Identification of myocardial diffuse fibrosis by 11 heartbeat MOLLI T1 mapping: averaging to improve precision and correlation with collagen volume fraction
verfasst von:
Vassilios S. Vassiliou, Katharina Wassilew, Donnie Cameron, Ee Ling Heng, Evangelia Nyktari, George Asimakopoulos, Anthony de Souza, Shivraman Giri, Iain Pierce, Andrew Jabbour, David Firmin, Michael Frenneaux, Peter Gatehouse, Dudley J. Pennell, Sanjay K. Prasad
Our objectives involved identifying whether repeated averaging in basal and mid left ventricular myocardial levels improves precision and correlation with collagen volume fraction for 11 heartbeat MOLLI T1 mapping versus assessment at a single ventricular level.
Materials and methods
For assessment of T1 mapping precision, a cohort of 15 healthy volunteers underwent two CMR scans on separate days using an 11 heartbeat MOLLI with a 5(3)3 beat scheme to measure native T1 and a 4(1)3(1)2 beat post-contrast scheme to measure post-contrast T1, allowing calculation of partition coefficient and ECV. To assess correlation of T1 mapping with collagen volume fraction, a separate cohort of ten aortic stenosis patients scheduled to undergo surgery underwent one CMR scan with this 11 heartbeat MOLLI scheme, followed by intraoperative tru-cut myocardial biopsy. Six models of myocardial diffuse fibrosis assessment were established with incremental inclusion of imaging by averaging of the basal and mid-myocardial left ventricular levels, and each model was assessed for precision and correlation with collagen volume fraction.
Results
A model using 11 heart beat MOLLI imaging of two basal and two mid ventricular level averaged T1 maps provided improved precision (Intraclass correlation 0.93 vs 0.84) and correlation with histology (R2 = 0.83 vs 0.36) for diffuse fibrosis compared to a single mid-ventricular level alone. ECV was more precise and correlated better than native T1 mapping.
Conclusion
T1 mapping sequences with repeated averaging could be considered for applications of 11 heartbeat MOLLI, especially when small changes in native T1/ECV might affect clinical management.
Introduction
The longitudinal relaxation time, T1, of the myocardium is regarded as a useful imaging biomarker, as it can change with cardiac pathology and is known to be associated with functional capacity and mortality [1‐5]. Traditionally, late gadolinium enhancement (LGE) cardiovascular magnetic resonance (CMR) exploits changes in T1 following administration of a gadolinium–based contrast agent (Gd): namely, shortening of T1, which manifests as bright signal intensity on conventional inversion-recovery gradient echo sequences. This has been used as the primary tool for identification of focal (or replacement) fibrosis, indicative of scar, and has entered clinical routine for multiple pathologies, including myocardial infarction and viability [6], cardiomyopathy [2, 7], congenital heart disease [8] and valvular heart disease [5, 9].
A limitation of T1-weighted inversion recovery sequences is that they rely on the nulling of signal in normal myocardium to highlight concentrations of Gd in fibrotic areas. In cases of diffuse (interstitial) fibrosis, however, where the myocardium can be globally affected, the myocardial signal may appear isointense and, hence, lack sensitivity in identifying fibrosis [10]. To address this unmet clinical need and allow identification of diffuse myocardial fibrosis, new T1 mapping CMR sequences have been developed, based on the Modified Look-Locker inversion recovery (MOLLI) sequence first described by Messroghli and colleagues [11]. These allow imaging of extracellular volume fractions as a surrogate for diffuse fibrosis [12‐16].
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Recent iterations of the MOLLI T1 mapping sequence acquire a total of 8 or 9 T1-weighted images over 11 heart beats [14, 17], in a 5b(3b)3b scheme pre-contrast, and a 4b(1b)3b(1b)2b scheme post-contrast, where ‘b’ denotes beats and the values in brackets indicate pause intervals. These shortened acquisitions enable rapid breath-held imaging in around 8–12 s, depending on heart-rate, compared to the 15–20 s required by older MOLLI sequences, which typically acquired T1-weighted images in a 3b(3b)3b(3b)5b scheme [11, 18]. While reducing the number of T1-weighted MOLLI source images from 11 to 8/9 may reduce T1 precision, it also has the distinct advantage of increased reliability through better patient breath-holding. Therefore, the newer, faster sequences have enabled extended applications in patients with poorer breath-holding ability. However, before a new sequence is fit for clinical application, assessment of precision and accuracy is required, benchmarked against the reference standard of histologically derived quantification of diffuse fibrosis.
We examined an 11 heartbeat (11HB) MOLLI prototype, by Siemens, with native 5b(3b)3b and post-contrast 4b(1b)3b(1b)2b, which is referred to in the main text as MOLLI for brevity. This sequence has undergone little exploratory validation, and thus the aim of this work is to:
(1)
explore the effect of six imaging models (models A–F, Table 1) on precision and correlation with collagen volume fraction (CVF), which we use as a surrogate for accuracy; these models use incremental averaging of left ventricular slices (up to two averages at basal and up to two at mid-ventricular levels, before and after Gd) here referred to as “incremental inclusion of images”, and will be compared with the conventional use of only one mid-ventricular level slice;
Table 1
Using the four native and four post-Gd images it was possible to construct a total of 6 T1 mapping models
Basal level
Repeated
Mid-level
Repeated
Model A
x
Model B
x
Model C
x
x
Model D
x
x
Model E
x
x
Model F
x
x
x
x
The “x” marks the slice location of inclusion of the additional imaging
(2)
histologically validate the 5b(3b)3b and 4b(1b)3b(1b)2b 11 heart beat MOLLI prototype in patients who have left ventricular myocardial biopsy at the time of aortic valve surgery; and
(3)
explore the relative precision and correlation with CVF of native T1 mapping, partition coefficient, and extracellular volume fraction (ECV).
Materials and methods
Population cohorts
Two cohorts of participants were recruited for this work: a group of healthy volunteers for estimating T1 mapping precision, and a group of aortic stenosis patients for estimating T1 mapping correlation with CVF. Written consent was obtained from all patients and volunteers, and the study was conducted after local research ethics approval from the Royal Brompton and Harefield NHS Foundation trust and in accordance with the Declaration of Helsinki principles for Medical Research.
Cohort for estimating reproducibility/precision
Healthy volunteers taking no medication and with no known medical conditions were recruited following advertisements on public notice boards. The volunteers underwent a detailed health questionnaire and blood screening to measure haemoglobin, renal function, liver function, thyroid function, and C-reactive protein. The bloods were measured in a clinical biochemistry laboratory. Additionally, blood pressure, heart rate, and temperature were recorded. All volunteers underwent electrocardiography. In the event that an abnormality (e.g., hypertension, ECG abnormalities, renal failure) was detected that could have affected the results, the participant was excluded.
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Cohort for estimating correlation with collagen volume fraction
A cohort of patients with severe aortic stenosis, scheduled for surgical aortic valve replacement, was recruited from outpatient clinics or inpatient wards at the Royal Brompton Hospital, London, UK. The patients were excluded if they had any contraindications to CMR or if they were scheduled for surgery for more than one valve. Patients who were scheduled for concurrent aortic valve replacement and coronary artery by-pass grafting (CABG) were included. As this was a correlation study, the patients were not excluded if they had treated hypertension, hyperlipidaemia, or diabetes.
Assuming similar correlations to histological CVF to previous published data [12], we estimated that a minimum of five patients would be required to detect an R2 correlation of at least 0.8 with 80% power. We opted to double this number to ten patients, giving us 90% power to detect a statistically significant correlation assuming that the true R2 correlation was at least 0.6.
Cardiovascular magnetic resonance
All CMR imaging was performed on a 1.5 T scanner (Siemens Avanto, Erlangen, Germany). The quadrature body coil was used for radiofrequency transmission with 12–18 elements of an anterior and posterior cardiac parallel array coil for reception. The standard manufacturer wireless-ECG was used as in routine clinical work.
T1 mapping acquisition
The T1 mapping acquisition protocol was the same for both volunteers and aortic stenosis patients. Following adjustment of the scanner reference frequency to the predominant Larmor nuclear magnetic resonance precession frequency of the signal received from a cuboid volume region over the left-heart (“volume adjust”, ideally performed end-expiration), MOLLI T1 mapping was applied with the following parameters: Single-shot balanced steady-state free-precession images, field-of-view = 360 × 306 mm, slice thickness = 8 mm, alpha pulse flip angle = 35o, 7/8ths partial ky acquisition with 1/8th zero-filling, a generalised autocalibrating partially parallel acquisition acceleration factor of 2 with 24 central ky lines fully acquired to obtain receiver coil profiles, and 1085 Hz/pixel ADC sampling bandwidth. The T1 weighting was initially TI = 120 ms, incrementing by 80 ms at the start of each Look-Locker set. Two different MOLLI acquisitions were used depending on participant heart rates: a high-resolution acquisition for heart rates less than 90 bpm and a low-resolution acquisition for heart rates greater than 90 bpm. Two different sequences were required because the high-resolution acquisitions were too long to fit into the stationary diastole phase for faster heart rates. The following parameters varied between high-resolution and low-resolution setups, and these differences have been shown to have negligible impact on T1 values while maximising image quality [10].
High resolution: TR/TE = 2.6/1.12 ms, 84 acquired PE lines, single-shot image duration 220 ms, Acquired pixel size 1.4 mm (FE) × 2.1 mm (PE).
Low resolution: TR/TE = 2.4/1.0 ms, 76 acquired PE lines, single-shot image duration 182 ms, Acquired pixel size 1.9 mm (FE) × 2.4 mm (PE).
Further, for the low- and high-resolution MOLLI acquisitions, two different MOLLI sampling schemes were used pre- and post-contrast [10]: a 5b(3b)3b scheme was used for native T1 values and a 4b(1b)3b(1b)2b scheme was used for post-contrast T1.
A total of four native T1 maps were acquired (one basal and repeated once; one mid-ventricular level and repeated once). Then, starting fifteen minutes after Gd administration, post-Gd MOLLI T1 maps were acquired at basal and mid-ventricular levels (and repeated once at each level, giving rise to four post-Gd T1 maps) using the 4b(1b)3b(1b)2b scheme, again with low or high resolution depending on the heart rate. In total, four native T1 maps and four post-contrast T1 maps were obtained. The addition of a complete T1 mapping protocol to a clinical scan increased the total scan time by about 5–7 min per patient.
To assess interscan reproducibility, the healthy volunteers underwent a second CMR scan within 60 days of the first. To mimic routine clinical practice, the staff undertaking the second scan were unaware of the exact slice position used for acquisition in the first scan. The aortic stenosis patients underwent a single CMR scan as close to the day of surgery as possible.
Image post-processing and analysis
For quantification of LV function, volumes, and T1 values, dedicated software CMR Tools (Cardiovascular Imaging Solutions, London, UK, Fig. 1) was used by experienced (level 3 SCMR) blinded operators. Visual inspection of the colour maps was undertaken both in-line on the Siemens platform and off-line using CMR 42 (Circle CVI, Calgary, Canada, Fig. 2).
Fig. 1
Representative short axis images from a healthy volunteer with native T1 maps (a–d) and post gad T1 maps (e–h). One basal and one mid-ventricular level were selected and imaging at each level was repeated both before and after the administration of Gd (a, b native T1 basal; e, f post-Gd basal; c, d native T1 mid-ventricular level, g, h, mid-ventricular level post-Gd). Regions of interest (ROI) were drawn in the myocardium and blood
Fig. 2
a showing a basal slice with native T1 mapping using the high resolution 5(3)3 beat sequence as the heart rate was 58 bpm. b shows the post-Gd image using a high resolution 4(1)3(1)2 beat sequence. c shows the native T1 mapping and d the post-Gd contrast T1 mapping using the same high resolution sequence as in (a, b) respectively, but at the mid-ventricular level
×
×
MOLLI T1 maps were generated automatically in-line on the scanner workstation, following motion correction and pixel-by-pixel curve fitting with Look-Locker correction. DICOM images were anonymised and maps were analysed in a blinded fashion by two observers to evaluate interstudy and interobserver variability. A third observer adjudicated values of >5% relative difference. Native and post-Gd MOLLI source images were inspected and a quality score from 1 to 5, with five being excellent and 1 very poor, was recorded for respiratory drift, cardiac motion artefact, and appropriate cardiac triggering of each image, before proceeding with measurements on the derived T1-maps. Only patients scoring ≥4 in all categories were subsequently included in the analysis.
Regions of interest (ROIs) were drawn on the T1 maps (Fig. 1) within the mid-wall of the septum, with care being taken to avoid partial-volume or cardiac-motion-related blurring of the myocardium-blood boundary, where blood signal contaminates myocardial data. A second set of ROIs were drawn in the blood, avoiding myocardium and papillary muscles. A standardised approach was undertaken in all patients with regards to the location of the ROI, and all areas were included, even if they were subsequently shown to have LGE. This had been decided a priori, as in patients where only native T1 mapping is undertaken, one does not have the subsequent benefit of knowing where LGE is present, and therefore our protocol was standardised in this way for all the patients.
Once native and post-Gd myocardial and blood values and haematocrit were obtained, extracellular volumes (ECVs) were calculated as shown in Eq. (1):
where T1myopost and T1myopre are the T1 values of post-contrast and native myocardium, and T1bloodpost and T1bloodpre are the T1 values of post-contrast and native blood, respectively.
Myocardial biopsy: procedure and analysis
All aortic stenosis patients included underwent successful myocardial biopsy intraoperatively using the following standardised protocol: Once the chest was opened and cardiopulmonary bypass was established, a long near-transmural left ventricular “tru-cut” biopsy was taken. The aim was to undertake multiple biopsies provided that patient safety was not compromised. Upon completion of the biopsy, the myocardium was sutured, if required, and surgery continued as normal. The myocardial biopsies were immediately fixed in warm buffered 4% formalin. Histological analysis of fibrosis was undertaken on 3-µm-thick sections from formalin-fixed, paraffin-embedded endomyocardial biopsies using a special collagen stain (Picrosirius red). Quantification was performed using standardised semiautomatic image analysis software (Nikon Advanced Research NIS Elements imaging software, NIS elements AR 4.10.02, Nikon) on images of 14 randomly chosen consecutive high-power fields (×200 magnification), which were obtained with a Nikon Eclipse E400 light projection microscope (Nikon, Minato, Tokyo, Japan). The 14 high power fields equaled 1 mm2. Endocardium, subendocardial fibrosis and subendocardial fat, procedure-related optically empty spaces and epicardial fat were eliminated from analysis. Subsequent image analysis was performed to determine the level of fibrosis including reactive, band-like perimysial collagen depositions and perivascular fibrosis, defined as collagen surrounding arterioles. Fibrosis was calculated as the collagen volume fraction (%) per square millimeter, as previously described [19].
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Statistical analysis
The CMR native T1 values, partition coefficients, and ECVs were compared to the histologically identified collagen volume fraction (CVF). Intraclass correlation coefficients (ICC) were calculated using ‘R’ (R Foundation for Statistical Computing, Vienna, Austria) and used to assess agreement in the healthy volunteer ‘precision’ cohort. For the aortic stenosis ‘correlation with CVF' cohort, graph-plotting and analysis was again undertaken using the statistics package ‘R’. The six models, A–F, described for CMR estimation of myocardial diffuse fibrosis were compared to identify the most reproducible model (from the volunteer precision cohort) and most accurate/correlating with CVF (from the aortic stenosis biopsy cohort). There is no published method of incorporating both precision and accuracy (via correlation with CVF) in one single measurement for such imaging work. We therefore proposed and calculated the product of the scan-rescan R2 values for the volunteer (precision) and ECV-histological fibrosis R2 for aortic stenosis biopsy patients (correlation with CVF) as a single combined measure of correlation with CVF and precision for this imaging modality, described in this manuscript as Product of R2.
Results
Reproducibility-precision: the volunteer cohort
Fifteen healthy volunteers, eight males, mean age = 31 ± 5 years, were recruited and the reproducibility of their corresponding native T1 maps, post Gd T1 maps, partition coefficient and ECV results are shown in Table 2. All volunteers had an HR < 90 bpm for both scans, and; therefore, the higher resolution sequence was used. Participants tolerated both scans well with no complications and excellent T1 mapping images were obtained. No volunteer was excluded due to respiratory drift, cardiac motion artefact, or inappropriate cardiac triggering. There was no statistically significant difference between the two scans with regards to heart rate, blood pressure, or haematocrit (p = 0.27, p = 0.19, p = 0.89, respectively). Both interstudy T1 and interstudy ECV differences showed excellent results (Bland–Altman shown in Fig. 3 for native T1 and Fig. 4 for ECV, respectively).
Table 2
Showing interscan reproducibility
Interstudy reproducibility
Basal
Repeat
Mid
Repeat
Native T1
mapping
Post Gd mapping
Partition coefficient
ECV
ICC
p value
ICC
p value
ICC
p value
ICC
p value
Model A
x
0.90
P < 0.001
0.72
p = 0.014
0.53
p = 0.098
0.84
p = 0.001
Model B
x
0.84
p = 0.001
0.68
p = 0.018
0.4
p = 0.17
0.75
p = 0.006
Model C
x
x
0.88
p < 0.001
0.82
p = 0.002
0.81
p = 0.002
0.94
p < 0.001
Model D
x
x
0.80
p = 0.001
0.75
p = 0.006
0.66
p = 0.024
0.88
p < 0.001
Model E
x
x
0.90
p < 0.001
0.71
p = 0.013
0.54
p = 0.08
0.88
p < 0.001
Model F
x
x
x
x
0.88
p < 0.001
0.79
p = 0.003
0.81
p = 0.002
0.93
P < 0.001
The six models A–F incorporating increasing levels and averaging of myocardial T1 maps are shown. Model C–F showed the best extracellular volume (ECV) reproducibility
ICC intraclass correlation
Fig. 3
Bland–Altman analysis of T1, including mean difference, correlation, and distribution of differences plots. Mean difference = 11.5 ms (red line on difference plot) with limits of agreement at −21 and 43 ms; the line of zero difference (dashed) is within the limits of agreement
Fig. 4
Bland–Altman analysis of ECV, including mean difference, correlation, and distribution of differences plots. Mean difference = 0.003 (red line on difference plot) with limits of agreement at −0.024 and 0.029; the line of zero difference (dashed) is within the limits of agreement
×
×
Both intra- and interobserver variability were excellent. Intraobserver ICCs were: 0.995 for native T1 (p < 0.001), 0.996 for partition coefficient (p < 0.001) and 0.999 for ECV (p < 0.001). Interobserver ICCs were: 0.993 for native T1 (p < 0.001), 0.985 for partition coefficient (p < 0.001), and 0.997 for ECV (p < 0.001).
Correlation with collagen volume fraction: The aortic stenosis cohort
Ten consecutive patients with symptomatic severe aortic stenosis scheduled for surgical valve replacement underwent CMR and intraoperative myocardial biopsies: eight male, mean age = 71 ± 10 years, and three with significant major epicardial coronary artery disease (defined as disease >50% of lumen diameter) requiring CABG at the time of the operation. Of these patients, five received treatment for hypertension and their blood pressure was well controlled at the time of the CMR (BP < 140/90 mmHg), four had treated hyperlipidaemia, two had chronic obstructive pulmonary disease requiring bronchodilators and two had prior distant history of neoplasia (breast/bladder). Of the three patients requiring CABG, one had 2-vessel CABG (left anterior descending (LAD) and circumflex) and the other two had single vessel CABG (one of the LAD and one of the intermediate coronary artery respectively). No patients suffered from diabetes. All patients tolerated the CMR well and the T1 mapping images were free from disqualifying artefacts and were diagnostic in all participants. In one patient the initial native T1 maps needed repeating in view of poor breathholding. This was appreciated during the scan, and therefore was repeated before proceeding to Gd administration. The repeat maps were of acceptable quality with no apparent respiratory drift, cardiac motion artefact, or inappropriate cardiac triggering. All patients had apical–lateral wall biopsies taken intraoperatively and no patients had biopsies from all three basal, mid, and apical levels due to surgical concerns. One patient had to be taken back to theatre within 24 h from surgery for bleeding, which may have been related to the apical myocardial biopsy sampling. The patient made a good recovery and discharged home within five days with no further sequela. No other side-effects relating to the myocardial biopsies were seen. Therefore, the basal and/or mid-myocardial T1 values were taken as a surrogate for a global T1 value and were correlated with histology from the apical–lateral wall. Microscopic views of the sections prepared from the biopsies are shown in Fig. 5.
Fig. 5
Samples from the intraoperative myocardial biopsies stained with Picrosirius red. a Shows fibrous septae, which show perivascular collagen to support mural arteries. There is no scarring, but only a slight increase in collagen fibres surrounding each cardiomyocyte (light red). b Shows interstitial fibrosis only, each cardiomyocyte is supported by a thin collagen layer (light red), there is only focal perivascular(pericapillary–capillary encircled) increase in collagen fibers (dark red area annotated). c Shows an annotated red area, qualifying as scar, as the dimension of the area exceeds double the diameter of the adjacent hypertrophic cardiomyocyte indicated with ⟷
×
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The relative correlation with CVF of native T1 maps, partition coefficient, and ECV were assessed using histology. The histologically derived CVF was plotted against each of these parameters, as shown in Table 3. Native T1 values from model F (which had shown best correlation) showed a moderate, statistically-significant correlation with the histologically obtained fibrosis burden, with R2 = 0.42, and p = 0.046. However, the partition coefficient and ECV both showed strong correlations with histology, with R2 = 0.81 and R2 = 0.83, and these both were statistically significant, with p < 0.001 (Table 3; Fig. 6).
Table 3
showing the correlation of extracellular volume (ECV) by each model with histological collagen volume fraction (CVF) from apical–lateral histology
Correlation of ECV with histological fibrosis
Basal level
Basal repeated
Mid-level
Mid-level repeated
ECV (%)
R2 with histology
p value
Model A
x
27.47
0.36
0.068
Model B
x
26.67
0.77
0.001
Model C
x
x
26.86
0.49
0.025
Model D
x
x
26.79
0.81
<0.001
Model E
x
x
27.07
0.72
0.002
Model F
x
x
x
x
26.83
0.83
<0.001
It can be argued that in view of other myocardial pathologies co-existing with aortic stenosis such as oedema or ischaemia, CVF might not be the gold standard for fibrosis comparison. Therefore, this table should be interpreted in the appropriate clinical context. In patients with aortic stenosis, it would appear that ECV derived from the basal slice correlated better with CVF than the mid-ventricular level, but a combination of both the basal and mid had the best correlation. These results would suggest that further research is warranted to show whether imaging of basal and mid-ventricular level should be routinely undertaken in patients with aortic stenosis
Fig. 6
The agreement comparing (apical) histological CVF against ECV (a), native T1 mapping (b), and partition coefficient (c). There was good agreement between CVF and all the imaging parameters; however, partition coefficient and ECV performed considerably better than native T1 mapping alone
×
Having established that ECV was the most accurate imaging parameter from T1 mapping, we further investigated the incremental addition of more myocardial regions and averaged slices. When only one mid-level T1-map was used (i.e., Model A), the correlation with histology was only modest, and was not significant (R2 = 0.36, p = 0.068), similar to data from published studies that used only one mid-level T1-map [14, 20]. Increasing the number of T1 maps, and including the basal level as well as the mid-ventricular-level in this averaging improved the correlation significantly: R2 = 0.72, p = 0.002 when the average of a single basal and single mid-level image was used for ECV (Model E) and importantly R2 = 0.83, p < 0.001 when acquisition was repeated at both basal and mid-levels (Model F) as shown in Table 3 and Fig. 7.
Fig. 7
a Showing the correlation of (apical–lateral) histological collagen volume fractions (CVF) with ECV calculated from CMR at a single mid-ventricular level, corresponding to Model A and showing only mild non-significant correlation. b Showing correlation of histological fibrosis with a single basal level (Model B), showing that for this pathology the correlation increases and has now become significant. c Showing correlation between the average of one mid-level and one basal level (Model E) with histology showing a significant correlation. d Represents Model F with two basal and two mid-slices showing that this model demonstrated the strongest correlation (R2 = 0.83, p < 0.001). This work confirms that including incrementally more levels imaged improves accuracy
×
Combining precision and correlation with collagen volume fraction
To allow us to clarify the relative incremental addition of imaging for each model combining both accuracy (via correlation with CVF) and precision we sought a single parameter for each model to incorporate both correlation with CVF and precision. However, such a single measure has not been described for T1 mapping. We therefore devised a new model, incorporating the product of the R2 from the precision cohort and R2 from the ‘correlation with CVF' cohort as a unique parameter for each model. The results are shown in Table 4, and indicate that the inclusion of a repeated basal image and a repeated mid-image, giving a total of four native and four post Gd T1 maps to calculate ECV, was the most precise method with the best correlation with CVF.
Table 4
Combining accuracy and precision in a single measurement, the Product of R2 indicating that Model F offers the best imaging protocol (basal and repeat, mid-ventricular level and repeat) for optimal accuracy and precision
Basal
Repeat
Mid
Repeat
Volunteer interscan R2
ECV vs histology R2
Product of R2
Model A
x
0.759
0.356
0.27
Model B
x
0.722
0.773
0.56
Model C
x
x
0.808
0.486
0.39
Model D
x
x
0.637
0.809
0.52
Model E
x
x
0.623
0.715
0.45
Model F
x
x
x
x
0.778
0.829
0.65
ECV extracellular volume
Discussion
Any new CMR sequence needs to show both good accuracy and precision to become clinically relevant. In this work, we used two cohorts to establish precision and correlation with CVF (as a surrogate for accuracy) for an as yet non-validated T1 mapping sequence. Furthermore, this is the first time a study has reported a model of incremental image acquisition and averaging of basal and mid-ventricular T1-measurements as a means of obtaining an average of the global T1-mapping ECV. The volunteer cohort demonstrated that four models of slice acquisition and averaging showed an excellent interscan correlation. Model A native T1 mapping (one native T1 mid-ventricular level slice), Model E native T1 mapping (average of one basal and one mid-level slice native T1), Model C ECV (average of ECV of two mid-level slices), and Model F ECV (average ECV of two basal and two mid-slices) all showed excellent interscan reproducibility, with R2 ≥ 0.90.
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The correlation with CVF was assessed using a cohort of ten patients with aortic stenosis scheduled for surgical valve replacement who had CMR using our model of incremental addition of imaging acquisitions and intraoperative biopsies. This confirmed that in aortic stenosis patients, measuring ECV in the mid-ventricular wall alone (Model A) showed only a trend towards weak correlation with histological collagen volume fraction (CVF), R2 = 0.36, p = 0.068. A model utilising the basal level alone (Model B) showed good correlation with histology (R2 = 0.77, p = 0.001), while a model based on one basal level being imaged twice and averaged (Model D) showed better correlation (R2 = 0.81, p < 0.001). The best correlation was achieved by a model having one basal and one mid-ventricular slice being imaged twice each and averaged (Model F, R2 = 0.83, p < 0.001). Incorporating both precision and correlation with CVF parameters into the Product R2, showed that ECV calculated from Model F was the most accurate and precise. We speculate that the improved correlation and precision associated with Model F may relate to the incorporation of further areas of the myocardium (both basal and mid-ventricular level) and the repeat scan may serve to average out any potential errors associated with imaging a single slice.
This work therefore supports the following conclusions: firstly, the 11 heart beat MOLLI prototype incorporating native 5b(3b)3b and post-contrast 4b(1b)3b(1b)2b schemes, was well tolerated by volunteers and patients. Secondly, when isolated native T1 mapping was used (without post-contrast T1 maps), it is reproducible in healthy volunteers, especially when Model A (one mid-slice), Model C (one mid-slice repeated), Model E (one basal and one mid-slice), or Model F (one basal and one mid-ventricular level, both repeated) are used. Repeating native T1 maps does not appear to offer additional improvement in precision, as Model A performed at least as well as Models C, E and F. Thirdly, both partition coefficient and ECV have been shown to be more accurate than native T1 maps alone. Therefore, we propose that post-Gd imaging (with or without haematocrit sampling) should be routinely undertaken when looking for an estimation of diffuse fibrosis in patients. Fourthly, a single mid-ventricular ECV measurement appears to show poorer correlation with CVF in patients with aortic stenosis (as shown by Model A). Providing additional image repeats, such as model C, E or F for example, appear to show improved correlation with CVF. Although our study is not without its limitations, particularly regarding the use of the CVF as the reference standard, further work could consider whether the additional improvement in correlation provided by models C, E, and F, for example, might be of clinical importance. Finally, the most accurate and precise model is Model F, whereby imaging of one basal and one mid-ventricular level slice, with both being repeated once, is performed both in the native state and after Gd administration.
We therefore recommend that this should be considered if there is available scanner time and the patients can tolerate it. However, increasing scanner time (even by 5–7 min) might not be possible in many busy CMR units. As such, undertaking repeats of basal and mid-ventricular levels might not be an option. Nonetheless, even in busy units it should be possible to undertake repeat imaging of a single level, which will only add two breathholds to the scan time. Therefore, if a unit undertakes a mid-ventricular slice T1 mapping routinely in the native and post-contrast state, we recommend that imaging at the same level is repeated once. This will provide additional improvement in the correlation-precision, but also safeguard against potential poor breathholding, poor coregistration, or motion correction in one of the two acquisitions. Such a practical compromise will only increase scanner time by about 30 s. It should be noted that this relation only holds true for the 11HB sequence we have tested, and other MOLLI sequences might not behave in a similar way.
This study has certain limitations. Firstly, our samples for both cohorts were small; however, this is in line with other recently published studies, which also use small (fewer than ten patients) datasets for histological validation [21, 22]. Secondly, we used healthy volunteers for the interscan reproducibility, as this was practically easier to achieve. As aortic stenosis patients can be more breathless and might have difficulties with breathholding, it is possible that the reproducibility might not be as good as for healthy controls. However, recently published work [23, 24] has shown that reproducibility in aortic stenosis was excellent, and therefore, we would not have anticipated different results to our controls, as T1 mapping in our aortic stenosis patients was of very good quality. Furthermore, we elected not to include apical T1 mapping in any of our T1 mapping strategies, as this region is known to suffer increased partial-volume artefact at the endocardial and epicardial borders, which are not perpendicular to the image slice in the apical short-axis region [25]. Moreover, we did not undertake intra-study reproducibility which could have provided additional information. We felt that intrascan reproducibility for ECV would be difficult to interpret as by default the post-Gd T1 maps would be taken at different times. In addition, our myocardial biopsies were taken from the apico-lateral wall. Nonetheless, earlier studies have shown that, unlike replacement fibrosis, where there is a significant difference between basal and apical areas [26], interstitial fibrosis tends to follow a more homogenous pattern [23, 27] in patients with aortic stenosis. Therefore, we feel that our results are valid for the apico-lateral wall biopsies to represent global diffuse fibrosis measurement in these patients. Finally, it is appreciated that other pathological processes might affect T1/ECV in aortic stenosis including oedema [25] and ischaemia [28, 29]; therefore, the correlation between T1/ECV and CVF should be regarded as an association rather than causative, as there could be multiple aetiologies that might increase T1/ECV.
Conclusion
This work was the first to utilise T1 mapping strategies with increasingly inclusive additional imaging for averaging the septal ECV measurements, going from one slice imaged to a total of four images (one basal repeated and one mid repeated) to improve both the correlation with CVF and the precision of the T1-measurement (both before and after Gd), comparing histological CVF estimation of fibrosis to the T1-mapping outcomes of native T1 maps, partition coefficient and ECV. We have shown that the 11 heartbeat MOLLI sequence used in this research, native 5b(3b)3b with post-contrast 4b(1b)3b(1b)2b, was well-tolerated in both volunteers and patients with aortic stenosis. Furthermore, it was both accurate and precise, particularly as incremental imaging of additional basal and mid-ventricular slice images are included. Finally, this work also confirms that partition coefficient and ECV can be accurately used to correlate with histological CVF estimation of diffuse fibrosis.
Acknowledgements
The authors would like to acknowledge the assistance of Mr Alex Bowman, Histopathology Core Facility Laboratory Manager, Biomedical Research Unit, Royal Brompton Hospital, London with the preparation of the histology blocks.
Funding
This work was supported by the National Institute of Health Research Cardiovascular Biomedical Research Unit at the Royal Brompton Hospital and Imperial College, London and Rosetrees Trust charity. Dr Heng was supported by a British Heart Foundation Clinical Research Training fellowship (FS/13/76/30477).
Compliance with ethical standards
Conflict of interest
Professor Pennell is a stockholder and director of Cardiovascular Imaging Solutions and received research support from Siemens. Professor Frenneaux has received funding from Medtronic for investigator-initiated research. Dr Prasad has received speaker's fees from Bayer. Dr Giri is an employee of Siemens Healthcare. The remaining authors have no competing interests.
Ethical approval
All procedures performed in studies involving human participants were in accordance with the ethical standards of the institutional research committee and with the 1964 Declaration of Helsinki and its later amendments or comparable ethical standards.
Informed consent
Informed consent was obtained from all individual participants included in the study.
Open AccessThis article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made.
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Identification of myocardial diffuse fibrosis by 11 heartbeat MOLLI T 1 mapping: averaging to improve precision and correlation with collagen volume fraction
verfasst von
Vassilios S. Vassiliou Katharina Wassilew Donnie Cameron Ee Ling Heng Evangelia Nyktari George Asimakopoulos Anthony de Souza Shivraman Giri Iain Pierce Andrew Jabbour David Firmin Michael Frenneaux Peter Gatehouse Dudley J. Pennell Sanjay K. Prasad
