set has met the preset threshold, but the first S-wave end point set has not met the preset threshold, the ECG may be followed _sq (k) Searching under the searching condition of less than or equal to (0.1+0.01) A, and simultaneously adjusting a first Q wave starting point set and a first S wave ending point set to ensure that the number of Q wave starting points in the first Q wave starting point set and the number of J points in the first S wave ending point set meet preset thresholds; the first set of Q wave starting points meeting the preset threshold can also be reserved and stored according to the ECG _sq (k)≤And (0.1+x) A, and only adjusting the first S-wave termination point set so that the number of J points in the first S-wave termination point set meets a preset threshold.

In this embodiment, the amplitude characteristic of the electrocardiographic signal can be highlighted through square amplification, and by presetting search conditions and dynamically adjusting the search conditions, it can be ensured that enough first Q wave starting points and first S wave ending points are obtained, so that the accuracy of the ISO point and ST point positions is improved.

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

The slope characteristic of the electrocardiosignal can be embodied through differential processing, and the second Q wave starting point set and the second S wave ending point set are determined based on differential signals with obvious slope characteristics.

In a specific embodiment, the determining, based on the R-wave locus of the electrocardiograph signal and a preset differential formula, a second Q-wave start point set and a second S-wave end point set in the electrocardiograph signal includes: performing signal processing on the electrocardiosignals through a preset differential formula to obtain differential signals corresponding to the electrocardiosignals; and determining a first Q wave start point set and a first S wave end point set in the electrocardiosignal from the differential signal based on the R wave locus.

Wherein, the differential formula may be:

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

wherein, search conditions may be set as follows: ECG _diff (k)∈[-t，t]The smaller the ordinate of the differential signal, the smaller the corresponding electrocardiosignal slope, and the flatter the corresponding signal characteristic point is. Specifically, the initial condition may be t=1, and the search condition is that n differential signal values are [ -1,1]Is a point of (2). As shown in fig. 8B, detected from the R-wave locus to the left and right, the second Q-wave start point set [ qposz_1, ] satisfying the search condition is counted]And a second S-wave end point set [JposZ_1，......，JposZ_n2]. Where n1 and n2 are the number of points, and may be, for example, n1=10, n2=10.

In this embodiment, after determining the second Q-wave start point set and the second S-wave end point set, it may further be determined whether the number of Q-wave start points in the second Q-wave start point set and the number of J-points in the second S-wave end point set meet a preset threshold, and if not, the size of t in the search conditions of the Q-wave start points and the J-points is adjusted. For example, the preset threshold may be 10, it is determined whether n1 is greater than or equal to 10, and if n1 is greater than or equal to 10, the value of t is dynamically adjusted if n1 is greater than or equal to 10, for example, t= (1+15%) t may be set, and the adjusted search condition may be:

ECG _diff (k)∈[-(1+15％)t，(1+15％)t]。

after the Q-wave start point and the J-wave search condition are adjusted, the second Q-wave start point set and the second S-wave end point set may be adjusted synchronously, or only one of them may be adjusted. For example, when t=1, if the second Q-wave start point set has met the preset threshold, but the second S-wave end point set has not met the preset threshold, the ECG may be followed _diff (k)∈[-(1+15％)t，(1+15％)t]Searching for the searching conditions of the second Q wave starting point set and the second S wave ending point set, and adjusting the second Q wave starting point set and the second S wave ending point set so that the number of Q wave starting points in the second Q wave starting point set and the number of J points in the second S wave ending point set both meet a preset threshold; the second set of Q-wave starting points meeting the preset threshold can also be reserved and stored according to the ECG _diff (k)∈[-(1+15％)t，(1+15％)t]And (3) searching the searching conditions of the second S wave ending point set, and adjusting the second S wave ending point set only to enable the number of J points in the second S wave ending point set to meet a preset threshold.

In this embodiment, the slope characteristic of the electrocardiograph signal can be effectively highlighted through differential processing, and by presetting search conditions and dynamically adjusting the search conditions, it can be ensured that enough second Q-wave start points and second S-wave end points are obtained, so that the accuracy of ISO point and ST point positions is improved.

Step 705, determining the isoelectric point position of the electrocardiograph signal according to the first Q-wave start point set and the second Q-wave start point set.

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

In a specific embodiment, after the first Q-wave start point set and the second Q-wave start point set are determined, the rationality of the Q-wave start point needs to be judged, the point with the larger error is removed, the influence of noise is reduced, and the accuracy of the Q-wave start point is improved, so that the accuracy of the ST offset value is improved.

In the present embodiment, the rationality of the Q-wave origin can be judged by the following condition:

first set of Q-wave start points:

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

T1＝a|Qpos_m-Qpos_1|

the first Q wave starting point effective interval is: [ mean_Qpos-T1, mean_Qpos+T1]

Wherein 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 region between the first Q wave starting point and the mth Q wave starting point in the first Q wave starting point set. In practical application, a may be adjusted according to practical requirements, for example, a=0.4.

Second set of Q-wave start points:

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

T3＝c|QposZ_n1-QposZ_1|；

the second Q-wave start effective interval is: [ mean_QposZ-T3, mean_QposZ+T3]

Wherein mean_qposz is the average value of n 1Q wave start points in the second Q wave start point set, and T3 is c times the length of the region between the first Q wave start point and the n1 st Q wave start point in the second Q wave start point set. In practical application, a may be adjusted according to practical requirements, for example, c=0.45.

In this embodiment, after the rationality judgment of Q is finished, Q-wave start points in the first Q-wave start point valid section and the second Q-wave start point valid section can be respectively screened to obtain a screened first Q-wave start point and a screened second Q-wave start point. Wherein, the Q-wave start points in the first Q-wave start point effective section and the second Q-wave start point effective section can be filtered by using min|QPos_i1-QPosZ_j1|. Wherein qpos_i1 is any Q-wave start point of the first Q-wave start point valid section, and qposz_j1 is any Q-wave start point of the second Q-wave start point valid section. Specifically, two Q-wave starting points with the smallest difference value are selected as a first Q-wave starting point after screening and a second Q-wave starting point after screening. And then determining a point closest to the R wave from the first Q wave starting point after screening and the second Q wave starting point after screening as a target Q wave starting point according to the principle of the close proximity R wave.

In this embodiment, after determining the target Q-wave start point, the isoelectric point position can be determined according to the heart rate. Specifically, the isoelectric point location, that is, the ISO point, is determined according to the following formula.

ISO_pos＝Q_POS-t ₁

Moving the target Q-wave origin to the left by t according to the above formula ₁ Millisecond, where t ₁ Is determined by the heart rate. If the heart rate is greater than 120, t ₁ Sampling points corresponding to 20 milliseconds are taken; if the heart rate is not greater than 120, t ₁ Sampling points corresponding to 30 milliseconds are taken.

In this embodiment, the average value in the first Q-wave start point set is obtained, and the length of the region between the first Q-wave start point and the mth Q-wave start point is reduced; and by obtaining the average value in the second Q wave starting point set and reducing the area length between the first Q wave starting point and the n1 th Q wave starting point. The method can effectively judge the rationality of the Q wave starting point, eliminates the point with larger error, reduces the influence of noise, and improves the accuracy of the ST offset value. Noise can be further removed through cyclic screening and the principle of the adjacent R wave, and accuracy of the starting point of the Q wave is improved, so that accuracy of the ST offset value is further improved.

Step 706, determining the ST point position of the electrocardiosignal according to the first S-wave end point set and the second S-wave end point set.

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

In a specific embodiment, after the first S-wave termination point set and the second S-wave termination point set are determined, the rationality of the J points needs to be judged, the points with larger errors are removed, the influence of noise is reduced, and the accuracy of the J points is improved, so that the accuracy of the ST offset value is improved.

In the present embodiment, the rationality of the J point can be judged by the following condition:

first set of S-wave termination points:

Mean_Jpos＝mean([Jpos_1,…,Jpos_m])

T2＝b|Jpos_m-Jpos_1|；

the first J point effective interval is: [ mean_Jpos-T2, mean_Jpos+T2];

wherein mean_jpos is the average value of m J points in the first S-wave start point set, and T2 is b times the length of the region between the first J point and the mth J point in the first J-wave start point set. In practical application, b may be adjusted according to practical requirements, for example, b=0.45.

Second set of S-wave termination points:

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

T4＝d|JposZ_n2-JposZ_1|

the second J point effective interval is: [ mean_JposZ-T4, mean_JposZ+T4]

Wherein mean_jpos is the average value of n 2J points in the second S-wave start point set, and T4 is d times the length of the region between the first J point and the n 2J point in the second Q-wave start point set. In practical application, d may be adjusted according to practical requirements, for example, d=0.45.

In this embodiment, after the rationality judgment of J is finished, J points in the first J point effective interval and the second J point effective interval can be screened respectively to obtain a screened first J point and a screened second J point. Wherein, the J points in the first J point effective interval and the second J point effective interval can be filtered by using min|Jpos_i1-JposZ_j1|. Wherein, jpos_i1 is any J point of the first J point effective section, and Jpos Z_j1 is any J point of the second J point effective section. Specifically, two J points with the smallest difference value are selected as a first J point after screening and a second J point after screening. And then determining a point closest to the R wave from the first J point after screening and the second J point after screening as a target J point according to the principle of the close proximity R wave.

In this embodiment, after determining the target J point, 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

Moving the target J point to the right by t according to the formula ₂ The number of sampling points corresponding to milliseconds, wherein t ₂ Is determined by the heart rate. If the heart rate is greater than 120, t ₂ Taking the number of sampling points corresponding to 60 milliseconds; if the heart rate is not greater than 120, t ₂ Taking the number of sampling points corresponding to 80 milliseconds.

In this embodiment, the average value in the first J-wave start point set is obtained, and the area length between the first J-point and the mth J-point is reduced; and the average value in the second J wave starting point set is obtained, and the length of the area between the first J point and the n 1J point is reduced. The method can effectively judge the rationality of the J point, eliminates the point with larger error, reduces the influence of noise and further improves the accuracy of the ST offset value. Noise can be further removed through cyclic screening and the principle of the adjacent R wave, and the accuracy of the J point is improved, so that the accuracy of the ST offset value is further improved.

And step 707, determining an ST offset value of the electrocardiosignal according to the isoelectric point position and the ST point position.

After determining the positions of the isoelectric point and the ST point, a difference between the isoelectric point position and the ordinate of the ST point position can be calculated in the original signal, and the difference is used as an ST offset value.

The application provides a ST offset value calculation method, which comprises the following steps: acquiring an electrocardiosignal, extracting an R wave locus of the electrocardiosignal, determining a first Q wave start point set and a first S wave end point set in the electrocardiosignal based on the R wave locus of the electrocardiosignal and a preset square formula, and determining a second Q wave start point set and a second S wave end point set in the electrocardiosignal based on the R wave locus of the electrocardiosignal and a preset differential formula; according to the scheme, the amplitude characteristics of the electrocardiosignal can be highlighted through square amplification, so that the signal quality is effectively improved, a Q wave starting point set and an S wave ending point set of the electrocardiosignal can be accurately determined, and the accuracy of ST offset value calculation is further improved; then determining the isoelectric point position of the electrocardiosignal through the first Q wave starting point set and the second Q wave starting point set, determining the ST point position of the electrocardiosignal through the first S wave ending point set and the second S wave ending point set, and determining the ST offset value of the electrocardiosignal according to the isoelectric point position and the ST point position; after square amplification and differential processing, the position of the isoelectric point and the position of the ST point can be accurately determined based on the high-precision Q wave starting point set and the high-precision S wave ending point set, the ST offset value can be accurately determined, the influence of drifting in electrocardiosignals can be avoided, the difficulty of judging the heart physiological state of a patient by medical staff is reduced, and the judgment accuracy of the medical staff is improved.

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

step 901, displaying an ST offset value display area, wherein the ST offset value display area comprises a concentric ring display diagram; the concentric circle display map includes a plurality of concentric circles for representing different cascade ST offset values.

Wherein the ST value display area includes a concentric ring display. As shown in fig. 10, the upper half part of the concentric ring display diagram is set to be sequentially provided with leads I, II, III and aVR, aVL, aVF from the center of a circle to the maximum radius, and the lower half part is set to be sequentially provided with leads V1, V2, V3, V4, V5 and V6 from the center of the circle to the maximum radius; and the positive direction is defined as clockwise direction, the negative direction is anticlockwise direction, the 0-0 line is defined as the boundary line of the ST offset value positive and negative, the boundary line and the positive boundary line are divided together to obtain four sector areas, and the positive and negative polarities of the areas are obtained by combining the defined positive direction as shown in fig. 10. In practical applications, explicit marking may be performed by "+", "-" of different colors.

In practical application, if 12 leads of the standard limb leads, the pressurized monopolar limb leads and V1-V6 can not meet the detection requirement in the conventional electrocardiographic examination. If right heart, right ventricular hypertrophy and myocardial infarction are suspected, and V7, V8, V9 and V3R leads are needed to be added, the concentric ring display diagram in the scheme can also increase the display of the V7, V8, V9 and V3R leads on the basis of displaying 12 leads.

Step 902, determining a ratio of the ST offset value to the preset display threshold according to the preset display threshold corresponding to the concentric ring display diagram; the preset display threshold is used for indicating the maximum value of ST offset values which can be displayed by the concentric ring display diagram.

Wherein a maximum value of ST offset values that can be displayed by one concentric ring display diagram is set, for example, a maximum range of ST offset values that can be represented by half concentric rings is set to [ -a, +a ]. Based on the above, the ST offset value expressed by each degree of central angle in the half concentric ring is 2*A/180. Therefore, if the ST offset value is calculated as B, the ST offset value B can be represented by an annular sector region having a central angle of 2×a×b/180 in the concentric ring. As shown in fig. 11, the larger the central angle, the larger the ST offset value (absolute value). As shown in fig. 11, the corresponding leads from top to bottom and the ST offset values at the leads 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, displaying a first annular sector area representing the ST offset value on a concentric ring corresponding to the ST offset value according to the ratio.

Wherein, the concentric circle corresponding to the ST offset value refers to the same lead corresponding to the ST offset value and the concentric circle. For example, the ST offset value of the V6 lead is to be represented on concentric circles identifying the V6 lead.

After calculating the ST offset value, the size of the circular sector for the ST offset value is determined according to the size of the ST offset value represented by the central angle of each degree, and the size is displayed on the concentric circles.

In the embodiment, different rings in the concentric ring display diagram are used for identifying different leads, so that ST offset values in the multi-lead electrocardiogram can be clearly displayed according to the types of the leads, and the ST offset values are more intuitively displayed.

In a specific embodiment, the displaying, according to the ratio, the annular sector area representing the ST offset value according to a preset display sequence after the concentric ring corresponding to the ST offset value further includes: acquiring a preset equipotential point preset by a user; determining an isoelectric point position offset value of the electrocardiosignal according to the isoelectric point position and the preset isoelectric point position; the equipotential point position offset value is used for indicating the difference between the equipotential point position and the preset equipotential point position; determining the ratio of the equipotential point position offset value to the preset display threshold according to the preset display threshold; and displaying a second annular sector area representing the equipotential point position offset value on a concentric ring corresponding to the ST offset value according to the ratio of the equipotential point position offset value to the preset display threshold value based on the first annular sector area.

The preset display threshold is further used for indicating that the concentric ring display diagram can display the maximum value of the equipotential point position offset value, and the indicated maximum value of the equipotential point position offset value is equal to the maximum value of the ST offset value.

When real-time ST analysis is performed, the annular sector area can reflect the relative relation among the ST offset value, the magnitude, the positive and negative of the difference value between the current heart beat equipotential point position and the preset equipotential point position. As shown in fig. 12, 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), respectively from top to bottom. Taking aVF lead as an example, in the nth heart beat, the calculated value of ST offset is 0.8, and comparing the ordinate value at the ST point with the manually set ordinate value at the equipotential point, the difference (the equipotential point offset value) between the ordinate value at the equipotential point and the manually set ordinate value at the equipotential point is-0.2, so that the real-time ST offset in the current heart beat is obtained: 0.8+ (-0.2) =0.6 mV. In this embodiment, it is ensured that the end edge of the isoelectric point position offset value always falls on the boundary of the region corresponding to the real-time ST offset value, and the variation of the isoelectric point position offset value is more obvious, and the start edge of the isoelectric 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 the phenomenon that when the ST offset value, the difference between the current heart beat baseline and the artificially set isoelectric point position (isoelectric point position offset value) is small, the annular sector area is too small, and specific values are difficult to identify (arrange), the ST offset value and the specific values of the isoelectric point position offset value are difficult to distinguish in the graph; meanwhile, from the standpoint of reducing the complexity of the graph and improving the clarity of numerical display, the scheme provided by the application can set a detailed numerical control legend beside the concentric ring display graph, and the legends correspond to the dividing areas of the leads on the 0-0 axis one by one, so that the specific numerical value of the current lead is intuitively and definitely marked; in different modes, the corresponding indication area can be lightened, so that the user can observe conveniently; in order to meet different observing demands of professionals on ST offset value indexes, an independent classification table is further arranged at the lowest part, ST offset values are intuitively displayed through the table, and data comparison is facilitated for users.

In one embodiment, the present application proposes an ST offset value calculation apparatus as shown in fig. 14, the apparatus comprising:

an electrocardiosignal acquisition module 1401 is used for acquiring an electrocardiosignal, wherein the electrocardiosignal comprises an ST segment positioned between a QRS complex and a T wave.

The R-wave position extraction module 1402 is configured to extract an R-wave position of the electrocardiograph signal.

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

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

An equipotential point determining module 1405, configured to determine an equipotential point position of the electrocardiograph signal according to the first Q-wave start point set and the second Q-wave start point set.

And an ST point determining module 1406 configured to determine an ST point position of the electrocardiograph signal according to the first S-wave end point set and the second S-wave end point set.

And an ST offset value determining module 1407, configured to determine an ST offset value of the electrocardiographic signal according to the isoelectric point position and the ST point position.

As shown in fig. 15, in one embodiment, is an internal structural diagram of a computer device. The computer apparatus may be an ST offset value calculation device, or a terminal or server connected to an ST offset value calculation device. As shown in fig. 15, the computer device includes a processor, a memory, and a network interface connected by a system bus. The memory includes a nonvolatile storage medium and an internal memory. The non-volatile storage medium of the computer device stores an operating system, and may also store a computer program that, when executed by a processor, causes the processor to implement a ST offset value calculation method. The internal memory may also store a computer program which, when executed by the processor, causes the processor to perform a method of calculating an ST offset value. The network interface is used for communicating with the external connection. It will be appreciated by those skilled in the art that the structure shown in fig. 15 is merely a block diagram of a portion of the structure associated with the present inventive arrangements and is not limiting of the computer device to which the present inventive arrangements are applied, and that a particular computer device may include more or fewer components than shown, or may combine certain components, or have a different arrangement of components.

In one embodiment, a method for calculating an ST offset value according to the present application may be implemented in the form of a computer program that can be executed on a computer device as shown in fig. 15. The memory of the computer apparatus may store therein respective program templates constituting the ST offset value calculating means. For example, an electrocardiograph signal acquisition module 1401, an r-wave position point extraction module 1402, a first point set determination module 1403, a second point set determination module 1404, an equipotential point determination module 1405, an st point determination module 1406, and an st offset value determination module 1407.

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: acquiring an electrocardiosignal comprising an ST segment located between a QRS complex and a T wave; extracting an R wave locus of the electrocardiosignal; determining a first Q wave start point set and a first S wave end point set in the electrocardiosignal based on an R wave locus of the electrocardiosignal and a preset square formula; determining a second Q wave start point set and a second S wave end point set in the electrocardiosignal based on an R wave locus of the electrocardiosignal and a preset differential formula; determining the isoelectric point position of the electrocardiosignal according to the first Q wave starting point set and the second Q wave starting point set; determining the ST point position of the electrocardiosignal according to the first S wave end point set and the second S wave end point set; and determining an ST offset value of the electrocardiosignal according to the isoelectric point position and the ST point position.

In one embodiment, the determining the first Q-wave start point set and the first S-wave end point set in the electrocardiograph signal based on the R-wave position point of the electrocardiograph signal and a preset square formula includes: square amplification is carried out on the electrocardiosignal through a preset square formula, and a square amplification signal corresponding to the electrocardiosignal is obtained; and determining a first Q wave start point set and a first S wave end point set in the electrocardiosignal from the square amplification signal based on the R wave locus.

In one embodiment, before the extracting the R-wave site of the electrocardiograph signal, the method includes: determining a signal-to-noise ratio of the electrocardiosignal; if the signal-to-noise ratio is smaller than the signal-to-noise ratio threshold, re-executing the step of acquiring the electrocardiosignal; and if the signal-to-noise ratio is not smaller than the signal-to-noise ratio threshold, executing the step of extracting the R wave locus of the electrocardiosignal.

In one embodiment, the ST offset value calculation method is applied to a ST offset value calculation circuit, and the circuit comprises a notch filter module and a band-pass filter module; before the extracting of the R-wave locus of the electrocardiosignal, the method further comprises: the notch filter module is used for carrying out filter processing on the electrocardiosignals to obtain first filter signals; and filtering the first filtering signal through the band-pass filtering module to obtain a filtered electrocardiosignal.

In one embodiment, after determining the ST offset value of the electrocardiograph signal according to the isoelectric point position and the ST point position, the method further includes: displaying an ST value display area including concentric circle display diagrams; the concentric ring display diagram comprises a plurality of concentric rings for representing ST offset values of different cascades; determining the ratio of the ST offset value to the preset display threshold according to the preset display threshold corresponding to the concentric ring display diagram; the preset display threshold is used for indicating the maximum value of ST offset values which can be displayed by the concentric ring display diagram; and displaying a first annular sector area representing the ST offset value on a concentric ring corresponding to the ST offset value according to the ratio.

In one embodiment, the displaying, according to the ratio, the annular sector area representing the ST offset value in a concentric ring corresponding to the ST offset value according to a preset display order further includes: acquiring a preset equipotential point preset by a user; determining an isoelectric point position offset value of the electrocardiosignal according to the isoelectric point position and the preset isoelectric point position; the equipotential point position offset value is used for indicating the difference between the equipotential point position and the preset equipotential point position; determining the ratio of the equipotential point position offset value to the preset display threshold according to the preset display threshold; and displaying a second annular sector area representing the equipotential point position offset value on a concentric ring corresponding to the ST offset value according to the ratio of the equipotential point position offset value to the preset display threshold value based on the first annular sector area.

A computer readable storage medium storing a computer program which, when executed by a processor, causes the processor to perform the steps of: acquiring an electrocardiosignal comprising an ST segment located between a QRS complex and a T wave; extracting an R wave locus of the electrocardiosignal; determining a first Q wave start point set and a first S wave end point set in the electrocardiosignal based on an R wave locus of the electrocardiosignal and a preset square formula; determining a second Q wave start point set and a second S wave end point set in the electrocardiosignal based on an R wave locus of the electrocardiosignal and a preset differential formula; determining the isoelectric point position of the electrocardiosignal according to the first Q wave starting point set and the second Q wave starting point set; determining the ST point position of the electrocardiosignal according to the first S wave end point set and the second S wave end point set; and determining an ST offset value of the electrocardiosignal according to the isoelectric point position and the ST point position.

Those skilled in the art will appreciate that implementing all or part of the above-described methods in the embodiments may be accomplished by computer programs stored in a computer-readable storage medium, which when executed, may include the steps of the embodiments of the methods described above. The storage medium may be a magnetic disk, an optical disk, a Read-Only memory (ROM), a random-access memory (Random Access memory, RAM), or the like.

The foregoing disclosure is illustrative of the present application and is not to be construed as limiting the scope of the application, which is defined by the appended claims.

Claims

1. A method for calculating an ST offset value, the method comprising:

extracting an R wave locus of the electrocardiosignal;

2. The method of claim 1, wherein determining a first set of Q-wave start points and a first set of S-wave end points in the electrocardiograph signal based on the R-wave locus of the electrocardiograph signal and a preset squaring formula comprises:

Square amplification is carried out on the electrocardiosignal through a preset square formula, and a square amplification signal corresponding to the electrocardiosignal is obtained;

and determining a first Q wave start point set and a first S wave end point set in the electrocardiosignal from the square amplification signal based on the R wave locus.

3. The method of claim 1, wherein determining a second set of Q-wave start points and a second set of S-wave end points in the electrocardiograph signal based on the R-wave locus of the electrocardiograph signal and a preset differential formula comprises:

performing signal processing on the electrocardiosignals through a preset differential formula to obtain differential signals corresponding to the electrocardiosignals;

and determining a second Q wave start point set and a second S wave end point set in the electrocardiosignal from the differential signal based on the R wave locus.

4. The method of claim 1, wherein the extracting the R-wave sites of the electrocardiographic signal is preceded by:

determining a signal-to-noise ratio of the electrocardiosignal;

if the signal-to-noise ratio is smaller than the signal-to-noise ratio threshold, re-executing the step of acquiring the electrocardiosignal;

and if the signal-to-noise ratio is not smaller than the signal-to-noise ratio threshold, executing the step of extracting the R wave locus of the electrocardiosignal.

5. The method according to claim 1, wherein the ST offset value calculation method is applied to a ST offset value calculation circuit including a notch filter module and a band pass filter module;

before the extracting of the R-wave locus of the electrocardiosignal, the method further comprises:

the notch filter module is used for carrying out filter processing on the electrocardiosignals to obtain first filter signals;

and filtering the first filtering signal through the band-pass filtering module to obtain a filtered electrocardiosignal.

6. The method of claim 1, wherein after determining the ST offset value of the electrocardiograph signal from the isoelectric point location and the ST point location, further comprising:

displaying an ST offset value display area including a concentric ring display; the concentric ring display diagram comprises a plurality of concentric rings for representing ST offset values of different cascades;

determining the ratio of the ST offset value to the preset display threshold according to the preset display threshold corresponding to the concentric ring display diagram; the preset display threshold is used for indicating the maximum value of ST offset values which can be displayed by the concentric ring display diagram;

And displaying a first annular sector area representing the ST offset value on a concentric ring corresponding to the ST offset value according to the ratio.

7. The method of claim 6, wherein the displaying the circular sector area representing the ST offset value in a concentric circle corresponding to the ST offset value according to the ratio in a preset display order further comprises:

acquiring a preset equipotential point preset by a user;

determining an isoelectric point position offset value of the electrocardiosignal according to the isoelectric point position and the preset isoelectric point position; the equipotential point position offset value is used for indicating the difference between the equipotential point position and the preset equipotential point position;

determining the ratio of the equipotential point position offset value to the preset display threshold according to the preset display threshold;

and displaying a second annular sector area representing the equipotential point position offset value on a concentric ring corresponding to the ST offset value according to the ratio of the equipotential point position offset value to the preset display threshold value based on the first annular sector area.

8. An ST offset value calculation apparatus, characterized in that the apparatus comprises:

9. A computer device comprising a memory and a processor, the memory storing a computer program that, when executed by the processor, causes the processor to perform the steps of the method of 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.