Roberto M.Lang, MichelleBierig, Richard B.Devereux, Frank A.Flachskampf, ElyseFoster, Patricia A.Pellikka, Michael H.Picard, Mary J.Roman, JamesSeward, JackShanewise, ScottSolomon, Kirk T.Spencer, MartinSt. John Sutton, WilliamStewart
Quantification of cardiac chamber size, ventricular mass and function ranks among the most clinically important and most frequently requested tasks of echocardiography. Over the last decades, echocardiographic methods and techniques have improved and expanded dramatically, due to the introduction of higher frequency transducers, harmonic imaging, fully digital machines, left-sided contrast agents, and other technological advancements. Furthermore, echocardiography due to its portability and versatility is now used in emergency rooms, operating rooms, and intensive care units. Standardization of measurements in echocardiography has been inconsistent and less successful, compared to other imaging techniques and consequently, echocardiographic measurements are sometimes perceived as less reliable. Therefore, the American Society of Echocardiography, working together with the European Association of Echocardiography, a branch of the European Society of Cardiology, has critically reviewed the literature and updated the recommendations for quantifying cardiac chambers using echocardiography. This document reviews the technical aspects on how to perform quantitative chamber measurements of morphology and function, which is a component of every complete echocardiographic examination.
left ventricular internal dimension
left ventricular internal dimension at end diastole
left ventricular internal dimension at end systole
septal wall thickness at end-diastole
posterior wall thickness at end-diastole
endocardial border delineation
Quantification of cardiac chamber size, ventricular mass and function ranks among the most clinically important and most frequently requested tasks of echocardiography. Standardization of chamber quantification has been an early concern in echocardiography and recommendations on how to measure such fundamental parameters are among the most often cited papers in the field.1,2 Over the last decades, echocardiographic methods and techniques have improved and expanded dramatically. Improvements in image quality have been significant, due to the introduction of higher frequency transducers, harmonic imaging, fully digital machines, left-sided contrast agents, and other technological advancements.
Furthermore, echocardiography has become the dominant cardiac imaging technique, which due to its portability and versatility is now used in emergency rooms, operating rooms, and intensive care units. Standardization of measurements in echocardiography has been inconsistent and less successful, compared to other imaging techniques and consequently, echocardiographic measurements are sometimes perceived as less reliable. Therefore, the American Society of Echocardiography, working together with the European Association of Echocardiography, a branch of the European Society of Cardiology, has critically reviewed the literature and updated the recommendations for quantifying cardiac chambers using echocardiography. Not all the measurements described in this document can be performed in all patients due to technical limitations. In addition, specific measurements may be clinically pertinent or conversely irrelevant in different clinic scenarios. This document reviews the technical aspects on how to perform quantitative chamber measurements and is not intended to describe the standard of care of which measurements should be performed in individual clinical studies. However, evaluation of chamber size and function is a component of every complete echocardiographic examination and these measurements may have an impact on clinical management.
Enhancements in imaging have followed technological improvements such as broadband transducers, harmonic imaging and left-sided contrast agents. Nonetheless, image optimization still requires considerable expertise and attention to certain details that are specific to each view (Table 1). In general, images optimized for quantitation of one chamber may not necessarily be optimal for visualization or measurement of other cardiac structures. The position of the patient during image acquisition is important. Optimal views are usually obtained with the patient in the steep left-lateral decubitus position using a cut-out mattress to permit visualization of the true apex while avoiding LV foreshortening. The patient's left arm should be raised to spread the ribs. Excessive translational motion can be avoided by acquiring images during quiet respiration. If images are obtained during held end-expiration, care must be taken to avoid a Valsalva maneuver, which can degrade image quality.
Elements of image acquisition and measurement for two-dimensional quantitation
Minimize translational motion
Quiet or suspended respiration (at end-expiration)
Maximize image resolution
Image at minimum depth necessary
Highest possible transducer frequency
Adjust gains, dynamic range, transmit and lateral gain controls appropriately
Frame rate ≥30/s
Avoid apical foreshortening
Steep lateral decubitus position
Avoid reliance on palpable apical impulse
Maximize endocardial border
Contrast enhancement delineation
Identify end-diastole and end-systole
Mitral valve motion and cavity size rather than reliance on ECG
Digital capture and display of images on the echocardiographic system or on a workstation should optimally display images at a rate of at least ≥30 frames/second. In routine clinical practice a representative cardiac cycle can be used for measurement as long as the patient is in sinus rhythm. In atrial fibrillation, particularly when there is marked RR variation, multiple beats should be used for measurements. Averaging measurements from additional cycles may be particularly useful when R-R intervals are highly irregular. When premature atrial or ventricular contractions are present, measurements should be avoided in the post-ectopic beat since the length of the preceding cardiac cycle can influence ventricular volume and fiber shortening.
Harmonic imaging is now widely employed in clinical laboratories to enhance the images especially in patients with poor acoustic windows. While this technology reduces the “drop-out” of endocardial borders, the literature suggests that there is a systemic tendency for higher measurements of LV wall thickness and mass and smaller measurements of internal dimensions and volumes.3,4 When analyzing serial studies on a given patient, differences in chamber dimension potentially attributable to imaging changes from the fundamental to the harmonic modality are probably smaller than the inter and intra-observer variability of these measurements. The best technique for comparing serial changes in quantitation is to display similar serial images side-by-side and make the same measurement on both images by the same person, at the same time.5 It is important to note that most measurements presented in this manuscript are derived from fundamental imaging as normative values have not been established using harmonic imaging.
Left-sided contrast agents used for endocardial border delineation (EBD) are helpful and improve measurement reproducibility for suboptimal studies and correlation with other imaging techniques. While the use of contrast agents has been reviewed elsewhere in detail,6 a few caveats regarding their use deserve mention. The mechanical index should be lowered to decrease the acoustic power of the ultrasound beam, which reduces bubble destruction. The image should be “focused” on the structure of interest. Excessive shadowing may be present during the initial phase of bubble transit and often the best image can be recorded several cardiac cycles following the appearance of contrast in the left ventricle. When less than 80% of the endocardial border is adequately visualized, the use of contrast agents for EBD is strongly recommended.7 By improving visualization of the LV apex, the problem of ventricular foreshortening is reduced and correlation with other techniques improved. Contrast enhanced images should be labeled to facilitate the reader identification of the imaging planes.
Quantitation using transesophageal echocardiography (TEE) has advantages and disadvantages compared to transthoracic echocardiography (TTE). Although visualization of many cardiac structures is improved with TEE some differences in measurements have been found between TEE and TTE. These differences are primarily attributable to the inability to obtain from the transesophageal approach the standardized imaging planes/views used when quantifying chamber dimensions transthoracically.8,9 It is the recommendation of this writing group that the same range of normal values for chamber dimensions and volumes apply for both TEE and TTE. In this manuscript, recommendations for quantification using TEE will primarily focus on acquisition of images that allow measurement of cardiac structures along imaging planes that are analogous to TTE.
In addition to describing a parameter as normal or abnormal (reference values), clinical echocardiographers most often qualify the degree of abnormality with terms such as “mildly”, “moderately” or “severely” abnormal. Such a description allows the clinician to not only understand that the parameter is abnormal but also the degree to which their patient's measurements deviate from normal. In addition to providing normative data it would be beneficial to standardize cutoffs for severity of abnormality across echocardiographic laboratories, such that moderately abnormal had the same implication in all laboratories. However, multiple statistical techniques exist for determining thresholds values, all of which have significant limitations.10
The first approach would be to define cutoffs empirically for mild, moderate and severe abnormalities based on standard deviations above/below the reference limit derived from a group of normal subjects. The advantage of this method is that this data readily exists for most echocardiographic parameters. However, this approach has several disadvantages. Firstly, not all echocardiographic parameters are normally distributed, or Gaussian in nature, making the use of standard deviation questionable. Secondly, even if a particular parameter is normally distributed in control subjects, most echocardiographic parameters when measured in the general population have a significant asymmetric distribution in one direction (abnormally large for size or abnormally low for function parameters). Using the standard deviation derived from normal subjects leads to abnormally low cutoff values which are inconsistent with clinical experience, as the standard deviation inadequately represents the magnitude of asymmetry (or range of values) towards abnormality. This is the case with LV ejection fraction (EF) where 4 standard deviations below the mean (64±6.5) results in a cutoff for severely abnormal of 38%.
An alternative method would be to define abnormalities based on percentile values (95th, 99th, etc.) of measurements derived from a population that includes both normal subjects and those with disease states.11 Although this data may still not be Gaussian, it accounts for the asymmetric distribution and range of abnormality present within the general population. The major limitation of this approach is that large enough population data sets simply do not exist for most echocardiographic variables.
Ideally, an approach that would predict outcomes or prognosis would be preferred. That is defining a variable as moderately deviated from normal would imply that there is a moderate risk of a particular adverse outcome for that patient. Although sufficient data linking risk and cardiac chamber sizes exist for several parameters (i.e., EF, LV size, LA volume); risk data are lacking for many other parameters. Unfortunately, this approach continues to have several limitations. The first obstacle is how to best define “risk”. The cutoffs suggested for a single parameter vary broadly for the risk of death, myocardial infarction (MI), atrial fibrillation etc. In addition, much of the risk literature applies to specific populations (post-MI, elderly), and not general cardiovascular risk readily applicable to consecutive patients studied in an echocardiography laboratory. Lastly, although having data specifically related to risk is ideal, it is not clear that this is necessary. Perhaps cardiac risk rises inherently as echocardiographic parameters become more abnormal. This has been shown for several echocardiographic parameters (LA dimension, wall thickness, LV size and LV mass) which, when partitioned based on population estimates, demonstrated graduated risk, which is often non-linear.11
Lastly cutoffs values may be determined from expert opinion. Although scientifically least rigorous, this method takes into account the collective experience of having read and measured tens of thousands of echocardiograms.
No single methodology could be used for all parameters. The tables of cutoffs represent a consensus of a panel of experts using a combination of the methods described above (Table 2). The consensus values are more robust for some parameters than others and future research may redefine the cutoff values. Despite the limitations, these partition values represent a leap forward towards the standardization of clinical echocardiography.
Methods used to establish cutoff values of different echocardiographic parameters
Septal wall thickness
LV function linear method
Quantification of the left ventricle
Left ventricular dimensions, volumes and wall thicknesses are echocardiographic measurements widely used in clinical practice and research.12,13 LV size and performance are still frequently visually estimated. However, qualitative assessment of LV size and function may have significant inter-observer variability and is a function of interpreter skill. Therefore, it should regularly be compared to quantitative measurements, especially when different views qualitatively suggest different degrees of LV dysfunction. Similarly, it is also important to cross-check quantitative data using the “eye-ball” method, to avoid overemphasis on process-related measurements, which at times may depend on structures seen in a single still-frame. It is important to account for the integration over time of moving structures seen in one plane, and the integration of three-dimensional space obtained from viewing a structure in multiple orthogonal planes. Methods for quantitation of LV size, mass and function using two-dimensional imaging have been validated.14–17
There are distinct advantages and disadvantages to each of the accepted quantitative methods (Table 3). For example, linear LV measurements have been widely validated in the management of valvular heart disease, but may misrepresent dilatation and dysfunction in patients with regional wall motion abnormalities due to coronary artery disease. Thus, laboratories should be familiar with all available techniques and peer review literature and should apply them on a selective basis.
LV quantification methods: utility, advantages and limitations
– High frame rates
– Beam orientation frequently off-axis
– Wealth of accumulated data
– Single dimension may not be representative in “distorted” ventricles
– Most representative in “normally” shaped ventricles
– Assures orientation perpendicular to ventricular long-axis
– Lower frame rates than in M-mode
– Single dimension only
– Corrects for shape distortions
– Apex frequently foreshortened
– Minimizes mathematical assumptions
– Endocardial dropout
– Relies on only two planes
– Little accumulated data on normal population
– Partial correction for shape distortion
– Based on mathematical assumptions
- Little accumulated data
M-mode or 2-D guided
– Wealth of accumulated data
– Inaccurate in ventricles with regional abnormalities
– Beam orientation (M-mode)
– Small errors magnified
– Overestimates LV mass
– Allows for contribution of papillary muscles
– Insensitive to distortion in ventricular shape
– More sensitive to distortions in ventricular shape
– Based on a number or mathematical assumptions
– Minimal/normal data
General principles for linear and volumetric LV measurements
To obtain accurate linear measurements of interventricular septal and posterior wall thicknesses and LV internal dimension, recordings should be made from the parasternal long-axis acoustic window. It is recommended that LV internal diameters (LVIDd and LVIDs, respectively) and wall thicknesses be measured at the level of the LV minor axis, approximately at the mitral valve leaflet tips. These linear measurements can be made directly from 2D images or using 2D-targeted M-mode echocardiography.
By virtue of their high pulse rate, M-mode recordings have excellent temporal resolution and may complement 2-D images in separating structures such as trabeculae adjacent to the posterior wall, false tendons on the left side of the septum, and tricuspid apparatus or moderator band on the right side of the septum from the adjacent endocardium. However, it should be recognized that even with 2D guidance, it may not be possible to align the M-mode cursor perpendicular to the long axis of the ventricle which is mandatory to obtain a true minor axis dimension measurement. Alternatively, chamber dimension and wall thicknesses can be acquired from the parasternal short-axis view using direct 2D measurements or targeted M-mode echocardiography provided that the M-mode cursor can be positioned perpendicular to the septum and LV posterior wall.
A 2D method, useful for assessing patients with coronary artery disease has been proposed. When using this method, it is recommended that LV internal diameters (LVIDd and LVIDs, respectively) and wall thicknesses be measured at the level of the LV minor dimension, at the mitral chordae level. These linear measurements can also be made directly from 2D images or using 2D-targeted M-mode echocardiography. Direct 2D minor axis measurements at the chordae level intersect the interventricular septum below the left ventricular outflow tract,2,5,18 and thus provides a global assessment in a symmetrically contracting LV, and also evaluates basal regional function in a chamber with regional wall motion abnormalities. The direct 2D minor axis dimensions are smaller than the M-mode measurements with the upper limits of normal of LVIDd being 5.2cm vs 5.5cm and the lower limits of normal for fractional shortening being 0.18 vs 0.25. Normal systolic and diastolic measurements reported for this parameter are 4.7±0.4cm and 3.3±0.5cm, respectively.2,18
LVID and septal and posterior wall thicknesses (SWT and PWT, respectively) are measured at end-diastole (d) and end-systole (s) from 2-D or M-mode recordings,1,2 preferably on several cardiac cycles (Fig. 1).1,2 Refinements in image processing have allowed improved resolution of cardiac structures. Consequently, it is now possible to measure the actual visualized thickness of the ventricular septum and other chamber dimensions as defined by the actual tissue–blood interface, rather than the distance between the leading edge echoes which had previously been recommended.5 Use of 2-D echo-derived linear dimensions overcomes the common problem of oblique parasternal images resulting in overestimation of cavity and wall dimensions from M mode. If manual calibration of images is required, 6 cm or larger distances should be used to minimize errors due to imprecise placement of calibration points.
Measurement of left ventricular end-diastolic diameter (EDD) and end-systolic diameter (ESD) from M-mode, guided by a parasternal short axis image (upper left) to optimize medial-lateral beam orientation.
In order to obtain volumetric measurements the most important views for 2-D quantitation are the mid-papillary short-axis view and the apical four- and two-chamber views. Volumetric measurements require manual tracing of the endocardial border. The papillary muscles should be excluded from the cavity in the tracing. Accurate measurements require optimal visualization of the endocardial border in order to minimize the need for extrapolation. It is recommended that the basal border of the LV cavity area be delineated by a straight line connecting the mitral valve insertions at the lateral and septal borders of the annulus on the four-chamber view and the anterior and inferior annular borders on the two-chamber view.
End-diastole can be defined at the onset of the QRS, but is preferably defined as the frame following mitral valve closure or the frame in the cardiac cycle in which the cardiac dimension is largest. In sinus rhythm, this follows atrial contraction. End-systole is best defined as the frame preceding mitral valve opening or the time in the cardiac cycle in which the cardiac dimension is smallest in a normal heart. In the two-chamber view, mitral valve motion is not always clearly discernible and the frames with the largest and smallest volumes should be identified as end-diastole and end-systole, respectively.
The recommended TEE views for measurement of LV diameters are the mid esophageal two-chamber view (Fig. 2) and the transgastric (TG) two- chamber views (Fig. 3). LV diameters are measured from the endocardium of the anterior wall to the endocardium of the inferior wall in a line perpendicular to the long-axis of the ventricle at the junction of the basal and middle thirds of the long-axis. The recommended TEE view for measurement of LV wall thicknesses is the TG mid short-axis view (Fig. 4). With TEE, the long-axis dimension of the LV is often foreshortened in the mid-esophageal four-chamber and long-axis views; therefore the mid-esophageal two-chamber view is preferred for this measurement. Care must be made to avoid foreshortening TEE views, by recording the image plane which shows the maximum obtainable chamber size, finding the angle for diameter measurement which is perpendicular to the long-axis of that chamber, then measuring the maximum obtainable short-axis diameter.
Transesophageal echo measurements of left ventricular minor axis diameter (LVD) from the trans-gastric two-chamber view of the left ventricle, usually best imaged at an angle of approximately 90–110 degrees after optimizing the maximum obtainable LV size by adjustment of medial-lateral rotation.
Transesophageal echo measurements of wall thickness of the left ventricular septal wall (SWT) and the posterior wall (PWT), from the trans-gastric short axis view of the left ventricle, at the papillary muscle level, usually best imaged at angle of approximately 0–30 degrees.
Calculation of left ventricular mass
In clinical practice, LV chamber dimensions are commonly used to derive measures of LV systolic function, whereas in epidemiologic studies and treatment trials, the single largest application of echocardiography has been the estimation of LV mass in populations and its change with antihypertensive therapy.13,19 All LV mass algorithms, whether utilizing M-mode, 2-D or 3-D echocardiographic measurements, are based upon subtraction of the LV cavity volume from the volume enclosed by the LV epicardium to obtain LV muscle or “shell” volume. This shell volume is then converted to mass by multiplying by myocardial density. Hence, quantitation of LV mass requires accurate identification of interfaces between the cardiac blood pool and endocardium and between epicardium and pericardium.
To date, most LV mass calculations have been made using linear measurements derived from 2-D-targeted M-mode or, more recently, from 2-D linear LV measurements.20 The ASE recommended formula for estimation of LV mass from LV linear dimensions (validated with necropsy r=0.90, p<0.00121) is based on modeling the LV as a prolate ellipse of revolution:
This formula is appropriate for evaluating patients without major distortions of LV geometry, e.g., patients with hypertension. Since this formula requires cubing primary measurements, even small errors in these measurements are magnified. Calculation of relative wall thickness (RWT) by the formula, (2×PWTd)/LVIDd, permits categorization of an increase in LV mass as either concentric (RWT≥0.42) or eccentric (RWT≤0.42) hypertrophy and allows identification of concentric remodeling (normal LV mass with increased RWT) (Fig. 5).22
Comparison of relative wall thickness (RWT). Patients with normal LV mass can have either concentric remodeling (normal LV mass with increased RWT>0.42) or normal (RWT≤0.42) and normal LV mass. Patients with increased LV mass can have either concentric (RWT>0.42) or eccentric (RWT≤0.42) hypertrophy. These LV mass measurements are based on linear measurements.
The most commonly employed 2-D methods for measuring LV mass are based on the area–length formula and the truncated ellipsoid model, as described in detail in the 1989 ASE document on LV quantitation.2 Both methods were validated in the early 1980s in animal models and by comparing pre-morbid echocardiograms with measured LV weight at autopsy in humans. Both methods rely on measurements of myocardial area at the mid-papillary muscle level. The epicardium is traced to obtain the total area (A1) and the endocardium is traced to obtain the cavity area (A2). Myocardial area (Am) is computed as the difference: Am=A1−A2. Assuming a circular area, the radius is computed (b=A2/π) and a mean wall thickness (t) derived (Fig. 6). Left ventricular mass can be calculated by one of the two formulae shown in Fig. 6. In the presence of extensive regional wall motion abnormalities (e.g. myocardial infarction), the biplane Simpson's method may be used, although this method is dependent on adequate endocardial and epicardial definition of the LV which often is challenging from this window. Most laboratories obtain the measurement at end-diastole and exclude the papillary muscles in tracing the myocardial area.
Two methods for estimating LV mass based on the area–length (AL) formula and the truncated ellipsoid (TE) formula, from short axis (left) and apical four-chamber (right) 2-D echo views. A1=total LV area; A2=LV cavity area; Am=myocardial area, a is the long or semi-major axis from widest minor axis radius to apex, b is the short-axis radius (back calculated from the short-axis cavity area) and d is the truncated semi-major axis from widest short-axis diameter to mitral anulus plane. Assuming a circular area, the radius (b) is computed and mean wall thickness (t) derived from the short-axis epicardial and cavity areas. See text for explanation.
TEE evaluation of LV mass is also highly accurate, but has minor systematic differences in LV posterior wall thickness. In particular LV mass derived from TEE wall thickness measurements is higher by an average of 6g/m2.8
Left ventricular systolic function: linear and volumetric measurement
Many echocardiographic laboratories rely on M-mode measurements or linear dimensions derived from the two-dimensional image for quantification. Linear measurements from M-mode and 2-D images have proven to be reproducible with low intra- and inter-observer variability.20,23–26 Although linear measures of LV function are problematic when there is a marked regional difference in function, in patients with uncomplicated hypertension, obesity or valvular diseases, such regional differences are rare in the absence of clinically recognized myocardial infarction. Hence fractional shortening and its relationship to end-systolic stress often provide useful information in clinical studies.27 The previously used Teichholz or Quinones methods of calculating LV ejection fraction from LV linear dimensions may result in inaccuracies due to the geometric assumptions required to convert a linear measurement to a 3-D volume.28,29 Accordingly, the use of linear measurements to calculate LV EF is not recommended for clinic practice.
Contraction of muscle fibers in the LV midwall may better reflect intrinsic contractility than contraction of fibers at the endocardium. Calculation of midwall, rather than endocardial fractional shortening is particularly useful in revealing underlying systolic dysfunction in the setting of concentric hypertrophy.30 Mid-wall fractional shortening (MWFS) may be computed from linear measures of diastolic and systolic cavity sizes and wall thicknesses based on mathematical models,30,31 according to the following formulas:
The most commonly used 2-D measurement for volume measurements is the biplane method of discs (modified Simpson's rule) and is the currently recommended method of choice by consensus of this committee (Fig. 7). The principle underlying this method is that the total LV volume is calculated from the summation of a stack of elliptical discs. The height of each disc is calculated as a fraction (usually one-twentieth) of the LV long axis based on the longer of the two lengths from the two- and four-chamber views. The cross-sectional area of the disk is based on the two diameters obtained from the two- and four-chamber views. When two adequate orthogonal views are not available, a single plane can be used and the area of the disc is then assumed to be circular. The limitations of using a single plane are greatest when extensive wall motion abnormalities are present.
2-D measurements for volume calculations using the biplane method of discs (modified Simpson's rule), in the apical four-chamber (A4C) and apical two-chamber (A2C) views at end diastole (LV EDD) and at end-systole (LV ESD). The papillary muscles should be excluded from the cavity in the tracing.
An alternative method to calculate LV volumes when apical endocardial definition precludes accurate tracing is the area–length method where the LV is assumed to be bullet-shaped (Fig. 6). The mid LV cross-sectional area is computed by planimetry in the parasternal short-axis view and the length of the ventricle taken from the mid point of the annulus to the apex in the apical four-chamber view. These measurements are repeated at end-diastole and end-systole and the volume is computed according to the formula: volume=[5(area)(length)]÷6. The most widely used parameter for indexing volumes is the body surface area (BSA) in m2.
The end-diastolic and end-systolic volumes (EDV, ESV) are calculated by either of the two methods described above and the ejection fraction is calculated as follows:
Partition values for recognizing depressed LV systolic function in Table 6 follow the conventional practice of using the same cut-offs in women and men; however, emerging echocardiographic and MRI data suggests that LV ejection fraction and other indices are somewhat higher in apparently normal women than in men.32,33 Quantitation of LV volumes using TEE is challenging due to difficulties in obtaining a non-foreshortened LV cavity from the esophageal approach. However when carefully acquired, direct comparisons between TEE and TTE volumes and ejection fraction have shown minor or no significant differences.8,9
Reference values for left ventricular measurements (Tables 4–6)
Reference values for LV linear dimensions have been obtained from an ethnically diverse population of 510 normal-weight, normotensive, non-diabetic white, African-American and American-Indian adults without recognized cardiovascular disease (unpublished data). The populations from which these data has been derived have been described in detail previously.20,34–36 Reference values for volumetric measurements have also been obtained in a normal adult population.37
Reference limits and values and partition values of left ventricular function
Endocardial fractional shortening (%)
Midwall fractional shortening (%)
Ejection fraction (%)
Values in bold are recommended and best validated.
Normal values for LV mass differ between men and women even when indexed for body surface area (Table 4). The best method for normalizing LV mass measurements in adults is still debated. While body surface area (BSA) has been most often employed in clinical trials, this method will underestimate the prevalence of LV hypertrophy in overweight and obese individuals. The ability to detect LV hypertrophy related to obesity as well as to cardiovascular diseases is enhanced by indexing LV mass for the power of its allometric or growth relation with height (height2.7). Data are inconclusive as to whether such indexing of LV mass may improve or attenuate prediction of cardiovascular events. Of note, the reference limits for LV mass in Table 4 are lower than those published in some previous echocardiographic studies, yet are virtually identical to those based on direct necropsy measurement and cutoff values used in clinical trials.19,20,36,38,39 Although some prior studies have suggested racial differences in LV mass measurement, the consensus of the literature available indicates that no significant differences exist between clinically normal black and white subjects. In contrast, a recent study has shown racial-ethnic differences in left ventricular structure in hypertensive adults.40 Although the sensitivity, specificity and predictive value of LV wall thickness measurements for detection of LV hypertrophy are lower than for calculated LV mass, it is sometimes easiest in clinical practice to identify LV hypertrophy by measuring an increased LV posterior and septal thickness.41
The use of LV mass in children is complicated by the need for indexing the measurement relative to patient body size. The intent of indexing is to account for normal childhood growth of lean body mass without discounting the pathologic effects of overweight and obesity. In this way, an indexed LV mass measurement in early childhood can be directly compared to a subsequent measurement during adolescence and adulthood. Dividing LV mass by height raised to a power of 2.5–3.0 is the most widely accepted indexing method in older children and adolescents since it correlates best to indexing LV mass to lean body mass.42 Currently an intermediate value of 2.7 is generally used.43,44 In younger children (<8years), the most ideal indexing factor remains an area of research, but height raised to a power of 2.0 appears to be the most appropriate.45
Three-dimensional assessment of volume and mass
Three-dimensional chamber volume and mass are incompletely characterized by one-dimensional or two-dimensional approaches, which are based on geometric assumptions. While these inaccuracies have been considered inevitable and of minor clinical importance in the past, in most situations accurate measurements are required, particularly when following the course of a disease with serial examinations. Over the last decade, several three-dimensional echocardiographic techniques became available to measure LV volumes and mass.46–59 These can be conceptually divided into techniques, which are based on off-line reconstruction from a set of 2-D cross-sections, or on-line data acquisition using a matrix array transducer, also known as real-time 3-D echocardiography. After acquisition of the raw data, calculation of LV volumes and mass requires identification of endocardial borders (and for mass epicardial border) using manual or semi-automated algorithms. These borders are then processed to calculate the cavity or myocardial volume by summation of discs54,56 or other methods.46–48
Regardless of which acquisition or analysis method is used, 3-D echocardiography does not rely on geometric assumptions for volume/mass calculations and is not subject to plane positioning errors, which can lead to chamber foreshortening. Studies comparing 3-D echocardiographic LV volumes or mass to other gold-standards such as magnetic resonance imaging, have confirmed 3-D echocardiography to be accurate. Compared to magnetic resonance data, LV and RV volumes calculated from 3-D echocardiography showed significantly better agreement (smaller bias), lower scatter and lower intra- and inter-observer variability than 2-D echocardiography.46,54,57,60 The superiority of 3-D echocardiographic LV mass calculations over values calculated from M-mode derived or 2-D echocardiography has been convincingly shown.55,57,59 Right ventricular volume and mass have also been measured by 3-D echocardiography with good agreement with magnetic resonance data.58,61 Current limitations include the requirement of regular rhythm, relative inferior image quality of real-time 3-D echocardiography compared to 2-D images, and the time necessary for off-line data analysis. However, the greater number of acquired data points, the lack of geometric assumptions, increasingly sophisticated 3-D image and measurements solutions offset these limitations.
Regional left ventricular function
In 1989, the American Society of Echocardiography recommended a 16 segment model for LV segmentation.2 This model consists of six segments at both basal and mid-ventricular levels and four segments at the apex (Fig. 8). The attachment of the right ventricular wall to the left ventricle defines the septum, which is divided at basal and mid LV levels into anteroseptum and inferoseptum. Continuing counterclockwise, the remaining segments at both basal and mid ventricular levels are labeled as inferior, inferolateral, anterolateral and anterior. The apex includes septal, inferior, lateral, and anterior segments. This model has become widely utilized in echocardiography. In contrast, nuclear perfusion imaging, cardiovascular magnetic resonance and cardiac computed tomography have commonly used a larger number of segments.
Segmental analysis of LV walls based on schematic views, in a parasternal short and long axis orientation, at three different levels. The “apex segments” are usually visualized from apical four-chamber, apical two- and three-chamber views. The apical cap can only be appreciated on some contrast studies. A 16 segment model can be used, without the apical cap, as described in an ASE 1989 document.2 A 17 segment model, including the apical cap, has been suggested by the American Heart Association Writing Group on Myocardial Segmentation and Registration for Cardiac Imaging.62
In 2002, the American Heart Association Writing Group on Myocardial Segmentation and Registration for Cardiac Imaging, in an attempt to establish segmentation standards applicable to all types of imaging, recommended a 17-segment model (Fig. 8).62 This differs from the previous 16-segment model predominantly by the addition of a 17th segment, the “apical cap.” The apical cap is the segment beyond the end of the LV cavity. Refinements in echocardiographic imaging, including harmonics and contrast imaging are believed to permit improved imaging of the apex. Either model is practical for clinical application yet sufficiently detailed for semi-quantitative analysis. The 17-segment model should be predominantly used for myocardial perfusion studies or anytime efforts are made to compare between imaging modalities. The 16-segment model is appropriate for studies assessing wall motion abnormalities as the tip of the normal apex (segment 17) does not move.
The mass and size of the myocardium as assessed at autopsy is the basis for determining the distribution of segments. Sectioned into basal, mid ventricular and apical thirds, perpendicular to the LV long-axis, with the mid ventricular third defined by the papillary muscles, the measured myocardial mass in adults without cardiac disease was 43% for the base, 36% for the mid cavity and 21% for the apex.63 The 16-segment model closely approximates this, creating a distribution of 37.5% for both the basal and mid portions and 25% for the apical portion. The 17-segment model creates a distribution of 35.3%, 35.3% and 29.4% for the basal, mid and apical portions (including the apical cap) of the heart, respectively.
Variability exists in the coronary artery blood supply to myocardial segments. Nevertheless, the segments are usually attributed to the three major coronary arteries are shown in the TTE±distributions of Fig. 9.62
Artist's diagram showing the position of three long axis views and one short axis view of the left ventricle, showing the typical distributions of the right coronary artery (RCA), the left anterior descending (LAD), and the circumflex (Cx) coronary arteries. The arterial distribution varies between patients. Some segments have variable coronary perfusion.
Since the 1970s, echocardiography has been used for the evaluation of LV regional wall motion during infarction and ischemia.64–66 It is recognized that regional myocardial blood flow and regional LV systolic function are related over a wide range of blood flows.67 Although regional wall motion abnormalities at rest may not be seen until the luminal diameter stenosis exceeds 85%, with exercise, a coronary lesion of 50% can result in regional dysfunction. It is recognized that echocardiography can overestimate the amount of ischemic or infarcted myocardium, as wall motion of adjacent regions may be affected by tethering, disturbance of regional loading conditions and stunning.68 Therefore, wall thickening as well as motion should be considered. Moreover, it should be remembered that regional wall motion abnormalities may occur in the absence of coronary artery disease.
It is recommended that each segment be analyzed individually and scored on the basis of its motion and systolic thickening. Ideally, the function of each segment should be confirmed in multiple views. A segment which is normal or hyperkinetic is assigned a score of 1, hypokinesis=2, akinesis (negligible thickening)=3, dyskinesis (paradoxical systolic motion)=4, and aneurysmal (diastolic deformation)=5.1 Wall motion score index can be derived as a sum of all scores divided by the number of segments visualized.
Assessment of LV remodeling and the use of echocardiography in clinical trials
Left ventricular remodeling describes the process by which the heart changes its size, geometry and function over time. Quantitative 2-D transthoracic echocardiography enables characterization of LV remodeling that occurs in normal subjects and in a variety of heart diseases. LV remodeling may be physiological when the heart increases in size but maintains normal function during growth, physical training and pregnancy. Several studies have demonstrated that both isometric and isotonic exercise cause remodeling of the left and right ventricular chamber sizes and wall thicknesses.69–73 These changes in the highly-trained, elite “athlete hearts” are directly related to the type and duration of exercise and have been characterized echocardiographically. With isometric exercise, a disproportionate increase occurs in LV mass compared to the increase in LV diastolic volume resulting in significantly greater wall thickness to cavity size ratio (h/R ratio) than take place in normal non-athletic subjects with no change in ejection phase indices of LV contractile function.69–73 This physiologic hypertrophic remodeling of the athlete heart is reversible with cessation of endurance training and is related to the total increase in lean body weight70 and triggered by enhanced cardiac sympathetic activity.74 Remodeling may be compensatory in chronic pressure overload due to systemic hypertension or aortic stenosis resulting in concentric hypertrophy (increased wall thickness, normal cavity volume and preserved ejection fraction) (Fig. 5). Compensatory LV remodeling also occurs in chronic volume overload associated with mitral or aortic regurgitation, which induces a ventricular architecture characterized by eccentric hypertrophy, LV chamber dilatation and initially normal contractile function. Pressure and volume overload may remain compensated by appropriate hypertrophy which normalizes wall stress such that hemodynamics and ejection fraction remain stable long term. However, in some patients chronically increased afterload cannot be normalized indefinitely and the remodeling process becomes pathologic.
Transition to pathologic remodeling is heralded by progressive ventricular dilatation, distortion of cavity shape and disruption of the normal geometry of the mitral annulus and subvalvular apparatus resulting in mitral regurgitation. The additional volume load from mitral regurgitation escalates the deterioration in systolic function and development of heart failure. LV dilatation begets mitral regurgitation and mitral regurgitation begets further LV dilatation, progressive remodeling and contractile dysfunction.
Changes in LV size and geometry due to hypertension (Fig. 5) reflect the dominant underlying hemodynamic alterations associated with blood pressure elevation.22,75 The pressure-overload pattern of concentric hypertrophy is uncommon in otherwise healthy hypertensive individuals and is associated with high systolic blood pressure and high peripheral resistance. In contrast, eccentric LV hypertrophy is associated with normal peripheral resistance but high cardiac index consistent with excess circulating blood volume. Concentric remodeling (normal LV mass with increased relative wall thickness) is characterized by high peripheral resistance, low cardiac index, and increased arterial stiffness.76,77
A unique form of remodeling occurs following myocardial infarction due to the abrupt loss of contracting myocytes.22,78 Early expansion of the infarct zone is associated with early LV dilatation as the increased regional wall stress is redistributed to preserve stroke volume. The extent of early and late post-infarction remodeling is determined by a number of factors, including size and location of infarction, activation of the sympathetic nervous system, and up-regulation of the renin/angiotensin/aldosterone system and natriuretic peptides. Between one-half and one-third of post-infarction patients experience progressive dilatation79,80 with distortion of ventricular geometry and secondary mitral regurgitation. Mitral regurgitation further increases the propensity for deterioration in LV function and development of congestive heart failure. Pathologic LV remodeling is the final common pathway to heart failure, whether the initial stimulus is chronic pressure or chronic volume overload, genetically determined cardiomyopathy or myocardial infarction. The etiology of LV dysfunction in approximately two thirds of the 4.9 million patients with heart failure in the USA is coronary artery disease.81
While LV remodeling in patients with chronic systemic hypertension, chronic valvular regurgitation and primary cardiomyopathies has been described, the transition to heart failure is less well known because the time course is so prolonged. By contrast, the time course from myocardial infarction to heart failure is shorter and has been clearly documented.
The traditional quantitative echocardiographic measurements recommended to evaluate LV remodeling included estimates of LV volumes either from biplane or single plane images as advocated by the American Society of Echocardiography. Although biplane and single-plane volume estimations are not interchangeable, both estimates are equally sensitive for detecting time-dependent LV remodeling and deteriorating contractile function.77 LV volumes and derived ejection fraction have been demonstrated to predict adverse cardiovascular events at follow-up, including death, recurrent infarction, heart failure, ventricular arrhythmias and mitral regurgitation in numerous post-infarction and heart failure trials.78–81 This committee recommends the use of quantitative estimation of LV volumes, LVEF, LV mass and shape as (described in the respective sections above) to follow LV remodeling induced by physiologic and pathologic stimuli. In addition, these measurements provide prognostic information incremental to that of baseline clinical demographics.
Quantification of the RV and RVOT
The normal right ventricle (RV) is a complex crescent-shaped structure wrapped around the left ventricle and is incompletely visualized in any single 2-D echocardiographic view. Thus, accurate assessment of RV morphology and function requires integration of multiple echocardiographic views, including the parasternal long and short-axis views, the RV inflow view, the apical four-chamber and the subcostal views. While multiple methods for quantitative echocardiographic RV assessment have been described, in clinical practice assessment of RV structure and function remains mostly qualitative. Nevertheless, numerous studies have recently emphasized the importance of RV function in the prognosis of a variety of cardio-pulmonary diseases suggesting that more routine quantification of RV function is warranted under most clinical circumstances.
Compared to the left ventricle, the right ventricle is a thin-walled structure under normal conditions. The normal right ventricle is accustomed to a low pulmonary resistance and hence low afterload; thus, normal RV pressure is low and right ventricular compliance high. The right ventricle is therefore sensitive to changes in afterload, and alterations in RV size and function are indicators of increased pulmonary vascular resistance and load transmitted from the left-sided chambers. Elevations in RV afterload in adults are manifested acutely by RV dilatation and chronically by concentric RV hypertrophy. In addition, intrinsic RV abnormalities, such as infarction or RV dysplasia82 can cause RV dilatation or reduced RV wall thickness. Thus, assessment of RV size and wall thickness is integral to the assessment of RV function.
Right ventricular free wall thickness, normally less than 0.5cm, is measured using either M-mode or 2-D imaging. Although RV free wall thickness can be assessed from the apical and parasternal long-axis views, the subcostal view measured at the peak of the R wave at the level of the tricuspid valve chordae tendinae provides less variation and closely correlates with RV peak systolic pressure (Fig. 10).75 Care must be taken to avoid over measurement due to the presence of epicardial fat deposition as well as coarse trabeculations within the right ventricle.
Methods of measuring right ventricular wall thickness (arrows) from an M-mode echo (left) and a subcostal transthoracic echo (right).
Qualitative assessment of RV size is easily accomplished from the apical four-chamber view (Fig. 11). In this view, RV area or mid cavity diameter should be smaller than that of the left ventricle. In cases of moderate enlargement, the RV cavity area is similar to that of the LV and it may share the apex of the heart. As RV dilation progresses, the cavity area will exceed that of the LV and the RV will be “apex forming”. Quantitative assessment of RV size is also best performed in the apical four-chamber view. Care must be taken to obtain a true non-foreshortened apical four-chamber view, oriented to obtain the maximum RV dimension, prior to making these measurements. Measurement of the mid-cavity and basal RV diameter in the apical four-chamber view at end-diastole is a simple method to quantify RV size (Fig. 11). In addition, RV longitudinal diameter can be measured from this view. Table 7 provides normal RV dimensions from the apical four-chamber view.76,80,83
Reference limits and partition values of right ventricular and pulmonary artery size76
Basal RV diameter (RVD#1) (cm)
Mid RV diameter (RVD#2) (cm)
Base-to-apex length (RVD#3) (cm)
Above aortic valve (RVOT#1) (cm)
Above pulmonic valve (RVOT#2) (cm)
Below pulmonic valve (PA#1) (cm)
Right ventricular size may be assessed may be assessed with TEE in the mid-esophageal four- chamber view (Fig. 12). The mid-esophageal four- chamber view, which generally parallels what is obtainable from the apical four-chamber view, should originate at the mid-left atrial level and pass through the LV apex with the multiplane angle adjusted to maximize the tricuspid annulus diameter, usually between 10 and 20 degrees.
Transesophageal echo measurements of right ventricular diameters from the mid-esophageal four-chamber view, best imaged after optimizing the maximum obtainable RV size by varying angles from approximately 0–20 degrees.
Right ventricular systolic function is generally estimated qualitatively in clinical practice. When the evaluation is based on a qualitative assessment, the displacement of the tricuspid annulus should be observed. In systole, the tricuspid annulus will normally descend toward the apex 1.5–2.0cm. Tricuspid annular excursion of less than 1.5cm has been associated with poor prognosis in a variety of cardiovascular diseases.84 Although a number of techniques exist for accurate quantitation, direct calculation of RV volumes and ejection fraction remains problematic given the complex geometry of the right ventricle and the lack of standard methods for assessing RV volumes. Nevertheless, a number of echocardiographic techniques may be used to assess RV function. Right ventricular fractional area change (FAC) measured in the apical four-chamber view is a simple method for assessment of RV function that has correlated with RV ejection fractions measured by MRI (r=0.88) and has been related to outcome in a number of disease states.81,85 Normal RV areas and fractional area changes are shown in Table 8. Additional assessment of the RV systolic function includes tissue imaging of tricuspid annular velocity or right ventricular index of myocardial performance (Tei Index).86
Reference limits and partition values of right ventricular size and function as measured in the apical four-chamber view 80
RV diastolic area (cm2)
RV systolic area (cm2)
RV fractional area change (%)
The RV outflow tract (RVOT) extends from the anterosuperior aspect of the right ventricle to the pulmonary artery, and includes the pulmonary valve. It is best imaged from the parasternal long-axis view angled superiorly, and the parasternal short-axis at the base of the heart. It can additionally be imaged from the subcostal long and transverse windows as well as the apical window. Measurement of the RV outflow tract is most accurate from the parasternal short-axis (Fig. 13) just proximal to the pulmonary valve. Mean RVOT measurements are shown in Table 7.75 With TEE, the mid-esophageal RV inflow-outflow view usually provides the best image of the RVOT just proximal to the pulmonary valve (Fig. 14).
Measurement of the right ventricular outflow tract diameter at the subpulmonary region (RVOT1) and at the pulmonic valve annulus (RVOT2), in the mid-esophageal aortic valve short axis view, using a multiplane angle of approximately 45–70 degrees.
Measurement of the right ventricular outflow tract at the pulmonic valve annulus (RVOT2), and at and main pulmonary artery from the midesophageal RV inflow-outflow view.
Quantification of LA/RA size
The left atrium (LA) fulfills three major physiologic roles that impact on LV filling and performance. The left atrium acts as a contractile pump that delivers 15–30% of the LV filling, as a reservoir that collects pulmonary venous return during ventricular systole and as a conduit for the passage of stored blood from the LA to the LV during early ventricular diastole.87 Increased left atrial size is associated with adverse cardiovascular outcomes.88–90 An increase in atrial size most commonly is related to increased wall tension due to increased filling pressure.91,92 Although increased filling volumes can cause an increase in LA size, the adverse outcomes associated with increased dimension and volume are more strongly associated with increased filling pressure. Relationships exist between increased left atrial size and the incidence of atrial fibrillation and stroke,93–101 risk of overall mortality after MI,102,103 and the risk of death and hospitalization in subjects with dilated cardiomyopathy.104–108 LA enlargement is a marker of both the severity and chronicity of diastolic dysfunction and magnitude of LA pressure elevation.88,91,92
The LA size is measured at the end-ventricular systole when the LA chamber is at its greatest dimension. While recording images for computing LA volume, care should be taken to avoid foreshortening of the LA. The base of the LA should be at its largest size indicating that the imaging plane passes through the maximal short-axis area. The LA length should also be maximized ensuring alignment along the true long-axis of the LA. When performing planimetry the LA, the confluences of the pulmonary veins and LA appendage should be excluded.
With TEE, the LA frequently cannot fit in its entirety into the image sector. Measurements of LA volume from this approach cannot be reliably performed however; LA dimension can be estimated combining measurements from different imaging planes.
LA linear dimension
The LA can be visualized from multiple echocardiographic views from which several potential LA dimensions can be measured. However, the large volume of prior clinical and research work used the M-mode or 2-D derived anteroposterior (AP) linear dimension obtained from the parasternal long-axis view making this the standard for linear LA measurement (Fig. 15).93,95,96,98,104,105 The convention for M-mode measurement is to measure from the leading edge of the posterior aortic wall to the leading edge of the posterior LA wall. However, to avoid the variable extent of space between the LA and aortic root, the trailing edge of the posterior aortic is recommended.
Measurement of left atrial diameter (LAD) from M-mode, guided by a parasternal short axis image (upper right) at the level of the aortic valve. This linear method is not recommended.
Although these linear measurements have been shown to correlate with angiographic measurements and have been widely used in clinical practice and research, they inaccurately represent true LA size.109,110 Evaluation of the LA in the AP dimension assumes that a consistent relationship is maintained between the AP dimension and all other LA dimensions as the atrium enlarges, which is often not the case.111,112 Expansion of the left atrium in the AP dimension may be constrained by the thoracic cavity between the sternum and the spine. Predominant enlargement in the superior-inferior and medial-lateral dimensions will alter LA geometry such that the AP dimension may not be representative of LA size. For these reasons, AP linear dimensions of the left atrium as the sole measure of left atrial size may be misleading and should be accompanied by left atrial volume determination in both clinical practice and research.
LA volume measurements
When LA size is measured in clinical practice, volume determinations are preferred over linear dimensions because they allow accurate assessment of the asymmetric remodeling of the LA chamber.111 In addition, the strength of the relationship between cardiovascular disease is stronger for LA volume than for LA linear dimensions.97,113 Echocardiographic measures of LA volume have been compared with cine-computed tomography, biplane contrast ventriculography and MRI.109,114–116 These studies have shown either good agreement or a tendency for echocardiographic measurements to underestimate comparative LA volumes.
The simplest method for estimating LA volume is the cube formula, which assumes that the LA volume is that of a sphere with a diameter equal to the LA antero-posterior dimension. However, this method has proven to be inferior to other volume techniques.109,111,117 Left atrial volumes are best calculated using either an ellipsoid model or Simpson's rule.88,89,97,101,102,109–111,115–117
The ellipsoid model assumes that the LA can be adequately represented as a prolate ellipse with a volume of 4π/3(L/2)(D1/2)(D2/2), where L is the long-axis (ellipsoid) and D1 and D2 are orthogonal short-axis dimensions. LA volume can be estimated using this biplane dimension-length formula by substituting the LA antero-posterior diameter acquired from the parasternal long-axis as D1, LA medial-lateral dimension from the parasternal short-axis as D2 and the LA long-axis from the apical four-chamber for L.117–119 Simplified methods using non-orthogonal linear measurements for estimation of LA volume have been proposed.113 Volume determined using linear dimensions is very dependent on careful selection of the location and direction of the minor axis dimensions and has been shown to significantly underestimate LA volume.117
In order to estimate the LA minor axis dimension of the ellipsoid more reliably, the long-axis LA areas can be traced and a composite dimension derived. This dimension takes into account the entire LA border, rather than a single linear measurement. When long-axis-area is substituted for minor axis dimension, the biplane area–length formula is used: 8(A1)(A2)/3π(L), where A1 and A2 represent the maximal planimetered LA area acquired from the apical four- and two-chamber-views, respectively. The length (L) remains the LA long-axis length determined as the distance of the perpendicular line measured from the middle of the plane of the mitral annulus to the superior aspect of the left atrium (Fig. 16). In the area–length formula the length (L) is measured in both the four- and two-chamber views and the shortest of these two L measurements is used in the formula.
Measurement of left atrial volume from the area–length method using the apical four-chamber (A4C) and apical two-chamber (A2C) views at ventricular end-systole (maximum LA size). The length (L) is measured from the back wall to the line across the hinge points of the mitral valve. The shorter (L) from either the A4C or A2C is used in the equation.
The area–length formula can be computed from a single plane, typically the apical four-chamber, by assuming A1=A2, such that volume=8(A1)2/3π(L).120 However, this method makes geometric assumptions that may be inaccurate. In older subjects the diaphragm lifts the cardiac apex upward which increases the angle between ventricle and atrium. Thus the apical four-chamber view will commonly intersect the atria tangentially in older subjects and result in underestimation of volume using a single plane technique. Since the majority of prior research and clinical studies have used the biplane area–length formula, it is the recommended ellipsoid method (Figs. 15 and 16).
LA volume may also be measured using Simpson's rule, similar to its application for LV measurements, which states that the volume of a geometrical figure can be calculated from the sum of the volumes of smaller figures of similar shape. Most commonly, Simpson's algorithm divides the LA into a series of stacked oval disks whose height is h and whose orthogonal minor and major axes are D1 and D2 (method of disks). The volume of the entire left atrium can be derived from the sum of the volume of the individual disks. Volume=π/4(h)∑(D1)(D2). The formula is integrated with the aid of a computer and the calculated volume provided by the software package online (Fig. 17).
Measurement of left atrial volume from the biplane method of discs (modified Simpson's rule), using the apical four-chamber (A4C) and apical two-chamber (A2C) views at ventricular end-systole (maximum LA size).
The use of the Simpson's method in this way requires the input of biplane LA planimetry to derive the diameters. Optimal contours should be obtained orthogonally around the long-axis of the left atrium using TTE apical views. Care should be taken to exclude the pulmonary veins from the LA tracing. The inferior border should be represented by the plane of the mitral annulus. A single plane method of disks could be used to estimate LA volume by assuming the stacked disks are circular V=π/4(h)∑(D1).2 However, as noted above, this makes the assumption that the LA width in the apical two- and four-chamber are identical, which is often not the case and therefore this formula is not preferred.
Three-dimensional echocardiography should provide the most accurate evaluation of LA volume and has shown promise, however to date no consensus exists on the specific method that should be used for data acquisition and there is no comparison with established normal values.121–123
Normal values of LA measurements
The non-indexed LA linear measurements are taken from a Framingham Heart Study cohort of 1099 subjects between the ages of 20 and 45years old who were not obese, were of average height and were without cardiovascular disease (Table 9).11 Slightly higher values have been reported in a cohort of 767 subjects without cardiovascular disease in which obesity and height were not exclusion criteria.113 Both body size and aging have been noted to influence LA size.10,87,113 There are also gender differences in LA size, however, these are nearly completely accounted for by variation in body size.87,113,120,124 The influence of subject size on LA size is typically corrected by indexing to some measure of body size. In fact, from childhood onward the indexed atrial volume changes very little.125 Several indexing methods have been proposed, such as height, weight, estimated lean body mass and body surface area.10,113 The most commonly used convention, and that recommended by this committee, is indexing LA size by dividing by body surface area.
Reference limits and partition values for left atrial dimensions/volumes
LA diameter (cm)
LA diameter/BSA (cm/m2)
RA minor axis dimension (cm)
RA minor axis dimension /BSA (cm/m2)
LA area (cm2)
LA volume (ml)
LA volume/BSA (ml/m2)
Values in bold are recommended and best validated.
Normal indexed LA volume has been determined using the preferred biplane techniques (area–length or method of disks) in a number of studies involving several hundred patients to be 22±6ml/m2.88,120,126,127 Absolute LA volume has also been reported however in clinical practice indexing to body surface area accounts for variations in body size and should therefore be used. As cardiac risk and LA size are closely linked, more importantly than simply characterizing the degree of LA enlargement, normal reference values for LA volume allow prediction of cardiac risk. There are now multiple peer reviewed articles which validate the progressive increase in risk associated with having LA volumes greater than these normative values.89,97,99–103,106–108,128 Consequently, indexed LA volume measurements should become a routine laboratory measure since it reflects the burden and chronicity of elevated LV filling pressure and is a strong predictor of outcome.
Much less research and clinical data are available on quantifying right atrial size. Although the RA can be assessed from many different views, quantification of RA size is most commonly performed from the apical four-chamber view. The minor axis dimension should be taken in a plane perpendicular to the long-axis of the RA and extends from the lateral border of the RA to the interatrial septum. Normative values for the RA minor axis are shown in Table 9.80,129 Although RA dimension may vary by gender, no separate reference values for male and females can be recommended at this time.
Although, limited data are available for RA volumes, assessment of RA volumes would be more robust and accurate for determination of RA size than linear dimensions. As there are no standard orthogonal RA views to use an apical biplane calculation, the single plane area–length and method of discs formulae have been applied to RA volume determination in several small studies.120,130,131 We believe there is too little peer reviewed validated literature to recommend normal RA volumetric values at this time. However, limited data on small number of normal subjects revealed that indexed RA volumes are similar to LA normal values in men (21ml/m2) but appear to be slightly smaller in women.120
Quantification of the aorta and IVC
Recordings should be made from the parasternal long-axis acoustic window to visualize the aortic root and proximal ascending aorta. Two-dimensional images should be used to visualize the LV outflow tract and the aortic root should be recorded in different views in varying intercostal spaces and at different distances from the left sternal border. Right parasternal views, recorded with the patient in a right lateral decubitus position are also useful. Measurements are usually taken at: (1) aortic valve annulus (hinge point of aortic leaflets); (2) the maximal diameter in the sinuses of Valsalva; and (3) sinotubular junction (transition between the sinuses of Valsalva and the tubular portion of the ascending aorta).
Views used for measurement should be those that show the largest diameter of the aortic root. When measuring the aortic diameter, it is particularly important, to use the maximum obtainable short-axis diameter measured perpendicular to the long-axis of the vessel in that view. Some experts favor inner edge-to-inner edge techniques to match those used by other methods of imaging the aorta, such as MRI and CT scanning. However the normative data for echocardiography were obtained using the leading edge technique (Fig. 18). Advances in ultrasound instrumentation which have resulted in improved image resolution should minimize the difference between these measurement methods.
Measurement of aortic root diameters at the aortic valve annulus (AV ann) level, the sinuses of Valsalva (Sinus Val), and the Sino-tubular junction (ST J×n) from the mid-esophageal long axis view of the aortic valve, usually at an angle of approximately 110–150 degrees. The annulus is measured by convention at the base of the aortic leaflets. Although leading edge to leading edge technique is demonstrated for the sinuses of Valsalva and sinotubular junction, some prefer the inner edge to inner edge method (see text for further discussion).
Reliability of aortic root measurements by this method yielded an intra-class correlation coefficient of 0.79 (p<0.001) in a study of 183 hypertensive patients (unpublished data). Two-dimensional aortic diameter measurements are preferable to M-mode measurements, as cyclic motion of the heart and resultant changes in M-mode cursor location relative to the maximum diameter of the sinuses of Valsalva result in systematic underestimation (by ∼2mm) of aortic diameter by M-mode in comparison to the 2-D aortic diameter.132 The aortic annular diameter is measured between the hinge points of the aortic valve leaflets (inner edge–inner edge) in the parasternal or apical long-axis views that reveal the largest aortic annular diameter with color flow mapping to clarify tissue–blood interfaces if necessary.132
The thoracic aorta can be better imaged using TEE than, as most of it is in the near field of the transducer. The ascending aorta can be seen in long-axis, using the mid-esophageal aortic valve long-axis view at about 130 degrees and the mid-esophageal ascending aorta long-axis view. The short-axis view of the ascending aorta is obtained using the mid-esophageal views at about 45 degrees. For measurements of the descending aorta, short-axis views at about 0 degrees, and long-axis views at about 90 degrees, can be recorded from the level of the diaphragm up to the aortic arch (Fig. 19). The arch itself and origins of two of the great vessels can be seen in most patients. There is a “blind spot” in the upper ascending aorta and the proximal arch that is not seen by TEE due to the interposed tracheal bifurcation.
Measurement of aortic root diameter at the sinuses of Valsava from 2-D parasternal long-axis image. Although leading edge to leading edge technique is shown, some prefer the inner edge to inner edge method (see text for further discussion).
Identification of aortic root dilatation
Aortic root diameter at the sinuses of Valsalva is related most strongly to body surface area and age. Therefore, body surface area may be used to predict aortic root diameter in three age-strata: <20years, 20–40 and >40years, by published equations.132 Aortic root dilatation at the sinuses of Valsalva is defined as an aortic root diameter above the upper limit of the 95% confidence interval of the distribution in a large reference population.132 Aortic dilatation can be easily detected by plotting observed aortic root diameter versus body surface area on previously-published nomograms (Fig. 20).132 Aortic dilatation is strongly associated with the presence and progression of aortic regurgitation133 and with the occurrence of aortic dissection.134 The presence of hypertension appears to have minimal impact on aortic root diameter at the sinuses of Valsalva133,135 but is associated with enlargement of more distal aortic segments.135
95% confidence intervals for aortic root diameter at the sinuses of Valsalva based on body surface area in: children and adolescents (A), adults aged 20–39years (B), and adults aged 40years or more (C).132
Evaluation of the inferior vena cava
Examination of the inferior vena cava (IVC) from the subcostal view should be included as part of the routine TTE examination. It is generally agreed that the diameter of the inferior vena cava should be measured with the patient in the left decubitus position at 1.0–2.0cm from the junction with the right atrium, using the long-axis view. For accuracy, this measurement should be made perpendicular to the IVC long-axis. The diameter of the inferior vena cava decreases in response to inspiration when the negative intrathoracic pressure leads to an increase in right ventricular filling from the systemic veins. The diameter of the IVC and the percent decrease in the diameter during inspiration correlate with right atrial pressure. The relationship has been called the “collapsibility index”.136 Evaluation of the inspiratory response often requires a brief “sniff” as normal inspiration may not elicit this response.
The normal IVC diameter is <1.7cm. There is a 50% decrease in the diameter when the right atrial pressure is normal (0–5mmHg). A dilated IVC (>1.7cm) with normal inspiratory collapse (≥50%) is suggestive of a mildly elevated RA pressure (6–10mmHg). When the inspiratory collapse is <50%, the RA pressure is usually between 10 and 15mmHg. Finally, a dilated IVC without any collapse suggests a markedly increased RA pressure of >15mmHg. In contrast, a small IVC (usually <1.2cm) with spontaneous collapse often is seen in the presence of intravascular volume depletion.137
There are several additional conditions to be considered in evaluating the inferior vena cava. Athletes have been shown to have dilated inferior vena cavae with normal collapsibility index. Studies137,138 have found that the mean IVC diameter in athletes was 2.31±0.46 compared to 1.14±0.13 in aged-matched normals. The highest diameters were seen in highly trained swimmers.
One study showed that a dilated IVC in the mechanically ventilated patient did not always indicate a high right atrial pressure. However, a small IVC (<1.2cm) had a 100% specificity for a RA pressure of less than 10mmHg with a low sensitivity.139 A more recent study suggested that there was a better correlation when the IVC diameter was measured at end-expiration and end-diastole using M-mode echocardiography.140
The use of the inferior vena cava size and dynamics is encouraged for estimation of the right atrial pressure. This estimate should be used in estimation of the pulmonary artery pressure based on the tricuspid regurgitant jet velocity.
The authors wish to thank Harvey Feigenbaum, MD, and Nelson B. Schiller for their careful review and thoughtful comments.
↵* A report from the American Society of Echocardiography's Nomenclature and Standards Committee and the Task Force on Chamber Quantification, developed in conjunction with the American College of Cardiology Echocardiography Committee, the American Heart Association, and the European Association of Echocardiography, a branch of the European Society of Cardiology.
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Roberto M.Lang, MichelleBierig, Richard B.Devereux, Frank A.Flachskampf, ElyseFoster, Patricia A.Pellikka, Michael H.Picard, Mary J.Roman, JamesSeward, JackShanewise, ScottSolomon, Kirk T.Spencer, MartinSt. John Sutton, WilliamStewart
European Heart Journal - Cardiovascular Imaging Mar 2006, 7 (2) 79-108; DOI: 10.1016/j.euje.2005.12.014
Roberto M.Lang, MichelleBierig, Richard B.Devereux, Frank A.Flachskampf, ElyseFoster, Patricia A.Pellikka, Michael H.Picard, Mary J.Roman, JamesSeward, JackShanewise, ScottSolomon, Kirk T.Spencer, MartinSt. John Sutton, WilliamStewartEur J Echocardiogr(2006)7 (2):
79-108DOI: http://dx.doi.org/10.1016/j.euje.2005.12.014First published online: 1 March 2006 (30 pages)