Simulated correction method, device, medium and product for dynamic electrocardiogram electrode misplacement

Abstract

The application provides a dynamic electrocardiogram electrode misplacement simulation correction method, device, medium and product, which is used for simulation correction in the case of F and N electrode misplacement, relates to the technical field of medical treatment, and comprises the following steps: acquiring dynamic electrocardiogram original data in the case of F and N electrode misplacement; receiving a personalized coefficient of a patient, and performing individualized triangular modeling according to the personalized coefficient; calculating a potential baseline deviation and a distance between F and N electrodes, and inversely calculating a real F and N electrode potential voltage array point by point; based on the Eshbach triangular potential balance rule, correcting the error voltage array point by point to obtain a corrected limb lead voltage array; and verifying the corrected limb lead voltage array through a predetermined core clinical feature of the dynamic electrocardiogram. By using the technical scheme, the accurate correction of error electrocardiogram lead voltage and waveform can be automatically realized in the case of F and N electrode misplacement, and the clinical detection efficiency is improved.

Description

Technical Field

[0001] This invention relates to the field of medical technology, and in particular to a method, device, medium, and product for simulating and correcting incorrect electrode placement in dynamic electrocardiography. Background Technology

[0002] Ambulatory electrocardiography (AECG), also known as Holter monitoring, is a technique for continuously recording cardiac electrical activity for 24 hours or longer. It can capture transient abnormal cardiac electrical changes that are difficult to detect with conventional electrocardiograms. It has irreplaceable clinical value in the diagnosis, treatment evaluation, and prognosis of conditions such as palpitations, syncope, myocardial ischemia, and arrhythmias, and is widely used in outpatient settings, elderly patients, and other scenarios requiring long-term cardiac monitoring. The accuracy of ambulatory electrocardiography is highly dependent on the correct application of the surface electrodes. The limb electrodes include RA (right upper limb), LA (left upper limb), F (left lower limb), and N (right lower limb ground electrode). The placement and functional accuracy of these electrodes directly determine the accuracy of the lead waveforms. Unlike resting electrocardiograms (ECGs), Holter monitoring is designed to accommodate patients' daily activities. Instead of placing the F and N electrodes on the distal end of the lower limbs, the electrodes are placed on the proximal end of the abdomen. This placement characteristic means that both the F and N electrodes are within the influence range of the cardiac electrophysiological field and are non-zero body surface potential points. Furthermore, the functional difference between the two (F is the effective probing electrode, and N is the grounded reference electrode) has a much greater impact on the lead potentials than in resting ECGs.

[0003] In clinical practice, incorrect electrode placement is a common human error in Holter monitoring. When the F and N electrodes are placed incorrectly, incorrect raw ECG data will be obtained directly. In this incorrect raw data, the lead data are all a continuous voltage array, which corresponds to the ECG signal sampling point sequence, rather than a single fixed voltage value. This error will cause distortion of the potential difference, polarity, amplitude, and electrical axis of the limb leads in all dimensions, breaking the potential balance law of Einthoven's triangle (Ⅰ+Ⅲ=Ⅱ), making the waveform completely unable to match the normal ECG characteristics and unable to be directly used for clinical diagnosis.

[0004] Currently, existing Holter monitoring analysis software cannot effectively solve the problem of incorrect F and N electrode connection in Holter monitoring. Existing solutions, after obtaining erroneous raw data, can only require patients to wear the Holter monitor again for a second test. This not only increases patient discomfort and inconvenience, but is also unsuitable for elderly or critically ill patients who cannot undergo repeated testing. Furthermore, it reduces clinical testing efficiency, increases medical costs, and may delay diagnosis due to the second test. Summary of the Invention

[0005] Embodiments of the present invention provide a method, device, medium, and product for simulating and correcting incorrect placement of dynamic electrocardiogram electrodes, so as to automatically and accurately correct the voltage and waveform of incorrect electrocardiogram leads when the F and N electrodes are reversed.

[0006] To achieve the above objectives, on the one hand, a method for simulating and correcting incorrect electrode placement in dynamic electrocardiograms is provided, for simulating and correcting the situation where the F and N electrodes are reversed, including: The method acquires raw dynamic electrocardiogram data when the F and N electrodes are reversed. The raw data includes: erroneous voltage arrays of limb leads and voltage arrays of chest leads; in one specific implementation, the raw data also includes waveform features. The system receives the patient's personalized coefficients and performs individualized triangulation modeling based on these coefficients. The personalized coefficients include: gender, age, height, weight, and waist circumference. The individualized triangulation modeling includes: establishing a two-dimensional coordinate system on the body surface, recording electrode spatial coordinates, constructing a double-triangular structure, and calculating the angular offset of the lead vectors. The double-triangle structure includes: a misaligned triangle with the correct positions of the RA and LA electrodes as the upper vertex and the position of the incorrectly attached F electrode as the lower vertex, and a normal triangle with the correct position of the F electrode as the lower vertex; the normal triangle is used as a modeling reference. Based on the modeling results, the potential baseline deviation was calculated. array and spacing between F and N electrodes And according to the potential baseline deviation Arrays and Spacing The actual potential and voltage arrays of the F and N electrodes are obtained by point-by-point inversion; wherein, the potential baseline deviation The array = the pseudo center terminal potential array when the F and N electrodes are reversed minus the normal center terminal potential array when the F and N electrodes are not reversed; Based on Einstein's triangular potential balance law, the aforementioned angular offset is used. and the potential baseline deviation The erroneous voltage array of limb leads is corrected point by point to obtain the corrected limb lead voltage array, and the electrical axis is corrected to the predetermined normal range. The modified limb lead voltage array is validated using predetermined core clinical features of dynamic electrocardiogram, and the modified limb lead voltage array and waveform are output after successful validation.

[0007] Preferably, the simulation correction method for incorrect placement of dynamic electrocardiogram electrodes, in establishing a two-dimensional coordinate system on the body surface, includes: A two-dimensional coordinate system is established on the body surface with the midpoint of the sternum as the origin O, the X-axis pointing horizontally to the right, and the Y-axis pointing vertically upward. The scaling ratio of the Y-axis is adjusted based on the height, and the reference width of the abdominal region on the X-axis is adjusted based on the waist circumference.

[0008] Preferably, in the simulation correction method for incorrect placement of dynamic electrocardiogram electrodes, wherein, Recording electrode spatial coordinates according to the aforementioned two-dimensional coordinate system of the body surface includes: Record the coordinates of the RA electrode (X1), the LA electrode (X2), the incorrectly placed F electrode (X3), the incorrectly placed N electrode (X4), and the correct F electrode position. The coordinates; The angular offset of the lead vector is calculated using the following formula. : ; in, The origin of the central electrical terminal is at the same position as the origin of the coordinate system O. The pseudo-center point origin when the F and N electrodes are reversed; spacing The distance between position X3 and position X4; The true F electrode potential and voltage array is obtained by point-by-point inversion using the following formula. : Where i = 1, 2, ..., n; n is the number of sampling points; in, This is the actual N-electrode potential and voltage array, which retains the original array unchanged; The abdominal potential attenuation coefficient is adjusted based on the stated weight, waist circumference, gender, and age, according to a predetermined correction rule.

[0009] Preferably, the simulation correction method for incorrect electrode placement in dynamic electrocardiograms includes point-by-point correction of the erroneous voltage array in the limb leads, comprising: Use the following formula to correct for unipolar limb leads: ; in, This is the angle correction factor. Corresponding to aVR, aVL, and aVF; among them, for aVR, =0.01mV / °; for aVL, =0.012mV / °; for aVF, =0.015mV / °; Use the following formula to correct for bipolar limb leads: ; ; ; The electrical axis is corrected using the following formula: ; in, The corrected electrical axis direction corresponds to degrees. Represents the corresponding voltage array The mean.

[0010] Preferably, the simulation correction method for incorrect electrode placement in dynamic electrocardiogram (ECG) verifies the corrected limb lead voltage array using the core clinical features of dynamic ECG, including: The potential balance verification deviation value is calculated using the following formula: ; When the deviation value is less than a predetermined deviation threshold, potential balance is determined; and, When the corrected electric axis is normal, When the main wave of the VF lead voltage array is upward and the mean value of the baseline drift array is less than a predetermined voltage threshold and is consistent with the chest lead voltage array, the verification is confirmed to be successful; wherein, the predetermined voltage threshold is less than or equal to 0.1mV.

[0011] Preferably, in the simulation correction method for incorrect placement of dynamic electrocardiogram electrodes, when the RA and LA electrodes are also connected in reverse, when constructing the double triangle structure, the mirror image of the RA and LA electrodes is first corrected by swapping their positions, and then the correct positions of the RA and LA electrodes after correction are used to construct the double triangle structure.

[0012] Preferably, in the simulated correction method for incorrect placement of dynamic electrocardiogram electrodes, the abdominal potential attenuation coefficient... The value should be set as follows: patients who meet the criteria of being thin and having thin body fat > patients who meet the criteria of being normal and having moderate body fat thickness > patients who meet the criteria of being obese and having thick abdominal fat.

[0013] On the other hand, an electronic device is provided, including a memory and a processor, the memory storing at least one program, the at least one program being executed by the processor to implement the steps of the simulation correction method for misplaced dynamic electrocardiogram electrodes as described in any of the above.

[0014] In another aspect, a computer-readable storage medium is also provided, wherein at least one program is stored therein, the at least one program being executed by a processor to implement the steps of the simulation correction method for misplaced dynamic electrocardiogram electrodes as described in any of the above descriptions.

[0015] In another aspect, a computer program product is also provided, including a computer program that, when executed by a processor, implements the steps of the simulation correction method for misplaced dynamic electrocardiogram electrodes as described above.

[0016] The above technical solution has the following technical effects: The technical solution of this invention addresses erroneous raw ECG data acquired when the F and N electrodes are reversed. By inputting individualized coefficients such as gender, age, height, weight, and waist circumference, and combining Einstein's triangle reconstruction, surface electrode angle offset modeling, and individualized potential inversion, it can achieve accurate simulation correction of erroneous lead waveforms without the need for secondary device wearing. This overcomes the shortcomings of existing technologies, where erroneous raw data acquired after incorrect F / N electrode placement in dynamic ECG cannot be corrected by software algorithms, requiring re-detection, and is not adapted to the characteristics of lead voltage arrays. This improves clinical testing efficiency, reduces medical costs, and ensures the accuracy of the corrected waveform through verification of core clinical features, meeting clinical diagnostic needs.

[0017] In a further embodiment, the present invention adjusts the scaling ratio of the Y-axis based on the height of different individuals and adjusts the reference width of the abdominal region on the X-axis based on the waist circumference, thereby realizing the construction of a personalized two-dimensional coordinate system on the body surface. Based on different individuals' gender, age, weight, etc., different values ​​of abdominal potential attenuation coefficient are adopted. The significant differences in the personalized coefficients of different individuals are taken into account, which will lead to different abdominal fat thickness, relative spatial position of the heart and electrodes, and body surface potential distribution, thereby further improving the adaptability and correction accuracy of the correction model. Attached Figure Description

[0018] Figure 1 This is a flowchart illustrating a method for simulating and correcting incorrect placement of dynamic electrocardiogram electrodes according to an embodiment of the present invention. Figure 2 A schematic diagram showing the normal connection of the RA electrode, LA electrode, F electrode, and N electrode; Figure 3 This diagram shows a lead misconnection where the RA and LA electrodes are connected correctly, but the F and N electrodes are incorrectly connected. Figure 4 This is a schematic diagram of lead misconnection where the RA and LA electrodes are mirror-misconnected, and the F and N electrodes are mirror-misconnected. Figure 5 This is a schematic diagram of the process of collecting erroneous raw data and entering personalized coefficients in one embodiment of the present invention; Figure 6 This is a schematic diagram of the process of personalized triangular modeling and potential inversion in one embodiment of the present invention; Figure 7 This is a schematic diagram of the lead correction, verification and termination process in one embodiment of the present invention. Detailed Implementation

[0019] To further illustrate the various embodiments, the present invention provides accompanying drawings. These drawings are part of the disclosure of the present invention, primarily used to illustrate the embodiments and to explain the operating principles of the embodiments in conjunction with the relevant descriptions in the specification. With reference to these drawings, those skilled in the art should be able to understand other possible implementations and the advantages of the present invention. Components in the drawings are not drawn to scale, and similar component symbols are generally used to represent similar components.

[0020] The present invention will now be further described in conjunction with the accompanying drawings and specific embodiments.

[0021] Example 1: The simulation correction method for incorrect F / N electrode placement in dynamic electrocardiograms according to this invention addresses the practical application scenario where the F and N electrodes are reversed and incorrect dynamic electrocardiogram raw data has been acquired. In the incorrect raw data, the data of limb leads I, II, III, aVR, aVL, aVF, and chest leads V1 to V6 are all a continuous voltage array. This voltage array corresponds to the ECG signal sampling point sequence, and the array length matches the sampling frequency and monitoring duration. Based on the spatial expansion of Einthoven's triangle and the vector projection principle of body surface potential, combined with the non-equipotential characteristics of the F and N electrodes of the dynamic electrocardiogram placed near the proximal end of the abdomen, the method achieves the simulation correction of the waveform of the incorrect leads through the steps of "incorrect raw data acquisition → individualized coefficient input → individualized triangular modeling → potential inversion → angle offset correction → potential balance verification". The core concept focuses on "individualized coefficient-driven precise correction + adaptation to voltage array characteristics".

[0022] Figure 1 This is a schematic flowchart illustrating a simulation correction method for incorrect electrode placement in dynamic electrocardiography according to an embodiment of the present invention. This simulation correction method is used to perform simulated correction when the F and N electrodes are reversed.

[0023] like Figure 1 The simulation correction method for incorrect placement of dynamic electrocardiogram electrodes in this embodiment includes: The raw data of the dynamic electrocardiogram were acquired when the F and N electrodes were reversed. The raw data included: the error voltage array of the limb leads and the voltage array of the chest leads; in one specific implementation, the raw data also included waveform features. Figure 2This is a schematic diagram showing the normal connection of the RA electrode, LA electrode, F electrode, and N electrode; where O WCT This is the position of the center electrical terminal during normal connection, which is the same position as the origin O of the coordinate system. Figure 3 This diagram illustrates a lead misconnection where the RA and LA electrodes are connected correctly, but the F and N electrodes are incorrectly connected (i.e., reversed). Figure 4 This is a schematic diagram of lead misconnection where the RA and LA electrodes are mirror-misconnected, and the F and N electrodes are mirror-misconnected. This is the location of the pseudo-center terminal in the case of lead misconnection. This location is different from O. WCT The locations overlap, but the references for calculating the potentials are different. In practice, limb leads include: I, II, III, aVR, aVL, and aVF; the chest lead voltage array includes voltage arrays from V1 to V6; the chest lead voltage array serves as a verification reference for subsequent correction effects, eliminating the need for re-collecting ECG data, thus aligning with practical clinical applications; all voltage arrays are continuous sampling sequences, denoted as... n is the number of sampling points, which is positively correlated with the duration of dynamic electrocardiogram monitoring and the sampling frequency; Figure 5 This is a schematic diagram illustrating the process of collecting erroneous raw data and entering personalized coefficients in one embodiment of the present invention.

[0024] The system receives the patient's individualized coefficients and performs individualized triangulation modeling based on these coefficients. The individualized coefficients include: gender, age, height, weight, and waist circumference. Individualized triangulation modeling includes: establishing a two-dimensional coordinate system on the body surface, recording electrode spatial coordinates, constructing a double-triangular structure, and calculating the angular offset of the lead vectors. The double-triangle structure includes: a misaligned triangle with the correct positions of the RA and LA electrodes as the upper vertices and the position of the incorrectly attached F electrode as the lower vertex; and a normal triangle with the correct position of the F electrode as the lower vertex. The normal triangle serves as the modeling reference. The normal triangle is as follows: Figure 2 In triangle OWCT X1X2X3'; the misjoined triangle is Figure 3 In the case of △OWCT' X1X2X3.

[0025] In one specific implementation, gender and age determine the basic decay pattern of the body surface potential; for example, the potential decay rate of female and elderly patients differs from that of male and young patients. Height determines the scaling ratio of the Y-axis of the electrode spatial coordinate system, waist circumference determines the scaling ratio of the abdominal region on the X-axis of the coordinate system and the distance between F and N electrodes. Weight determines the thickness of abdominal fat, which in turn corrects the potential decay coefficient, such as the abdominal potential decay coefficient. The RA and LA electrodes are attached below the clavicle and are in a fixed position, which can be confirmed by positioning on the body surface. Combined with the entered individualized coefficients, the scaling ratio of the two-dimensional coordinate system of the chest and abdomen is adjusted to quantify the differences in electrode spatial position among different individuals. In one specific implementation, the angular offset of the lead vector The overall offset characteristics of the voltage array are constants, with height and waist circumference directly affecting them. The calculation accuracy is improved, and gender and age are used to correct for deviations in angle calculations. Based on the modeling results, the potential baseline deviation was calculated. array and spacing between F and N electrodes And based on the potential baseline deviation Arrays and Spacing The actual potential and voltage arrays of the F and N electrodes are obtained by point-by-point inversion; among them, the potential baseline deviation is... Array = False center terminal potential array when F and N electrodes are reversed minus Normal center terminal potential array when F and N electrodes are not reversed; Potential baseline deviation The array is of the same length as the voltage array, corresponding to the baseline deviation of each sampling point; In one specific implementation, based on the surface potential vector projection formula and combined with the spatial correlation of abdominal surface potential, the inversion model of the true surface potential of F and N electrodes is optimized using the entered individualized coefficients as variables. This involves correcting the abdominal potential attenuation coefficient k by weight and waist circumference (e.g., the thicker the fat, the smaller the k value), correcting the potential inversion baseline coefficient by gender and age, correcting the influence of the relative distance between the heart and the electrode on the potential by height, and calculating the potential baseline deviation caused by the interchange of F and N electrodes. Potential baseline deviation It solves the problems of reference frame misalignment caused by the interchange of non-equipotential electrodes and inconsistent modeling of different individuals, while adapting to the continuous sampling characteristics of voltage arrays; Figure 6 This is a schematic diagram of the personalized triangular modeling and potential inversion process in one embodiment of the present invention.

[0026] Based on Einstein's trigonometric potential balance law, using angular offset and potential baseline deviation The erroneous voltage array of limb leads is corrected point by point to obtain the corrected limb lead voltage array, and the electrical axis is corrected to the predetermined normal range. In one specific implementation, the correction includes point-by-point correction of the erroneous voltage arrays of unipolar limb leads aVR, aVL, aVF and bipolar limb leads I, II, III; the correction accuracy is ensured by relying on individualized coefficients throughout the process, and the correction process is performed by point-by-point array calculation to ensure synchronization with the original sampling sequence; The modified limb lead voltage array is validated using predetermined core clinical features of dynamic electrocardiogram, and the modified limb lead voltage array and waveform are output after successful validation.

[0027] In one specific implementation, the predetermined core clinical features include one or more of the following: potential balance of the voltage array, electrical axis range, waveform polarity, baseline stability, and time consistency with the voltage array in the chest leads. If the validation fails, iterative adjustments are made in conjunction with individualized coefficients. , The system processes core parameters such as array and k until the waveform corresponding to the corrected voltage array meets the clinical diagnostic criteria, and then outputs the corrected normal ECG voltage array and its corresponding waveform.

[0028] Figure 7 This is a schematic diagram of the lead correction, verification and termination process in one embodiment of the present invention.

[0029] The following describes the formulas and variables used in the specific implementation of this invention. The lead data are all voltage arrays, corresponding to the ECG sampling point sequence; in one example, the sampling frequency is 500Hz, the monitoring duration is 10s, i.e., n=5000 sampling points; all potential calculations are performed point-by-point array operations.

[0030] 1. Angular deviation Calculation formula (adjusted for height, waist circumference, gender, and age) (This is a constant, and the overall offset of the adaptive voltage array is maintained). ; 2. Formula for calculating the center terminal potential (point-by-point array operation): (Normal, i=1,2,...,n); (Mistaken connection, i=1,2,...,n); 3. Potential baseline deviation Calculation formula (point-by-point array operation) (An array of the same length as the voltage array): (i=1,2,...,n); 4. Formula for calculating the distance d between F and N electrodes (combined with waist circumference correction, d is a constant and related to individual body shape): ; Where (x3, y3) are the x and y coordinates of the incorrectly attached F electrode at position X3, and (x4, y4) are the x and y coordinates of the incorrectly attached N electrode at position X4. 5. True F / N potential inversion formula (point-by-point array calculation, combined with weight, waist circumference, gender, and age to correct for the k value; the potential decay coefficient k is a constant): (i=1,2,...,n); in, This is a real array of F electrode potential and voltage; This is the actual N-electrode potential and voltage array, which retains the original array unchanged; 6. Correction formula for unipolar limb leads (point-by-point array calculation): ; This is the angle correction factor for aVR. =0.01mV / °; for aVL, =0.012mV / °; for aVF, =0.015mV / °, i=1,2,...,n; 7. Bipolar limb lead correction formula (point-by-point array calculation): ; ; Lead I does not require correction. , i=1,2,...,n; 8. Electric axis correction formula (calculated based on the average of the voltage array, adapted to the overall characteristics of the array): ; in, The corrected electrical axis direction corresponds to degrees. Represents the corresponding corrected voltage array The mean; 9. Formula for verifying the deviation value of potential balance (calculated based on the average value of the voltage array to verify the overall balance characteristics): ; When the deviation value is less than a predetermined deviation threshold, potential balance is determined; and, When the corrected electric axis is normal, When the main wave of the VF lead voltage array is upward and the mean value of the baseline drift array is less than a predetermined voltage threshold and is consistent with the chest lead voltage array, the verification is confirmed to be successful; wherein, the predetermined voltage threshold is less than or equal to 0.1mV; the deviation threshold is, for example, less than or equal to 10%.

[0031] Meaning of variables in the formula: 1. : The angle offset of the lead vector (constant), adapting to the overall offset characteristics of the voltage array, corresponding to Figure 2 The "normal triangle △OWCT X1X2X3'" and Figure 3 The angle between the lead vectors of the "misplaced triangle △OWCT' X1X2X3" is affected by height, waist circumference, gender, and age. 2. : Central electrical terminal origin, and Figure 2The “Origin of Coordinates O (Midpoint of the Sternum)” marked in the middle refers to the same location, which is the reference origin for Einstein trigonometric modeling and potential calculation; 3. : Spatial coordinates of electrode F under misconnection state, corresponding to Figure 3 , Figure 4 Coordinates of the F electrode in the misconnected area on the right; : Spatial coordinates of electrode F under normal application conditions, corresponding to Figure 2 The coordinates of the F electrode in the normal region on the left; 4. The pseudo-center terminal origin under misconnection conditions is calculated based on the misconnection triangle (RA-LA-N) and is different from the normal center terminal origin. The locations of the midpoints of the sternum coincide, only the base for calculating the potentials differs; 5. : The potential of the center terminal under normal conditions (voltage array, calculated point by point); The potential of the pseudo-center terminal under F / N misconnection conditions (voltage array, point-by-point calculation) is the difference between the two, which is the potential baseline deviation. ; 6. , , , : These are the body surface potentials (all voltage arrays) of electrodes RA, LA, F, and N, respectively. Figure 2 , Figure 3 , Figure 4 The potential values ​​of each electrode are collected, among which the potentials of F and N electrodes are affected by individualization factors (weight, waist circumference, etc.); 7. The spatial spacing (constant) between the F and N electrodes, combined with waist circumference correction, is illustrated in the diagram. Figure 1 , indication Figure 2 , indication Figure 3 The straight-line distance between the F electrode and the N electrode is calculated from their coordinates; 8. The abdominal potential decay coefficient (constant) is jointly corrected for by weight, waist circumference, gender, and age. The thicker the fat layer, the smaller the k-value. The k-value is a positive correlation model between body surface fat thickness and potential decay, based on the laws of bioelectrical conduction: thicker fat layer → slower electric field decay → smaller k; thinner fat layer → faster decay → larger k. Default values ​​are: 0.042 for underweight, 0.030 for normal, and 0.018 for obese, consistent with common sense about bioelectrical conduction, and individually corrected for by weight and waist circumference. In one specific implementation, the specific correction method for the k-value can be based on a pre-established correspondence between weight, waist circumference, gender, age, and the corrected k-value, and this correspondence is used to determine the k-value during the specific correction. 9. Angle correction coefficient (constant): A fixed constant corresponding to different unipolar limb leads, used to offset the differential effect of angle offset θ on the potential of each lead. Preferably: 0.01 mV / ° for aVR lead, 0.012 mV / ° for aVL lead, and 0.015 mV / ° for aVF lead. 10. The mean value of the voltage array of each lead after correction is used for electrical axis calculation and potential balance verification to ensure that the correction result conforms to Einstein's triangular potential balance law: I + III = II.

[0032] Example 3: This embodiment is a simulated correction procedure for a normal-sized adult male where the F and N electrodes are reversed, i.e., the F / N leads are incorrectly connected. This embodiment corresponds to... Figure 3 The F / N connection is incorrect. The dynamic electrocardiogram device has acquired incorrect raw electrocardiogram data after the F / N was incorrectly attached. The electrodes are incorrectly attached. In this case, RA and LA are correct, and F and N are interchanged. The raw electrocardiogram data are all voltage arrays.

[0033] The simulation correction method of this embodiment of the invention includes the following steps: Step 1: Error-prone raw data collection and individualized coefficient entry 1.1 Acquiring erroneous raw ECG data: Extracting erroneous voltage arrays and waveform characteristics from limb leads (I, II, III, aVR, aVL, aVF), and simultaneously extracting voltage arrays from chest leads (V1~V6) as a verification reference. Among the known erroneous data: the device mistakenly treated the voltage array of N as F, i.e. In this example, the array is shown below: Treat the voltage array of F as N, that is In this example, the array is shown below: The RA and LA voltage arrays are correct; in this example, the arrays are as follows: , Error axis -40°, baseline drift array mean <0.13mV; 1.2 Input individualization coefficients: gender (male), age (35 years old, young adult), height (175cm), weight (70kg), waist circumference (85cm). Based on these coefficients, determine the potential decay coefficient k=0.03mV / cm (for normal body type males with moderate fat thickness), the Y-axis reference length of the coordinate system is 80cm (suitable for a height of 175cm), and the X-axis abdominal region reference width is 42.5cm (suitable for a waist circumference of 85cm). No additional correction is needed for angle calculation (for young males with stable physiological characteristics).

[0034] Step 2: Individualized Triangulation Modeling 2.1 Establish a two-dimensional coordinate system on the body surface: Based on the entered height of 175cm, adjust the scaling ratio of the Y-axis, with a baseline length of 80cm. Based on the waist circumference of 85cm, adjust the baseline width of the abdominal area of ​​the X-axis to 42.5cm. Take the midpoint of the sternum (2cm above the xiphoid process) as the origin O, with the X-axis pointing horizontally to the right and the Y-axis pointing vertically upward. 2.2 Recording electrode spatial coordinates: The coordinates of the misconnected electrodes were confirmed by locating them on the body surface. RA (right infraclavicular fossa) X1 (2.5cm, 8.0cm), LA (left infraclavicular fossa) X2 (-2.5cm, 8.0cm), F (right lower abdomen) X3 (3.0cm, -5.0cm), and N (left lower abdomen) X4 (-3.0cm, -4.5cm). 2.3 Constructing a double triangle structure: With RA and LA as fixed upper vertices, construct the misaligned triangle △OWCT' X1X2X3, and simultaneously construct the normal triangle △OWCT X1X2X3'; where X3' is the normal application position of F, used as the modeling reference; 2.4 Calculate the angular offset Substituting into a unified formula and combining the adjusted coordinate data for height and waist circumference, the result is calculated. This is used for overall angular offset correction of the voltage array; since the patient's body type is normal, no additional correction based on gender and age is required. ; Step 3: Individualized potential inversion (point-by-point array operation) 3.1 Calculate the center terminal potential array: Substitute the values ​​into the unified formula above, and perform point-by-point calculations using the original erroneous voltage array to obtain the normal center terminal potential array. In this example, the array mean After incorrect connection, the pseudo-center terminal potential array In this example, the array mean ; 3.2 Calculate the potential baseline deviation Array: Substitute into a unified formula and perform point-by-point calculations to obtain... In this example, the array mean is 0.04mV. 3.3 Calculate the distance d between F and N electrodes FN Substituting the unified formula used for spacing calculation above, and combining it with the coordinates of the misconnected electrodes, in this example, we obtain d. FN =6.02cm; 3.4 Inverting the True F / N Voltage Array: Substituting into the unified inversion formula, and using k=0.03mV / cm determined based on weight and waist circumference, the true F / N voltage array is obtained through point-by-point inversion calculation. ; Array example: ,reality Keep the original array unchanged; array example: Gender and age have no additional effect on the k-value of this body type and do not require correction.

[0035] Step 4: Full correction of lead potentials (point-by-point array operation) 4.1 Correction for unipolar limb leads: Substitute into the unified correction formula mentioned above, and combine... , Array point-by-point operations yield the corrected array of unipolar lead voltages (example): ; ; The main wave resumes its upward trend, correcting the erroneous waveform. 4.2 Bipolar Limb Lead Correction: Calculate point-by-point using the unified correction formula; lead I requires no correction. Array example: The array mean is 0.17mV; Leads II and III are based on the inverted reality Point-by-point calculation yields the following correction value: Its average value is 0.25mV; Its average value is 0.08mV; 4.3 Electrical Axis Correction: Substituting into the unified electrical axis correction formula, calculations are performed based on the average value of the voltage array for each lead, combined with... After adjustment and correction, the electric axis is 42.3°, which is within the normal range of -30° to +120°, thus correcting the erroneous electric axis.

[0036] Step 5: Clinical Feature Validation and Iterative Optimization 5.1 Verification of Potential Balance: Substituting the unified deviation value formula, and calculating based on the mean of the corrected lead voltage array, the following is obtained: ,and If the deviation is consistent (0% < 10%), the potential balance returns to normal; in this example, the deviation threshold is 10%. 5.2 Comprehensive verification: After correction, the electrical axis is normal, the main wave of the voltage array in lead aVF is upward, and the mean value of the baseline drift array is <0.1mV, which is consistent with the phase of the voltage array in the chest leads. All verification items meet the standards and no iteration is required. 5.3 Output Results: Outputs the corrected normal voltage arrays and corresponding waveforms for all limb and chest leads, completing the error waveform correction based on individualized coefficients and adaptive voltage arrays, without the need for secondary data acquisition.

[0037] Step 6: Handling Special Cases In this embodiment, the patient has no abdominal organ lesions, the electrodes show no significant micro-movement, and gender and age have no additional interference with the correction parameters, eliminating the need to fit a nonlinear voltage array conversion relationship; in one specific implementation, the patient's individualized coefficients and parameter values, such as k=0.03mV / cm, The data is stored in a database to provide a reference for voltage array correction for patients of similar body type, gender, and age, thereby improving the efficiency of subsequent corrections.

[0038] Example 4: This embodiment describes a simulated correction procedure for misconnection of the F / N leads in obese elderly women. This embodiment corresponds to... Figure 3 The F / N misconnection is an incorrect connection state, suitable for obese elderly women, highlighting the influence of gender, age, weight, and waist circumference on the correction parameters. Based on the obtained original error voltage array, individualized coefficients are input to achieve precise correction. Relying on the unified core formula mentioned above, all calculations are point-by-point array operations. The simulation correction method of this embodiment of the invention includes the following steps.

[0039] Step 1: Error-prone raw data collection and individualized coefficient entry 1.1 Acquire the acquired erroneous raw ECG data: Extract the erroneous voltage array from the limb leads, given... ; In this example, an array is shown below: ; Array example: ; ; ; The electrical axis was -45°, the baseline drift was 0.15mV, and the chest lead voltage array was collected simultaneously as a verification reference. 1.2 Input individualization coefficients: Gender (female), Age (68 years old, elderly), Height (158cm), Weight (90kg), Waist circumference (100cm). Based on these coefficients, determine the potential decay coefficient k = 0.018mV / cm (elderly women, obese body type, thick abdominal fat, slow potential decay, k value is lower than normal body type). The Y-axis reference length is 72cm (suitable for a height of 158cm), and the X-axis abdominal region reference width is 50cm (suitable for a waist circumference of 100cm). Angle calculations need to consider the physiological characteristics of the elderly and, based on prior experience values ​​obtained from pre-testing, additionally correct for deviations of 0.3°. .

[0040] Step 2: Individualized Triangulation Modeling 2.1 Establish a coordinate system: Adjust the Y-axis scaling ratio based on height, adjust the X-axis abdominal width based on waist circumference, with the midpoint of the sternum as the origin; 2.2 Record the coordinates of the incorrectly connected electrodes: RA (3.0cm, 7.2cm), LA (-3.0cm, 7.2cm), incorrectly connected F (4.0cm, -5.5cm), incorrectly connected N (-4.0cm, -5.3cm); 2.3 Constructing a double-triangle structure: Similar to Example 1, construct a misconnected triangle and a normal triangle; 2.4 Calculate the angular offset Substituting into a unified formula and combining coordinate data, the initial values ​​are calculated. After adjustments based on the physiological characteristics of elderly women, the final In one specific implementation, The adjustment is based on the correspondence between pre-built individualized coefficients such as age and gender.

[0041] Step 3: Individualized potential inversion (point-by-point array operation) 3.1 Calculate the center terminal potential array, Array: Substitute into a unified formula and perform point-by-point calculations to obtain... Its average value is 0.32mV; Its average value is 0.37mV; Array, in this example, The array = [0.048, 0.050, 0.052, ..., 0.048] mV has a mean of 0.05mV; 3.2 Calculate d FN Substituting into the unified formula, we get d. FN =8.02cm; 3.3 Inverting the True F / N Voltage Array: Substituting into the unified inversion formula and performing point-by-point calculations, using k=0.018mV / cm determined based on weight, waist circumference, gender, and age, the true F / N voltage array is obtained. ; Array example: ),reality Keep the original array unchanged.

[0042] In one specific implementation, the above-mentioned k value is determined based on a pre-built correspondence between weight, waist circumference, gender, age and k value.

[0043] Step 4: Full correction of lead potentials (point-by-point array operation) 4.1 Correction for unipolar and bipolar leads: Substitute into the unified correction formula, and combine... , Example of obtaining the corrected voltage array through point-by-point array operations: ; ; ; (mean 0.17mV); (Mean value 0.244mV); (Mean value 0.074mV); 4.2 Electrical Axis Correction: Substituting into the unified electrical axis formula, calculations are performed based on the average value of the voltage array for each lead, combined with... After adjustment and correction, the electric axis is 38.7°, which is within the normal range.

[0044] Step 5: Verification and Iteration The formula for uniform deviation value was used for verification, and the calculation was based on the corrected array mean. The deviation value is 0%; the electrical axis, waveform, baseline, and precordial lead matching all meet the standards, no iteration is required, and the corrected normal ECG voltage array and waveform are output.

[0045] Step 6: Handling Special Cases Electrode movement is prone to occur in obese elderly women. Based on the pre-established correspondence between height and weight parameters and k-values, and combined with the preset k=0.018mV / cm for height and weight parameters, =0.015mV / ° (aVF lead), and the baseline filter coefficient is adjusted in conjunction with age to smooth the voltage array, reduce respiratory interference, and improve dynamic correction stability; if the verification does not meet the standard, the k value is adjusted first. In this case, it is most affected by body weight and waist circumference, and then adjusted. The value is then recalculated point by point in the array.

[0046] Example 5: This embodiment is a simulated correction procedure for a completely mirror-image misconnection of the RA / LA and F / N in a lean young male. This embodiment corresponds to Figure 4 The complete mirror image is in the wrong state, which is suitable for thin young men. It highlights the influence of height, weight and waist circumference on the correction of the misalignment of the two sets of electrodes. Based on the obtained original error voltage array, the individualized coefficient is input to achieve synchronous correction. Relying on the above unified core formula, all operations are point-by-point array operations.

[0047] The simulation correction method of this embodiment of the invention includes the following steps: Step 1: Error-prone raw data collection and individualized coefficient entry 1.1 Acquire the acquired erroneous raw ECG data: Extract the erroneous voltage array from the limb leads, given... In this example, the array is shown below: ; In this example, the array is shown below: ; ; ; The main wave of the voltage array in lead I reverses, indicating RA / LA interchange and abnormal electrical axis. Simultaneously acquire the voltage array of the chest leads. 1.2 Input Individualization Coefficients: Gender (Male), Age (28 years old, Youth), Height (182cm), Weight (55kg), Waist Circumference (72cm). Based on these coefficients, determine the potential decay coefficient k = 0.042mV / cm (for lean body types with thin fat and rapid potential decay). The Y-axis reference length is 86cm (suitable for a height of 182cm), and the X-axis abdominal region reference width is 36cm (suitable for a waist circumference of 72cm). The angle calculation does not require additional correction according to the pre-set angle adjustment rules. .

[0048] Step 2: Individualized triangulation modeling (simultaneous correction of RA / LA mirroring) 2.1 Establish a coordinate system: Adjust the coordinate scaling ratio based on height and waist circumference, with the midpoint of the sternum as the origin; 2.2 Record the coordinates of the incorrectly connected electrodes and correct the RA / LA mirror image: RA (-2.3cm, 8.6cm) and LA (2.3cm, 8.6cm) were incorrectly connected. First, swap their coordinates (correcting the RA / LA mirror image) to obtain the corrected RA (2.3cm, 8.6cm) and LA (-2.3cm, 8.6cm); F (2.8cm, -4.8cm) and N (-2.8cm, -4.6cm) were also incorrectly connected. 2.3 Constructing a double-triangle structure: Based on the corrected position coordinates of RA and LA, construct the misaligned triangle and the normal triangle; 2.4 Calculate the angular offset Substituting into the unified formula and combining it with the coordinate data, we obtain... .

[0049] Step 3: Individualized potential inversion (point-by-point array operation) 3.1 Calculate the center terminal potential array, Array: Substitute into a unified formula and perform point-by-point calculations to obtain... (The average value is 0.25mV) (mean value is 0.29mV) and Array; for example: The array = [0.038, 0.040, 0.042, ..., 0.038] mV has a mean of 0.04mV; 3.2 Calculate d FN Substituting into the unified formula used for spacing calculation above, we get d.FN =5.62cm; 3.3 Inverting the True F / N Voltage Array: Substituting into the unified inversion formula and performing point-by-point calculations, using k=0.042mV / cm, the true F / N voltage array is obtained. Array example: ,reality Keep the original array unchanged.

[0050] Step 4: Full correction of lead potentials: Simultaneous correction of RA / LA and F / N misalignment, point-by-point array calculation; 4.1 Correction of RA / LA mirror image bias: Invert the voltage array of lead I point by point, i.e. ,get ; 4.2 Correction for unipolar and bipolar leads: Substitute into the unified correction formula, and combine... , The array and the corrected RA / LA coordinates, the inverted true F / N voltage array, and the correction of all limb lead voltage arrays are completed point by point to ensure synchronization with the original sampling sequence; 4.3 Unipolar Limb Lead Correction (Adapted to RA / LA Mirror Correction Parameters): Point-by-point calculation yields the corrected unipolar lead voltage array (example): ; ; ; The main waves all returned to an upward direction, correcting the polarity abnormality caused by the misconnection of the mirror image; 4.4 Bipolar Limb Lead Correction - Synchronous Adaptation of RA / LA and F / N Double Misalignment): Lead I is further combined based on the inverted array before correction. The array is corrected point by point to obtain The array mean is 0.16mV, restoring the normal main wave direction; leads II and III are based on the inverted true value. And after correcting the voltage arrays RA and LA, point-by-point calculations are performed to obtain (exemplary): Its average value is 0.30mV; Its average value is 0.15mV; 4.5 Electrical Axis Correction: Substituting into the unified electrical axis correction formula, calculations are performed based on the average value of the voltage array for each lead, combined with... After adjustment and correction, the electric axis is 45.1°, which is within the normal range of -30° to +120°, completely correcting the electric axis abnormality caused by the mirror misconnection.

[0051] Step 5: Clinical Feature Validation and Iterative Optimization 5.1 Potential Balance Verification: Substituting the unified deviation value formula, the calculation is based on the mean of the corrected lead voltage array. ,and The deviation value is approximately 3.3% < 10%, which satisfies Einstein's triangular potential balance law, and the potential balance meets the standard. 5.2 Comprehensive clinical validation: The corrected electrical axis (45.1°) is normal, the main wave in lead aVF is upward, the mean value of the baseline drift array is <0.1mV, the direction of the main wave in lead I is restored to normal (correcting the mirror misconnection defect), and it is consistent with the phase of the voltage array of the chest leads. There are no waveform distortion, time lag or other problems. All validation items meet the standards and no iterative optimization is required. 5.3 Output Results: Outputs the normal voltage arrays and corresponding waveforms for all limb leads after correction, namely leads I, II, III, aVR, aVL, aVF, and chest leads (V1~V6). Simultaneously outputs individualized coefficients (gender male, age 28 years, etc.) and core correction parameters (k=0.042mV / cm). It can accurately correct RA / LA and F / N completely mirrored misconnections without the need to wear the device again to collect data.

[0052] Step 6: Handling Special Cases In this embodiment, the patient is thin with little body fat, resulting in poor electrode-skin contact stability and susceptibility to voltage array fluctuations caused by respiratory movements. The baseline filtering coefficient can be adjusted based on height and weight parameters to smooth the corrected voltage array and reduce interference noise. In one specific implementation, the baseline filtering coefficient is adjusted according to a preferred adjustment method obtained through prior testing. Simultaneously, the relatively close distance between the heart and electrodes in thin patients leads to rapid potential decay. Therefore, when correcting similar patients in the future, the k-value (0.042 mV / cm) in this case can be preferentially referenced, combined with minor adjustments to waist circumference to improve correction efficiency. If excessive electrical axis deviation occurs during verification, the coordinate deviation after RA / LA mirror correction should be adjusted first, followed by fine adjustments. The value is then recalculated point by point to ensure that the correction accuracy meets clinical diagnostic standards.

[0053] Examples 3 to 5 illustrate specific scenarios, and the specific values ​​of each variable used are merely illustrative. Those skilled in the art can adjust the values ​​according to the patient's actual personalized coefficients based on the concept of this invention, which will not be elaborated here.

[0054] Example 6: The present invention also provides an electronic device, which includes a processor, a memory, a bus 1103, and a computer program stored in the memory and executable on the processor. The processor includes one or more processing cores, and the memory is connected to the processor via the bus. The memory is used to store program instructions. When the processor executes the computer program, it implements the steps in the above-described method embodiment of Embodiment 1 of the present invention.

[0055] Furthermore, as an executable solution, the electronic device can be a computer unit, which can be a desktop computer, laptop, handheld computer, cloud server, or other computing device. The computer unit may include, but is not limited to, a processor and memory. Those skilled in the art will understand that the above-described structure of the computer unit is merely an example and does not constitute a limitation on the computer unit. It may include more or fewer components, or combine certain components, or use different components. For example, the computer unit may also include input / output devices, network access devices, buses, etc., and this embodiment of the invention does not limit this.

[0056] Furthermore, as an executable solution, the processor can be a Central Processing Unit (CPU), or other general-purpose processors, digital signal processors (DSPs), application-specific integrated circuits (ASICs), field-programmable gate arrays (FPGAs), or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc. The general-purpose processor can be a microprocessor or any conventional processor, etc. The processor is the control center of the computer unit, connecting various parts of the entire computer unit via various interfaces and lines.

[0057] The memory can be used to store the computer programs and / or modules. The processor implements various functions of the computer unit by running or executing the computer programs and / or modules stored in the memory and by calling data stored in the memory. The memory may mainly include a program storage area and a data storage area. The program storage area may store the operating system and at least one application program required for a function; the data storage area may store data created based on the use of the mobile phone, etc. In addition, the memory may include high-speed random access memory and may also include non-volatile memory, such as hard disk, RAM, plug-in hard disk, smart media card (SMC), secure digital card (SD card), flash card, at least one disk storage device, flash memory device, or other volatile solid-state storage device.

[0058] Example 7: The present invention also provides a computer-readable storage medium storing a computer program, which, when executed by a processor, implements the steps of the method described in the embodiments of the present invention.

[0059] If the modules / units integrated in the computer unit are implemented as software functional units and sold or used as independent products, they can be stored in a computer-readable storage medium. Based on this understanding, all or part of the processes in the methods of the above embodiments can also be implemented by a computer program instructing related hardware. The computer program can be stored in a computer-readable storage medium, and when executed by a processor, it can implement the steps of the various method embodiments described above. The computer program includes computer program code, which can be in the form of source code, object code, executable files, or certain intermediate forms. The computer-readable medium can include: any entity or device capable of carrying the computer program code, recording media, USB flash drives, portable hard drives, magnetic disks, optical disks, computer memory, read-only memory (ROM), random access memory (RAM), and software distribution media, etc. It should be noted that the content contained in the computer-readable medium can be appropriately increased or decreased according to the requirements of legislation and patent practice in the jurisdiction.

[0060] Example 8: The present invention also provides a computer program product, including a computer program that, when executed by a processor, implements the steps described above.

[0061] Although the invention has been specifically shown and described in conjunction with preferred embodiments, those skilled in the art should understand that various changes in form and detail may be made to the invention without departing from the spirit and scope of the invention as defined in the appended claims, all of which shall be within the scope of protection of the invention.

Claims

1. A method for simulating and correcting incorrect electrode placement in dynamic electrocardiography, used to perform simulated correction when the F and N electrodes are reversed, characterized in that, include: Acquire raw dynamic electrocardiogram data when the F and N electrodes are reversed. The raw data includes: erroneous voltage arrays of limb leads and voltage arrays of chest leads. The system receives the patient's personalized coefficients and performs individualized triangulation modeling based on these coefficients. The personalized coefficients include: gender, age, height, weight, and waist circumference. The individualized triangulation modeling includes: establishing a two-dimensional coordinate system on the body surface, recording electrode spatial coordinates, constructing a double-triangular structure, and calculating the angular offset of the lead vectors. The double-triangle structure includes: a misaligned triangle with the correct positions of the RA and LA electrodes as the upper vertex and the position of the incorrectly attached F electrode as the lower vertex, and a normal triangle with the correct position of the F electrode as the lower vertex; the normal triangle is used as a modeling reference. Based on the modeling results, the potential baseline deviation was calculated. array and spacing between F and N electrodes And according to the potential baseline deviation Arrays and Spacing The actual potential and voltage arrays of the F and N electrodes are obtained by point-by-point inversion; wherein, the potential baseline deviation The array = the pseudo center terminal potential array when the F and N electrodes are reversed minus the normal center terminal potential array when the F and N electrodes are not reversed; Based on Einstein's triangular potential balance law, the aforementioned angular offset is used. and the potential baseline deviation The erroneous voltage array of limb leads is corrected point by point to obtain the corrected limb lead voltage array, and the electrical axis is corrected to the predetermined normal range. The modified limb lead voltage array is validated using predetermined core clinical features of dynamic electrocardiogram, and the modified limb lead voltage array and waveform are output after successful validation.

2. The simulation correction method for incorrect placement of dynamic electrocardiogram electrodes according to claim 1, characterized in that, Establishing a two-dimensional coordinate system for the body surface includes: A two-dimensional coordinate system is established on the body surface with the midpoint of the sternum as the origin O, the X-axis pointing horizontally to the right, and the Y-axis pointing vertically upward. The scaling ratio of the Y-axis is adjusted based on the height, and the reference width of the abdominal region on the X-axis is adjusted based on the waist circumference.

3. The simulation correction method for incorrect placement of dynamic electrocardiogram electrodes according to claim 2, characterized in that, Recording electrode spatial coordinates according to the aforementioned two-dimensional coordinate system of the body surface includes: Record the coordinates of the RA electrode (X1), the LA electrode (X2), the incorrectly placed F electrode (X3), the incorrectly placed N electrode (X4), and the correct F electrode position. The coordinates; The angular offset of the lead vector is calculated using the following formula. : ； in, The origin of the central electrical terminal is at the same position as the origin of the coordinate system O. The pseudo-center point origin when the F and N electrodes are reversed; spacing The distance between position X3 and position X4; The true F electrode potential and voltage array is obtained by point-by-point inversion using the following formula. : Where i = 1, 2, ..., n; n is the number of sampling points; in, This is the actual N-electrode potential and voltage array, which retains the original array unchanged; The abdominal potential attenuation coefficient is adjusted based on the stated weight, waist circumference, gender, and age, according to a predetermined correction rule.

4. The simulation correction method for incorrect placement of dynamic electrocardiogram electrodes according to claim 3, characterized in that, Point-by-point correction of erroneous voltage arrays in limb leads includes: Use the following formula to correct for unipolar limb leads: ； in, This is the angle correction factor. Corresponding to aVR, aVL, and aVF; among them, for aVR, =0.01mV / °; for aVL, =0.012mV / °; for aVF, =0.015mV / °; Use the following formula to correct for bipolar limb leads: ； ； ； The electrical axis is corrected using the following formula: ； in, The corrected electrical axis direction corresponds to degrees. Represents the corresponding voltage array The mean.

5. The simulation correction method for incorrect placement of dynamic electrocardiogram electrodes according to claim 4, characterized in that, Validation of the modified limb lead voltage array using core clinical features of Holter monitoring includes: The potential balance verification deviation value is calculated using the following formula: ； When the deviation value is less than a predetermined deviation threshold, potential balance is determined; and, When the corrected electric axis is normal, When the main wave of the VF lead voltage array is upward and the mean value of the baseline drift array is less than a predetermined voltage threshold and is consistent with the chest lead voltage array, the verification is confirmed to be successful; wherein, the predetermined voltage threshold is less than or equal to 0.1mV.

6. The simulation correction method for incorrect placement of dynamic electrocardiogram electrodes according to claim 1, characterized in that, When the RA and LA electrodes are also reversed, when constructing the double-triangle structure, first correct the mirror image of the RA and LA electrodes by swapping their positions, and then use the corrected positions of the RA and LA electrodes to construct the double-triangle structure.

7. The simulation correction method for incorrect placement of dynamic electrocardiogram electrodes according to claim 3, characterized in that, Abdominal potential attenuation coefficient The value should be set as follows: patients who meet the criteria of being thin and having thin body fat > patients who meet the criteria of being normal and having moderate body fat thickness > patients who meet the criteria of being obese and having thick abdominal fat.

8. An electronic device, characterized in that, The device includes a memory and a processor, the memory storing at least one program, which is executed by the processor to implement the steps of the simulation correction method for misplaced dynamic electrocardiogram electrodes as described in any one of claims 1 to 7.

9. A computer-readable storage medium, characterized in that, The storage medium stores at least one program, which is executed by a processor to implement the steps of the simulation correction method for misplaced dynamic electrocardiogram electrodes as described in any one of claims 1 to 7.

10. A computer program product, comprising a computer program, characterized in that, When the computer program is executed by the processor, it implements the steps of the simulation correction method for misplaced dynamic electrocardiogram electrodes as described in any one of claims 1 to 7.

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