Journal of the American Society of Echocardiography
Review articleClinical applications of strain rate imaging
Section snippets
Measurement of the myocardial strain
Initial measurements of intrinsic myocardial deformation or strain involved tracking the movement of implanted radio-opaque markers (eg, metallic beads) by biplane cineangiography3, 4 or video5 measuring mutual motion and angulation of 3 needles pierced into the myocardial wall, using an electromagnetic inductive technique,6 or by sonomicrometric crystals embedded in the myocardium.7
More recently, strain parameters can be derived noninvasively from either magnetic resonance imaging (MRI)
Myocardial velocity gradient
Myocardial velocity gradient was first described by Fleming et al15 and was originally obtained from slope of linear regression line formed by multiple velocity points (or pixels) across myocardial wall obtained from M-mode Doppler tissue measurements. It was further validated and defined by Uematsu et al16 as (Vendo − Vepi)/L × cos θ. Where Vendo − Vepi is the differential velocity between the endocardium and the epicardium, L is myocardial wall thickness, and θ is the Doppler angle of
Strain echocardiography versus mri strain techniques
The strain derived from SRI differs from that by tagged MRI in the choice of original reference length and planes of measurements. MRI tagging techniques and the M-mode echocardiography measure Lagrangian strain wherein the end-diastolic dimension is used in lieu of the unstressed length as the initial length. Doppler tissue imaging (DTI)-derived strain measures natural strain, which uses instantaneous length as the reference length and is calculated as the temporal integral of the DTI-derived
Image acquisition
Doppler tissue velocity images of 3 to 4 cardiac cycles are acquired at end-expiration. To optimize the tissue velocity signals, the 2-dimensional image is optimized using the gain controls to obtain a clear differentiation between the myocardium and the blood pool. Adjustments are also made in the pulse repetition frequency setting to avoid any aliasing within the myocardial wall (usually 1-2 kHz). The frame rate is maximized using the machine frame rate controls and reducing sector size if
Limitations of strain echocardiography
Similar to any Doppler techniques, SRI signals are highly dependent on angle of insonation. Every effort is made to ensure the tissue direction is less than 30 degrees from the beam direction but this is technically challenging in the apical segments as the angle becomes wider. The narrow sector angle approach on an individual wall obviates some of the above problems. But this approach precludes concurrent comparison of contralateral segments. Also the signal-to-noise ratio of SR measurement
Myocardial strain and sr in control subjects
Strain echocardiography was feasible and reproducible in both children and adults.17, 23, 24, 25, 26 Normally, the longitudinal segmental strain and SR are homogeneous within a left ventricular (LV) wall from the base to apex and are lower than their radial counterparts (by about half) and also the corresponding right ventricular wall. However, the longitudinal SRs in the anterior and septal walls are comparable but higher than those in the anterolateral and inferolateral walls.25 Furthermore,
Ischemic heart disease
From animal experiments, the regional strain values have been validated to correlate with those obtained from sonomicrometry in acute coronary ischemia.22 In canine models, reduced systolic strain appears earlier and, therefore, is more sensitive than Doppler tissue velocity abnormality and semiquantitative visual wall-motion score in acute ischemia.34 Moreover, the radial peak systolic strain of normal myocardium correlates linearly with M-mode ejection fraction calculated with the Teichholz
Future directions
There is increasing evidence that abnormal wall motions during the IVC and IVR are better measures of regional LV function than peak wall motion during systole.55, 62 Segmental IVC motion represents asynchronous and rapid myocardial contraction after ventricular activation but before aortic valve opening, resulting in minor changes in the LV volume and wall thickness. Similar to PST in the IVR period, they are also sensitive to acute myocardial ischemia and correlate with transmural MI. It has
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