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Our laboratory has published the first evidence obtained from fast low-angle-shot cine magnetic resonance imaging (11.7T) studies demonstrating secondary myocyte death after ischemia/reperfusion (IR) of the murine heart. This work provides the first evidence from 11.7-T magnet-assisted pixel-level analysis of the post-IR murine myocardial infarct patches. Changes in function of the remodeling heart were examined in tandem. IR compromised cardiac function and induced LV hypertrophy. During recovery, the IR-induced increase in LV mass was partly offset. IR-induced wall thinning was noted in the anterior aspect of LV and at the diametrically opposite end. Infarct size was observed to be largest on post-IR days 3 and 7. With time (day 28), however, the infarct size was significantly reduced. IR-induced absolute signal-intensity enhancement was highest on post-IR days 3 and 7. As a function of post-IR time, signal-intensity enhancement was attenuated. The threshold of hyperenhanced tissue resulted in delineation of contours that identified necrotic (bona fide infarct) and reversibly injured infarct patches. The study of infarct transmurality indicated that whereas the permanently injured tissue volume remained unchanged, part of the reversibly injured infarct patch recovered in 4 weeks after IR. The approach validated in the current study is powerful in noninvasively monitoring remodeling of the post-IR beating murine myocardium. Antioxid. Redox Signal. 11, 1829–1839.
Reperfusion of the ischemic myocardium is aimed at reducing myocardial dysfunction and improving tissue survival. Reperfusion, however, also poses the threat of tissue injury. Reperfusion injury may be broadly viewed as having two major components: oxidant-induced myocardial tissue damage during the reperfusion process, and progressive tissue damage secondary to the initial insult. We previously reported that acute myocardial infarction is followed by activation of myocyte death in the surviving portion of the heart (33). Remodeling of the heart after ischemia/reperfusion (IR) has a major impact on the survival of patients who have had a myocardial infarction. Understanding of post-IR myocardial remodeling is therefore critically important. The use of noninvasive technologies for such studies allows the repeated measure of the same heart in an experimental setting, providing powerful longitudinal data.
Left ventricular (LV) remodeling, after IR injury, is associated with changes in LV geometry, function, and histologic characteristics that lead to increased risk of heart failure and death (29, 34). Cardiac magnetic resonance imaging (MRI) is a well-established clinical tool commonly used to monitor the infarcted heart (28, 48). MRI enables the noninvasive repeated-measures assessment of the anatomy and physiology of the infarcted heart (19, 24). The advent of high-field-strength, small-bore magnets has enabled high-resolution MRI of the IR rodent heart. Recently, our laboratory published the first evidence obtained from fast low-angle-shot (FLASH) cine MR-imaging studies using an 11.7-T magnet to track secondary myocyte death after IR of the murine heart (33). Myocardial delayed contrast-enhancement imaging represents a versatile tool to assess regional contractile function and myocardial viability (13, 49). An inversion-recovery FLASH sequence, with gadolinium diethylenetriamine pentaacetic acid (Gd-DTPA) as the contrast agent, enables the visualization of IR-induced myocardial infarction (35, 36, 43), as well as of specialized anatomic abnormalities, such as left ventricular apical ballooning (4, 5, 35) in large animals and humans.
Whether delayed hyperenhancement is specifically limited to dysfunctional but viable myocardium or to reversibly injured regions surrounding the acute infarct tissue as well remains unclear (24). In this study, we sought to address this issue by pixel-level analysis of the scar tissue and tandem assessment of heart function. Such analysis of contrast-enhanced inversion-recovery MR images enabled the visualization of hyperenhanced and moderately enhanced patches in murine post-IR heart. The findings reported represent the first evidence from 11.7-T high-field-strength imaging of post-IR myocardial patches. High-resolution images generated by such an approach enabled, for the first time, pixel-level analysis of the IR murine heart at multiple time points after reperfusion. Murine cardiac cine-FLASH sequences were optimized for the measurement of functional parameters such as left ventricular chamber volumes (end-diastolic, end-systolic, stroke), ejection fraction (EF), cardiac output (CO), and LV mass.
Male C57BL/6 adult mice (8-week-old; 24.5±1.5g, mean±SD; Harlan Technologies, IN) were maintained under standard laboratory housing conditions with access to chow and drinking water ad libitum. Ischemia/reperfusion of mice was performed as described earlier (33, 38). In brief, mice were anesthetized by using IP injection of a mixture of ketamine (50mg/ml) and xylazine (10 mg/ml), laid on a warm surgical table, and intubated endotracheally. The mice were ventilated with a device (Harvard Apparatus, Boston, MA) on an air-isoflurane at an appropriate rate and tidal volume. Cardiac electrophysiology was monitored throughout the surgery by using a three-lead ECG setup, and changes were recorded by using PC Powerlab software (AD Instruments). The heart was accessed via left thoracotomy. The left lung was retracted to allow entrance to the pericardium. The left auricle was elevated to expose the coronary left anterior descending (LAD) artery, which was isolated by using 7-0 silk suture with a tapered needle. The suture was tightened over a piece of PE-10 tubing to induce reversible ischemia. LAD was occluded for 60min. After 60min, the suture was released to allow reperfusion in the injured myocardium. On successful reperfusion, the thorax was closed with interrupted 7-0 nylon sutures, as well as the skin incision with 5-0 polypropylene (Prolene) sutures. Throughout the surgery, body temperature was maintained at 36.7±0.5°C by using a heated surgical table and monitored with a rectal thermal probe. The ischemia episode was observed with pale coloration of LV myocardium. Thorax was closed, sutured, and the tracheal tube was disconnected, enabling the mouse to breathe on its own. The animal was then returned to its cage and placed on a heating block set to 37°C. Once the recovery was complete, the animal was returned to the rodent vivarium unit before the MRI experimental procedure. Mice were killed for harvesting the heart tissue after MR imaging, according to a standard protocol. All procedures were approved by the Institutional Laboratory Animal Care and Use Committee (ILACUC) of the Ohio State University.
Baseline MR images (n=5) were obtained 3–5 days before the surgery to allow sufficient time for recovery. After IR surgery, longitudinal repeated measures (post-IR days 3, 7, 14, and 28) were performed for the same mouse over time, such that each mouse served as its own control (paired baseline data). During the MRI, mice were anesthetized by using 1.5% isoflurane in a 95% oxygen and 5% carbon dioxide mixture. Mice were then positioned prone in a custom-manufactured animal holder, as reported previously (33). A custom-designed cradle was used to position the mouse vertically in the magnet. The cradle consisted of a nose-cone, lines for delivering and scavenging anesthetic gases, temperature control and electrocardiography (ECG) leads, and a respiratory monitoring system. Body core temperature was maintained at 37°C by using a specifically designed warm-air blower. ECG coupled with a respiratory gating device (Small Animal Instruments, Inc., Stony Brook, NY) was used for monitoring cardiac and respiratory signals derived from two needles inserted subcutaneously in the front-left and rear-right paws. Mice were secured within the holder by using surgical tape, without compressing their abdomen and chest regions.
MRI was performed by using a Bruker 11.7-T (500MHz) MR microimaging system, which consists of a vertical magnet of bore size 30mm (Bruker Biospin, Ettlingen, Germany). Quadrature-driven birdcage coils with inner diameters of 25mm (Bruker Biospin) were used to transmit/receive the MR signals. In brief, mice were imaged by using a 30-mm proton-imaging probe. Tuning and matching the probe, slice-selective shimming and flip-angle calibration were performed manually before each experiment. Scout imaging for long- and short-axis orientation of the heart, by using a k-space segmented cardiac-triggered and ECG-gated gradient-recalled echo (GRE) fast low-angle shot (FLASH) sequence were performed. Six to seven contingent slices (slice thickness, 1mm) were then acquired in short-axis orientation covering the entire heart. The imaging parameters were as follows: FOV (30×30mm); matrix size, 256×192 (256×256 reconstructed postimaging); TE/TR, 1.43/8ms; NEX, 4 to 6, a gaussian excitation pulse was applied for all chronically failing mouse hearts for the first data set of each normal mouse followed by post–time point assessment experiments.
After the ECG R-wave trigger pulse, images were collected at a frequency of 8 to 10ms, such that 16 images were collected for each cardiac cycle, which lasts approximately 150ms. Breath holding was achieved by acquiring images within short acquisition times, which produced images that were comparatively free of motional artifact from cardiac or respiratory movement. The fast acquisition times also allowed images of the entire thorax to be obtained during a single breath-hold. Controlling the contingent supply of the air–anesthesia mixture also helped minimize respiratory-motion artifacts. Because only a single line of the image can be acquired for K-space filling in each cardiac cycle, data from multiple heartbeats were acquired to form a complete image. Signal averaging was used to enhance the signal-to-noise-ratio (SNR) and to minimize motion artifacts. The MR sequence used consisted of a radiofrequency (RF) pulse that excited the magnetization and gradient waveforms that spatially modulated the magnetization for image acquisition. The repetition time (TR) and echo time (TE) for GRE were chosen to be as short as possible to improve the temporal resolution and to allow more heart phases to be captured during the cardiac cycle. The flip angle of the excitation RF pulse used to acquire the image was 15 degrees. A single-slice acquisition was obtained in 2–3min, depending on relevant imaging parameters (i.e., matrix size and number of signal averages). The imaging time was estimated by multiplying the duration of the R–R interval of the ECG with the image matrix size and the number of signal averages. All animals were killed after MRI, and tissue was collected for histologic studies. All procedures were approved by the Institutional Laboratory Animal Care and Use Committee (ILACUC) of the Ohio State University.
To discriminate between viable and nonviable myocardial tissue in the infarct region, delayed-contrast enhancement (DCE) was performed on a separate group of C57BL/6 mice (n=4; time points: baseline and post-IR days 3 and 28). Gadolinium diethylenetriamine pentaacetic acid (Gd-DTPA; IP injection, 0.1–0.2mmol/kg) was used as the contrast agent. Gd-DTPA shortens the T1 (spin-lattice) relaxation time of the tissue (43). T1-weighted images were acquired 20–30min after contrast injection to detect the post-IR nonviable myocardium, which appears hyperintense because of the diffusion and retention of contrast agent into the site of the injury. Before image acquisition, an inversion RF pulse was applied, which inverted the tissue magnetization. The magnetization recovered at a rate corresponding to the T1 time of the specific tissue. An inversion time (TI) of 300ms was used to match the time at which the magnetization for normal myocardium nulls. At this time, the maximal contrast between viable and nonviable myocardium was achieved in murine heart. The optimal TI for DCE imaging can vary with the type of contrast agent, its concentration, and the field strength of the magnet. Proper selection of TI is important, as the contrast of the image can significantly vary, based on the choice of TI (8, 12, 42). A large flip angle (60 degrees) and a long TR (1,000ms at 11.7T) of 2 to 3 times the T1 of normal myocardium with signal averages of 6 were used to maximize signal per acquisition. Because of the long TR, the total time needed to acquire a DCE image with an adequate spatial resolution was 10–12min per acquisition. To image the entire left ventricle, a multislice acquisition (six slices of slice thickness 1.2mm) technique was applied.
MR images were converted to DICOM format, as reported previously (33). A stack of short-axis image slices was acquired (thickness, 1.0mm), fully covering the LV (planned at end-diastole) from the very base to the apical point. After the end-diastolic and end-systolic phases were identified on a slice-by-slice basis, the endocardial and epicardial borders were traced. LV end-systolic volume (ESV), LV end-diastolic volume (EDV), LV stroke volume (SV), cardiac output (CO), and LV ejection fraction (EF) were computed based on the traced borders. LV mass was calculated by slice summation by using the cardiac NMR (local software package), taking a specific gravity of 1.05g/cc. LV mass was measured, including the most basal image slice and papillary muscles.
Left ventricular epi- and endocardium were delineated in all data sets. Image analyses were performed off-line by using Segment software (http://segment.heiberg.se) (15). Two slices were selected from the midventricular level of each heart for analysis of regional contractile function (11). The midventricular level was chosen because the infarct pattern in this region typically includes all three tissue types of interest (i.e., enhanced, adjacent, and remote) (44). Slices closer to the base of the heart contain typically no or less infarct, whereas slices closer to the apex are nearly circumferentially infarcted. The circumference of each short-axis slice was divided into 18 equiangular radial segments, each of 20 degrees, taking right ventricular (RV) corner as the starting point, with clockwise rotation, as shown in the representative images (Fig. 2A). Papillary muscles were excluded in the endocardial borders during planimetry.
Delayed contrast-enhanced MR images were converted to DICOM format and transferred to Segment v1.8 R0670 software for infarct analysis. Images were processed pixel-wise by using Para-Vision PV4.0 software for infarct area, volume, and signal-intensity analysis. At each short-axis slice position, the end-diastolic phase was selected for infarct analysis. Image contrast and brightness were adjusted to nullify the noninfarcted myocardium while maximizing signal in the contrast-enhanced infarcted region. In the contrast-enhanced images, endocardial and epicardial borders as well as the borders of the signal-enhanced region were then subjected to planimetry. At each slice position, the number of enhanced and nonenhanced pixels was determined by using PV4.0. The size of the contrast-enhanced region was then expressed as a ratio of infarct to LV myocardial volume for all time points (Fig. 4ii). Scar size was assessed by using planimetry on each short-axis slice. Delineation of the hyperenhanced area followed by summation of data from each slice resulted in volume determination.
Signal intensity was measured in the normal region of the myocardium, and mean±SD was calculated. To determine hyperenhanced zones, we defined regions with image intensities greater than the mean signal intensity of the normal region within the transient and permanent infarct territories. If hyperenhancement was present, image intensities were thresholded at a level equal to 2 SD above the mean of the normal region and outlined only the hyperenhancement region to account for nontransmural involvement. The criterion for the threshold was chosen such that the “bright in the infarct is dead” (20). Contrast-enhanced short-axis images of the apical lower half of the LV with total infarct, magnified infarct region, and scar patches at different intensity levels were obtained by using these criteria. The delayed-hyperenhanced regions were subjected to contouring to detect the area of individual patchy islands. The necrotic and reversibly infarcted areas were quantified with planimetry.
The transmural extent of infarction (transmurality) was computed for each segment as the ratio of hyperenhanced to nonhyperenhanced areas, as shown in Fig. 6. Average transmurality for each infarct was calculated as the average of all segments with transmurality greater than zero.
Data are presented as mean±SEM. Significance of difference between means was determined (SPSS software package) with one-way analysis of variance (ANOVA) by using Tukey pairwise comparisons to assess differences between time points. Individual slices were considered to be separate observations (36). Student's paired t test was used to compare differences in transmurality in post-IR d3 and d28 (Fig. 6).
Attenuated R-wave amplitude, marked ST-segment elevation, and development of a large Q-wave were hallmarks of successful LAD occlusion during surgery. IR-insult compromised LV contraction, as manifested by enlarged end-diastole and end-systole volumes (Fig. 1A). Because our aim was to study remodeling in the surviving heart, myocardial infarction was limited to being mild. Under such conditions, EDV practically remained unchanged over time after IR. IR rapidly decreased stroke volume, and compromised stroke volume persisted over the duration of the study (Fig. 1Bi). Consistent with this observation, IR rapidly compromised LV functions, as represented by LVEF as well as CO (Fig. 1Bii). Concomitant with IR-induced rapid loss of LV function, LV mass substantially increased. This change was most prominent on day 3 after IR. This observation may have been contributed by edema in the inflammation phase or acute cardiomyocyte hypertrophy or both. As a function of recovery time, IR-induced increase in LV mass was noted to decrease. Although LV mass on post-IR day 28 was significantly higher than pre-IR baseline values, it was also significantly lower than the LV mass noted on post-IR day 3 (Fig. 1Biii; Table 1).
A segmental approach to measure LV wall motion was adopted (Fig. 2A). IR compromised LV contractility and caused enlargement of the cavity. IR-induced wall thinning was specifically noted in the anterior aspect of the LV, as represented by the angular positions 4 through 10. Unlike changes in LV function and mass that were most prominently noted on day 3 after IR, the LV wall-thinning response was most marked in post-IR days 7 and 14. In the border-zone sectors encompassing the midventricular and apical anterior septum, which were adjacent to infarcted anterior sectors, marginal decline of wall thickness was noted on post-IR day 3 (see data, Table 2). Such wall-thinning response, however, was significant on post-IR days 7 and 14. Recovery of wall thickness in these segments was noted in post-IR day 28. In the sector representing the midventricular septum, located remote from the infarct site, no significant change in wall motion was noted (Table 3).
The time course of hyperenhancement of LV injury was assessed by using the MR inversion-recovery sequence, which recognized true infarct size (Fig. 3). Earliest contrast-enhanced images were obtained 20–30min after contrast administration. Consistent with IR-induced changes noted in LV mass and function, infarct size was observed to be the largest on post-IR days 3 and 7. With time, however, the infarct size significantly decreased (Fig. 3, Table 3). Pixel-wise analysis of delayed hyperenhancement of infarct region via signal intensity was performed for the assessment of ischemic severity. A typical four-chamber view of the infarcted heart on post-IR day 3 is shown Fig. 4i. A representative contrast-enhanced short-axis image of the apical half of the LV depicting the injury on post-IR day 3 is presented in Fig. 4ii. Both normal (x) and hyperenhanced (y) regions were analyzed to obtain intensities of the normal myocardium and hyperenhanced myocardium, respectively. We observed that IR-induced absolute signal-intensity enhancement was highest on post-IR days 3 and 7. As a function of post-IR time, the signal-intensity enhancement was attenuated, suggesting that some of the damaged tissue may have recovered or the formation of scar tissue that does not lend itself to Gd-DTPA access because of compromised vascularization or both.
The hyperenhanced region was thresholded to obtain image intensities at three different regions: the normal myocardium, myocardium transient to infarction, and permanent infarction (24). Representative contrast-enhanced short-axis images of apical lower-half of LV depicting the total infarct, magnified infarct region, and scar patches at different intensity levels are shown in Fig. 5. The delayed-hyperenhanced regions are shown by contours. The necrotic and reversibly infarcted areas are quantitatively illustrated in Fig. 5iii (36). Interestingly, although the necrotic tissue area remains unaltered during the course of the post-IR recovery period, the reversibly infarcted tissue markedly was minimized during 4 weeks of recovery (Fig. 5iii).
The average transmurality of each infarct was calculated as the average of all segments with evidence of transmurality (Fig. 6). Delayed contrast-enhanced images obtained by administering Gd-DTPA to mice at different time points after IR were processed for the calculation of hyperenhanced and nonhyperenhanced patch areas of myocardium for all affected slices. Transmurality was expressed as a ratio of mean hyperenhanced to mean nonhyperenhanced areas (34). The approach adopted in this study was able to track infarct transmurality in beating murine hearts subjected to IR. Infarct transmurality markedly increased during post-IR recovery (day 3 vs. day 28), indicating that the permanent injury remains unchanged, whereas part of the reversibly injured tissue recovers in 4 weeks after IR.
Increased end-diastolic volume and compromised contractile function are commonly noted in the IR heart (50). Our observations are consistent with the literature demonstrating that after IR, cardiac functions are compromised and remain so over time (3, 17, 50). Attenuated LV ejection fraction and cardiac output in the post-IR heart represent hallmarks of a compromised state of cardiac function (41). Left ventricular hypertrophy, as is noted after myocardial infarction (2, 30, 46), was observed as an acute response after IR. Interestingly, during the four weeks of recovery after IR, although LV hypertrophy was still evident, LV mass was significantly lower compared with results recorded on post-IR day 3. Abnormal regional wall motion after myocardial infarction is caused by disrupted perfusion of the affected sites (11). LV segmental wall motion is useful to assess overall left ventricular function in acute myocardial infarction (22). Consistent with the clinical literature (1), we observed a gradation of wall-motion abnormality that consisted of hypokinetic (thinning, 40–50%) and akinetic (thinning, 30–40%) components. Progressive worsening of wall motion was noted during the first 2 weeks after IR. This is consistent with the notion of progressive myocyte death in the IR-affected myocardial site (33). In all middle and apical slices, the circumferential extent of wall thinning progressively increased in regions at angular positions 4 through 10. Analysis of the midventricular slices revealed that it was not only the IR-affected site where wall thinning was evident but also the wall diametrically opposite the infarct site had the thinning response. This response, although not clearly evident on post-IR day 3, was significantly noted on post-IR day 7. Mechanical load on the remote wall caused by the malfunctioning infarct site is likely to be responsible for the observation. Longitudinal measures conducted in our study demonstrate that in the murine heart, the thinning response is a progressive process that seems to peak on post-IR days 7 to 14. Beyond the first 2 weeks of IR, the structural geometry of the heart suggests that the thinning response not only stops but also partly reverses, as noted on post-IR day 28. Contribution of the scar tissue to this reversal response is likely, and histologic characterization is therefore of interest.
Clinically, hyperenhancement is commonly noted in post-IR myocardium after Gd-DTPA administration (31). Double-inversion pulse to null blood signal enhanced the contrast-to-noise ratio. Gd-DTPA rapidly diffuses out of capillaries into the extracellular space but cannot cross intact cell membranes. At the site of injury, however, Gd-DTPA enters into cells with compromised membrane integrity and is retained at that location because of poor perfusion of the injured tissue (45, 47). Partial-volume effect in the injured myocardium adds a layer of complexity to this interpretation (18, 23, 24). The partial-volume effect represents any of a set of effects that occur due to the finite size of the detection elements or resolution elements (voxels) and the fact that the object structure may vary rapidly over the region. When the object varies rapidly over distances comparable to the spatial resolution, one expects the image value to reflect the average value over the resolution element. This partial-volume averaging, a manifestation of the limited spatial resolution, is also called the linear partial-volume effect. Prudent consideration of the partial-volume effect is critical to the rational interpretation of MRI observations (27). We observed that the absolute volume of hyperenhanced myocardium decreased by a factor of 3.6 between post-IR days 3 and 28. Hyperenhancement includes both acutely necrotic regions and surrounding reversibly injured regions (10), as presented on post-IR day 3. Over the 4-week period of post-IR recovery, the necrotic tissue cannot reverse into viable myocardium, but a fraction of the reversibly injured tissue does recover, fractionally attenuating the infarct size. We also noted that the spatial extent of post-IR scar at 4 weeks of recovery was 3.6 times smaller than the spatial extent of acute myocyte necrosis at post-IR day 3. In canines, it is known that the infarct shrinks fourfold between post-IR day 4 and 6 weeks (30, 37). This is consistent with our observation demonstrating a significant reduction of proportional infarct size during 4 weeks of post-IR recovery. The observed reduction of infarct size over a 4-week period of post-IR recovery may be explained by (a) replacement of necrotic tissue by scar tissue (6, 9, 16, 28, 32), and (b) compensatory hypertrophy or enlargement of the uninjured tissue, with the goal to preserve cardiac function in the insulted heart (44).
Transmural ischemia is said to exist when ischemia extends subepicardially. This process has a more-visible effect on recovery of subepicardial cells compared with subendocardial cells. Recovery is more delayed in the subepicardial layers, and the subendocardial muscle fibers seem to recover first. Delayed contrast-enhanced cardiac MRI allows the direct visualization of the transmural extent of scar at high spatial resolution. This work provides a validated methodologic approach that is useful to quantify post-IR infarct tissue. When imaged by adopting a DHE MRI technique with an inversion-prepared T1-weighted sequence after injection of gadolinium chelates, the infarcted myocardium appears hyperenhanced relative to the unaffected healthy myocardium. The transmural extent of DHE predicts functional and anatomic remodeling in acute myocardial infarction as well as in chronic ischemic heart disease (7, 32, 34, 40). This approach can accurately discriminate between infarcted and dysfunctional but viable myocardium. The extent of delayed enhancement is reproducible and closely correlates with the size of myocardial necrosis or infarct scar (40). The transmural extent of viable tissue is inversely proportional to infarct expansion and may protect from subsequent LV remodeling (14). This work provides the first evidence from the study of transmurality in the post-IR heart of mice by using an 11.7-T system. Our observations are in tight agreement with clinical results addressing the key significance of scar size in LV remodeling (21, 34). Previously, it was suggested that contrast-enhanced MRI overestimates the size of myocardial infarcts when images are acquired much less than 20min after contrast injection (24). We observed that chronic infarct or scar volume, assessed by MRI, remained practically constant from post-IR day 3 (2.09mm3) to day 28 (2.76mm3). However, IR-induced change in volume of the injured-tissue compartment represented by moderate gadolinium concentration was reversible (post-IR day 3, 2.90mm3; day 28, 0.66mm3). Understanding the biology of these patches of repairing infarct tissue by using laser capture microdissection approaches (25, 26, 39) is likely to provide major advances in our understanding of post-IR myocardial wound healing.
This work was supported by NHLBI R01 HL073087.
2Ch, two chamber; 4Ch, four chamber; CO, cardiac output; DCE, delayed contrast enhancement; DICOM, digital imaging and communications in medicine; EF, ejection fraction; FA, flip angle; FLASH, fast low-angle shot; FOV, field of view; Gd-DTPA, gadolinium diethylenetriamine pentaacetic acid; GRE, gradient-recalled echo; IR, ischemia/reperfusion; IVS, interventricular septum; LAD, left anterior descending artery; LV, left ventricle; MR, magnetic resonance; MRI, magnetic resonance imaging; PM, papillary muscle; ROI, region of interest; RV, right ventricle; SNR, signal-to-noise ratio; T1, tissue magnetization recovery time; TE, echo time; TI, inversion-recovery time; TR, repetition time; SD, standard deviation.
No competing financial interests exist.