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Vectorcardiography
Vectorcardiography
from Wikipedia
Vectorcardiography
Normal vectorcardiogram
ICD-9-CM89.53
MeSHD014672

Vectorcardiography (VCG) is a method of recording the magnitude and direction of the electrical forces that are generated by the heart by means of a continuous series of vectors that form curving lines around a central point.[1]

Vectorcardiography was developed by Ernest Frank in the mid 1950s.[2][3] Since the human body is a three-dimensional structure, the basic idea is to construct three orthogonal leads containing all the electric information. The three leads are represented by right-left axis (X), head-to-feet axis (Y) and front-back (anteroposterior) axis (Z).

To calculate Frank's leads X, Y and Z using the standard leads system, the following expressions[4] are used:

X = -(-0.172 V1 - 0.074 V2 + 0.122 V3 + 0.231 V4 + 0.239 V5 + 0.194 V6 + 0.156 DI - 0.010 DII) (1)

Y = (0.057 V1 - 0.019 V2 - 0.106 V3 - 0.022 V4 + 0.041 V5 + 0.048 V6 - 0.227 DI + 0.887 DII) (2)

Z = -(-0.229 V1 - 0.310 V2 - 0.246 V3 - 0.063 V4 + 0.055 V5 + 0.108 V6 + 0.022 DI + 0.102 DII) (3)

Researchers have developed various methods of evaluating vectorcardiograms. Grygoriy Risman presents these different methods, which were developed over half a century and which offer an advanced approach called spatial vectorcardiometry (SVCM).[5] The original Russian thesis is filed in the Odesa National Medical University.[6] Recently, Bipolar Precordial Leads exploring the right to left axis combined with averaged unipolar precordial leads allowed to produce sectorial VCG loops in the horizontal plane.[7]

Spatial QRS-T angle

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The spatial QRS-T angle (SA) is derived from a vectorcardiogram, which is a three-dimensional representation of the 12-lead electrocardiogram (ECG) created with a computerized matrix operation. The SA is the angle of deviation between two vectors; the spatial QRS-axis representing all of the electrical forces produced by ventricular depolarization and the spatial T-axis representing all the electrical forces produced by ventricular repolarization.[8] The SA is indicative of the difference in orientation between the ventricular depolarization and repolarization sequence.[citation needed]

In healthy individuals, the direction of ventricular depolarization and repolarization is relatively reversed; this creates a sharp SA.[9] There is high individual variability and gender difference in the magnitude of the SA. The mean, normal SA in healthy young adult females and males is 66° and 80°, respectively,[9] and very similar magnitudes are found in the elderly population (65 years and older).[10] In ECG analysis, the SA is categorized into normal (below 105°), borderline abnormal (105–135°) and abnormal (greater than 135°).[11] A broad SA results when the heart undergoes pathological changes and is reflected in a discordant ECG. A large SA indicates an altered ventricular repolarization sequence, and may be the result of structural and functional myocardial changes that induce regional shortening in action potential duration and impaired ion channel functioning.[12]

Current standard ECG markers of repolarization abnormalities include ST depression, T wave inversion and QT prolongation. Many studies have investigated the prognostic strength of the SA for cardiac morbidity and mortality compared to these and other ECG parameters. In treated hypertensive patients, the SA was significantly larger in patients with elevated blood pressure compared to those with lower blood pressure values and a discrimination between patients with high and low blood pressure could not be detected using other ECG parameters.[13] In the Rotterdam Study with men and women aged 55 years and older, having an abnormal SA significantly increased the hazard ratios for cardiac death, sudden cardiac death, non-fatal cardiac events (infarction, coronary interventions) and total mortality. Independently, the SA was a stronger risk indicator of cardiac mortality compared to the other cardiovascular and ECG risk factors analyzed.[11] The Women's Health Initiative study concluded that a wide SA was the strongest predictor for incident coronary heart failure risk and a dominant risk factor for all cause mortality compared to several other ECG parameters.[12] The SA also increases accuracy of diagnosing left ventricular hypertrophy (LVH). Using only conventional ECG criteria to diagnose LVH the diagnostic accuracy was 57%, however the inclusion of the SA significantly improved the diagnostic accuracy to 79%.[14]

The SA is not routinely measured in clinical ECG examination even though the computerized vectorcardiography software is widely available, efficient and is not affected by observational biases unlike other ECG parameters.[13] The SA is a sensitive marker of repolarization aberrations and with further research support the SA will likely become clinically applied in predicting cardiac morbidity and mortality.[citation needed]

A simplified criteria in using the vectorcardiogram has the ability to identify patients with a diaphragmatic infarction not apparent in the electrocardiogram. [15]

See also

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References

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Revisions and contributorsEdit on WikipediaRead on Wikipedia
from Grokipedia
Vectorcardiography (VCG) is a diagnostic technique that records the magnitude, direction, and spatial orientation of the electrical forces produced by the heart during and , generating a three-dimensional vector loop representation of cardiac activity using orthogonal leads. This method provides a spatial synthesis of the heart's electrical vectors, complementing the planar views of the standard 12-lead electrocardiogram (ECG) by visualizing the trajectory of electrical activity in the frontal, transverse, and sagittal planes. VCG originated from early observations of the heart's dipolar electrical nature, first noted by Augustus D. Waller in his 1887 recording of the human electrocardiogram, which laid the groundwork for vector-based analysis. In the 1920s, Hubert Mann advanced the concept by introducing vector loops to depict cardiac electrical paths. While and saw further refinements, including systems proposed by Schellong (1937), (1939), and Duchosal and Sulzer (1949). The technique was standardized for clinical use in 1956 with Ernest Frank's development of an accurate orthogonal lead system (X, Y, Z leads), designed to minimize distortion from body geometry and enable precise spatial vectorcardiography. At its core, VCG principles rely on projecting the heart's instantaneous electrical vector onto three mutually axes, producing loops for the (atrial ), (ventricular ), and (ventricular ), which can be analyzed for magnitude, duration, and rotation. These loops offer quantitative indices, such as the spatial QRS-T angle and vector magnitudes, that enhance the detection of abnormalities not always evident in scalar ECG tracings. Clinically, VCG has proven valuable in diagnosing , where it detects spatial changes in the QRS loop with higher sensitivity (up to 98.07% accuracy for ischemia in some studies) than traditional ECG, as well as , bundle branch blocks, and . It also aids in assessing conduction delays, monitoring outcomes, and predicting ventricular arrhythmias or mortality in patients with implantable cardioverter-defibrillators. Although direct VCG recording waned with the widespread adoption of 12-lead ECG in the late , renewed interest has emerged through mathematical transformations—like the inverse matrix or Kors regression—that derive VCG parameters from standard ECGs. As of 2024, advancements including AI-driven 3D vectorcardiography and non-invasive tools like vMap have further enhanced its accessibility for prognostic and therapeutic applications without specialized equipment.

Definition and Principles

Core Concepts

Vectorcardiography (VCG) is a technique that provides a three-dimensional representation of the heart's electrical activity by recording the magnitude, direction, and temporal sequence of electrical vectors produced during and . These vectors model the heart as an equivalent dipole, known as the electric heart vector (EHV), which captures the net electrical forces generated by myocardial cells. Unlike (ECG), which measures voltage over time at specific points, VCG emphasizes the spatial orientation and progression of these forces, enabling a more comprehensive view of . The core principle of VCG involves transforming scalar ECG signals into continuous vector loops plotted in three mutually orthogonal planes: the frontal plane (reflecting left-right and superior-inferior axes), the (left-right and anterior-posterior), and the (superior-inferior and anterior-posterior). This transformation uses orthogonal lead systems to project the EHV's trajectory, where each loop corresponds to phases of the , such as the for ventricular or the ST-T segment for . The resulting loops illustrate how electrical activity propagates through the heart in a spatiotemporal manner, offering a visual synthesis of vector summation across the myocardium. Key terminology in VCG includes vectors, which denote the instantaneous direction and strength of electrical activity; loops, formed by the sequential connection of vector tips over time; magnitude, representing the loop's size or the vector's (e.g., voltage extent); , the angular direction of the vector within a plane; and , the loop's traversal direction ( or counterclockwise), indicating wavefront progression. These elements allow for the analysis of electrical forces' spatial relationships, such as their alignment or deviation during the . As a prerequisite for studying , VCG facilitates an intuitive grasp of how bioelectric signals spread in three dimensions, serving as a complementary method to the standard 12-lead ECG by highlighting vectorial dynamics rather than isolated waveforms.

Vectorial Analysis of Cardiac Activity

The biophysical basis of vectorcardiography lies in the electrical activity of cardiac cells, where changes in transmembrane potential during and generate dipole vectors. In individual cardiomyocytes, occurs as sodium ions influx across the , creating a potential difference that propagates as a , while involves potassium efflux, restoring the . These local transmembrane potential gradients (Vm\nabla V_m) produce intracellular current densities (JiJ_i) that act as , with the dipole moment proportional to the gradient according to Ji=giVmJ_i = g_i \nabla V_m, where gig_i is the intracellular conductivity. During the , rapid dominates, yielding large dipole contributions, whereas the ST-T segment reflects slower with smaller gradients. Multiple such dipoles from the atrial and ventricular myocardium sum vectorially to form the resultant heart vector observed at the body surface. The collective electrical activity of the myocardium, comprising billions of cells, is approximated by integrating these dipoles over the tissue volume, weighted by the body's conductivity and geometry, to yield surface potentials. In ventricular , early of the and creates initial dipoles that combine with later epicardial contributions, resulting in a net vector that propagates through the . This summation is modeled as a superposition of potentials, where the pseudo-vectorcardiogram (pVCG) component, for instance, is given by pVx=JiL12dA/σbpV_x = \int J_i \cdot L_{12} \, dA / \sigma_b, with L12L_{12} as the lead field and σb\sigma_b the body surface conductivity. The resultant heart vector thus represents the spatial and temporal integration of myocardial , attenuated by volume conduction. Mathematically, the instantaneous heart vector in vectorcardiography is represented as V(t)=(X(t),Y(t),Z(t))\vec{V}(t) = (X(t), Y(t), Z(t))
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