Skip to main content
PMC home page
Frontiers in Physiology logoLink to Frontiers in Physiology
. 2021 Jun 2;12:644837. doi: 10.3389/fphys.2021.644837

A Comparison of CVR Magnitude and Delay Assessed at 1.5 and 3T in Patients With Cerebral Small Vessel Disease

Michael S Stringer 1,2,†, Gordon W Blair 1,2,†, Yulu Shi 1,3, Iona Hamilton 1,2, David A Dickie 4, Fergus N Doubal 1,2, Ian M Marshall 1,2, Michael J Thrippleton 1,2,*, Joanna M Wardlaw 1,2
PMCID: PMC8207286  PMID: 34149442

Abstract

Background

Cerebrovascular reactivity (CVR) measures blood flow change in response to a vasoactive stimulus. Impairment is associated with several neurological conditions and can be measured using blood oxygen level-dependent (BOLD) magnetic resonance imaging (MRI). Field strength affects the BOLD signal, but the effect on CVR is unquantified in patient populations.

Methods

We recruited patients with minor ischemic stroke and assessed CVR magnitude and delay time at 3 and 1.5 Tesla using BOLD MRI during a hypercapnic challenge. We assessed subcortical gray (GM) and white matter (WM) differences using Wilcoxon signed rank tests and scatterplots. Additionally, we explored associations with demographic factors, WM hyperintensity burden, and small vessel disease score.

Results

Eighteen of twenty patients provided usable data. At 3T vs. 1.5T: mean CVR magnitude showed less variance (WM 3T: 0.062 ± 0.018%/mmHg, range 0.035, 0.093; 1.5T: 0.057 ± 0.024%/mmHg, range 0.016, 0.094) but was not systematically higher (Wilcoxon signal rank tests, WM: r = −0.33, confidence interval (CI): −0.013, 0.003, p = 0.167); delay showed similar variance (WM 3T: 40 ± 12 s, range: 12, 56; 1.5T: 31 ± 13 s, range 6, 50) and was shorter in GM (r = 0.33, CI: −2, 9, p = 0.164) and longer in WM (r = −0.59, CI: −16, −2, p = 0.010). Patients with higher disease severity tended to have lower CVR at 1.5 and 3T.

Conclusion

Mean CVR magnitude at 3T was similar to 1.5T but showed less variance. GM/WM delay differences may be affected by low signal-to-noise ratio among other factors. Although 3T may reduce variance in CVR magnitude, CVR is readily assessable at 1.5T and reveals comparable associations and trends with disease severity.

Keywords: cerebrovascular reactivity, small vessel disease, magnetic resonance imaging, stroke, BOLD signal

Introduction

Cerebrovascular reactivity (CVR) quantifies the change in blood flow in response to a vasoactive stimulus, providing an indicator of vascular health. CVR magnitude measures the amplitude of the response. However, CVR delay, the time between stimulus onset and observing a change in the blood flow, should also be considered to avoid underestimating CVR magnitude as response time can vary in different tissues (van Niftrik et al., 2017).

Impaired CVR is associated with several conditions, including cerebral small vessel disease (SVD), a major cause of stroke and dementia with no current treatments (Wardlaw et al., 2019). CVR magnitude is lower in patients with more severe SVD features on magnetic resonance imaging (MRI) (Blair et al., 2020), and CVR delay is longer in SVD patients than healthy controls (Sam et al., 2016; Thrippleton et al., 2018; Atwi et al., 2019). Therefore, exploring the role of CVR in SVD may provide valuable insight into disease progression mechanisms.

CVR is typically assessed using blood oxygenation level dependent (BOLD) MRI, and several different vasoactive stimuli are available (Liu et al., 2019). Common vasoactive stimuli include fixed or targeted CO2 inhalation, breath hold, and injection of acetazolamide. Fixed inhalation provides a robust stimulus applicable in many patient populations, including SVD (Thrippleton et al., 2018), the effectiveness of which is less dependent on patient compliance than breath hold and requires less specialist input than targeted inhalation.

Although field strength influences both the intra- and extravascular components of the BOLD signal (Silvennoinen et al., 2003), CVR comparisons at different field strengths remain limited (Driver et al., 2010; Triantafyllou et al., 2011; Peng et al., 2020). Increased field strength enhances contrast-to-noise ratio of the BOLD signal (Gati et al., 1997; Krüger et al., 2001; Triantafyllou et al., 2011) but increases susceptibility artifact (Bernstein et al., 2006). Additionally, CVR has mainly been measured at 3T or higher despite 1.5T MR scanners being more common clinically; therefore, the effect of field strength on CVR measurements in patient populations should be considered (Blair et al., 2016). Few studies have quantified the effect of field strength on CVR measurement at 1.5T and 3T. Triantafyllou et al. (2011) found the change in R2∗ per unit fractional flow change was 1.76 times higher at 3T than 1.5T using a fixed inhalation paradigm. Similarly, Peng et al. (2020) found a higher percentage signal change at 3T than 1.5T using breath hold. However, both studies were in healthy controls, and to our knowledge, no comparisons have compared CVR values at different field strengths in clinical populations.

We assessed subcortical gray (GM) and white matter (WM) CVR in patients with minor ischemic stroke at 1.5T and 3T to compare CVR magnitude and delay. Additionally, we compared associations between CVR and key clinical variables at each field strength.

Materials and Methods

Participants

We prospectively recruited patients with symptomatic minor, non-disabling, ischemic stroke as previously described (Wardlaw et al., 2009; Heye et al., 2016). We diagnosed patients based on clinical presentation, appearance on diffusion-weighted imaging and other relevant diagnostic MRI sequences as described in the STRIVE guidelines (Wardlaw et al., 2013). The patients had recovered from the minor stroke and were living independently in the community although many still had minor symptoms of the stroke. Many patients with stroke also have vascular risk factors, such as hypertension or hyperlipidemia; often have features of SVD on imaging, indicating chronic vascular brain damage; and are prescribed secondary prevention for stroke, including antihypertensive agents and lipid-lowering and antiplatelet drugs. Features of SVD on brain imaging commonly include WM hyperintensities (WMH), lacunes (small holes in subcortical GM or WM), microbleeds, and visible perivascular spaces (PVS). We excluded patients with disabling stroke (requiring assistance for activities in daily life), poorly controlled diabetes mellitus, hypertension, any psychiatric illness with the potential to limit study compliance, a family history of intracranial aneurysm, subarachnoid hemorrhage, known arteriovenous malformation, or contraindications to MRI.

We acquired written informed consent from all patients. We received approval from the UK Health Research Authority National Research Ethics Service Committee East Midlands, Nottingham 1 (ref. 14/EM/1126) and conducted all research in accordance with the Declaration of Helsinki.

Imaging Acquisition

As previously reported, we scanned participants at 1.5T (Signa HDxt, General Electric, Milwaukee, WI) with a gradient-echo echo-planar imaging (GE-EPI) sequence (TR/TE = 3,000/45 ms, voxel size: 4 × 4 × 4 mm3) and neurovascular structural imaging protocol, including 3-D T1-weighted imaging; axial T2-weighted, axial fluid-attenuated inversion recovery; and axial gradient echo (Table 1A; Blair et al., 2020). We subsequently scanned a subset of patients at 3T (Siemens Verio, Siemens Healthcare, Erlangen, Germany) with a GE-EPI sequence (TR/TE = 3,000/30 ms, voxel size: 3 × 3 × 3 mm3) and comparable structural imaging protocol (Table 1B).

TABLE 1.

MR sequence parameters used for (A) 1.5T and (B) 3T imaging protocols.

(A) 1.5T (Signa HDxt)
Sequence GE-EPI BOLD 3D IR-SPGR T1-w T2-w Propeller FLAIR GRE
TR (ms) 3,000 9.6 7,000 8,000 900
TE (ms) 45 4.0 90 100 15
TI (ms) − 500 − 2,000 −
Flip angle (°) 90 8 − − 20
Field of view (cm) 25.6 × 25.6 25.6 × 25.6 24 × 24 24 × 24 24 × 24
Acquisition matrix 64 × 64 192 × 192 320 × 256 384 × 256
Slice thickness (mm) 4 1.3 4 4 4
Number of slices 36 160 36 36 36
Other − − 1.5 signal averages, matrix size 384 − −
(B) 3T (Siemens Verio)
Sequence GE-EPI BOLD 3D MPRAGE T1-w T2-w BLADE FLAIR BLADE GRE
TR (ms) 3,000 2,300 11,400 9,100 600
TE (ms) 30 2.98 120 125 10
TI (ms) − 1,100 − 2,512 −
Flip angle (°) 90 9 − 130 15
Field of view (cm) 19.2 × 19.2 25.6 × 25.6 24 × 24 24 × 24 24 × 24
Acquisition matrix 64 × 64 256 × 256 384 × 384 256 × 256 320 × 256
Slice thickness (mm) 3 1 3 3 3
Number of slices 48 256 48 48 48
Other − − − − −
Open in a new tab

GE-EPI, gradient-echo echo-planar imaging; IR-SPGR, inversion recovery spoiled gradient echo; MPRAGE, magnetization prepared-rapid gradient echo; FLAIR, fluid-attenuated inversion recovery; GRE, gradient recalled echo.

The full protocol for the CVR experiment has been previously described (Thrippleton et al., 2018). A summary of the key steps is provided in Figure 1. In brief, we administered alternating blocks of 2 min of medical air and 3 min of medical air with CO2 at an elevated concentration of 6% (BOC Special Products, United Kingdom). Gases were administered via a disposable anesthetic mask while wearing a unidirectional breathing circuit (Intersurgical, Wokingham, United Kingdom). Vital signs [peripheral oxygen saturation, blood pressure, heart rate, end-tidal CO2 (ETCO2), and respiratory rate] were measured throughout using a CD-3A CO2 sensor (AEI Technologies, Pittsburgh, United States) at 20 Hz and MR patient monitors at 1 Hz (Millennia 3155A at 1.5T and Magnitude 3150 MRI at 3T; In vivo, Best, Netherlands).

FIGURE 1.

FIGURE 1

Open in a new tab

Schematic diagram of the study design and key analysis steps.

Processing

An experienced neuroradiologist assessed SVD features of WMH, lacunes, microbleeds, visible PVS, and brain atrophy, using visual ratings on the 1.5T scans, including Fazekas score for WMH, PVS and atrophy scores, and counts of lacunes and microbleeds, which were used to calculate the SVD score (Staals et al., 2014; Blair et al., 2020).

We converted the DICOM files through SPM8 (Wellcome Department of Imaging Neuroscience, London, United Kingdom) (Friston, 2007). We discarded dummy scans before aligning the remaining volumes to the mean BOLD image of each patient in SPM8. We coregistered the T1-w images to the T2-w space using rigid-body registration calculating the transformation between T2-w and mean BOLD image spaces using FLIRT (FMRIB Analysis Group, Oxford, United Kingdom) (Jenkinson et al., 2002). We calculated the WMH and intracranial volume (ICV) from the 1.5T scans as previously described (Blair et al., 2020).

We converted the CO2 data to ETCO2 by using in-house MATLAB (MathWorks, Inc., MA, United States) code to identify CO2 peaks as previously described (Thrippleton et al., 2018). We resampled the ETCO2 data to match the temporal resolution of the BOLD data prior to linear regression.

We applied linear regression using in-house Matlab code to determine region-wise CVR magnitude and delay as described in Thrippleton et al. (2018). Briefly, we performed multiple linear regression with the time-shifted ETCO2 profile and volume number (to adjust for signal drift) regressors and percentage signal change relative to baseline as the dependent variable. The regression model was evaluated for a range of time shifts, and the model with lowest sum-of-square residuals was selected. CVR magnitude was reported as the regression coefficient for the optimally time-shifted ETCO2; CVR delay was reported as the optimal ETCO2 time shift plus 4 s (to account for the travel time of exhaled gas from the breathing circuit to the CO2 sensor). Heart rate and respiratory rate were not included as nuisance regressors as the acquisition was not synchronized to the physiological data and given the potential for aliasing.

Regions of Interest for CVR Assessment

Due to the limited voxelwise contrast-to-noise, we chose 14 regions of interest (ROIs) to sample WM (frontal, periventricular, posterior, and centrum semiovale) and subcortical GM (caudate head, putamen, thalamus) regions affected in SVD (Thrippleton et al., 2018). We manually drew the regions on the coregistered 1.5T T1-w image in FSLview (FMRIB Analysis Group, Oxford, United Kingdom) following an established protocol (Thrippleton et al., 2018) and transformed the masks into the 3T T2-w space using FLIRT before thresholding, binarizing, and manually correcting the masks as needed to avoid misclassification of tissue. Manually defined stroke masks were used to exclude lesions. We coregistered the voxelwise CVR magnitude maps into the T2-w image using FLIRT and manually excluded blooming around the large veins and venous sinuses based on the voxelwise CVR magnitude maps before registering the ROIs to the mean BOLD image and calculating CVR magnitude and delay in each region at 1.5T and 3T using FSLview. We fitted the CVR for each region separately before averaging the CVR magnitude and delay values in WM and subcortical GM to calculate representative values.

Statistical Analysis

We applied linear mixed models using R (v3.6.3) to assess the effect of tissue type (subcortical GM/WM) on CVR magnitude and delay adjusting for field strength. We plotted WM, subcortical GM, and ROI-based CVR magnitude and delay using scatterplots overlaid with univariable linear regression lines. We performed Wilcoxon signed rank tests to assess differences at 1.5T vs. 3T. Finally, we applied separate multivariable linear regression models to explore associations of CVR magnitude at 1.5T or 3T with age, sex, systolic blood pressure, and key metrics of SVD burden (WMH volume, total Fazekas score, and SVD score) (Blair et al., 2020). For each model, we checked normality of residuals and homogeneity of variance using Q-Q plots, histograms, and plots of residuals vs. fitted values for each model and, consequently, log transformed the WMH volume. No corrections were applied for multiple comparisons (Rothman, 1990; Saville, 1990).

Results

Of the 20 patients, 19 completed CVR scans at both 1.5T and 3T; one participant withdrew after experiencing a panic attack during the scan at 3T. One data set was excluded due to a poor-quality ETCO2 trace and persistent motion in the CVR scan at 3T, leaving 18 patients with complete data at both field strengths. The gas challenge otherwise obtained similar changes within each patient at both the 1.5T and 3T scans (t-test: t = 1.60, confidence interval (CI) = −0.34, 2.48, p = 0.127). Representative CVR magnitude images at 1.5T and 3T are shown in Figure 2.

FIGURE 2.

FIGURE 2

Open in a new tab

Representative voxelwise cerebrovascular reactivity (CVR) magnitude maps at 1.5T (A) and 3T (B) in the visit-specific T2-w space. The higher spatial resolution and CVR magnitude values are evident in the 3T image.

The 18 patients had a mean age of 64 ± 7 (53–76) years; 14 (77.8%) were male, and 11 (61.1%) had a final stroke diagnosis of lacunar and seven (38.9%) of cortical subtype (Table 2). Imaging features of SVD were also common: eight (44%) had periventricular and six (33%) deep Fazekas score ≥2, and the median SVD score was two. The mean time between the 1.5T and 3T scans was 337 ± 103 (108–479) days.

TABLE 2.

Demographic data of patients by SVD score (numerical variables: mean ± standard deviation (if normally distributed) or median (interquartile range); summary statistics: % of group (number); categorical variables presented as median).

SVD score 0–1 (n = 8) SVD score 2–4 (n = 10) All patients (n = 18)
Age at visit 63 ± 7 65 ± 7 64 ± 7
Male 100% (8) 60% (6) 77.8% (14)
Diabetes 12.5% (1) 0% (0) 5.6% (1)
Hypertension 62.5% (5) 100% (10) 83.3% (15)
Systolic blood pressure 137 ± 12 140 ± 13 138 ± 12
Diastolic blood pressure 89 ± 5 89 ± 10 89 ± 8
WMH volume (ml), median (IQR) 6.55 (7.84) 14.11 (22.71) 11.26 (11.34)
WMH volume (% of ICV), median (IQR) 0.45 (0.53) 1.01 (1.22) 0.80 (0.74)
Deep Fazekas (median) 1 1.5 1
Periventricular Fazekas (median) 1 2 1
Total Fazekas score (median) 2 3.5 2
Lacunar subtype 50% (4) 70% (7) 61.1% (11)
Open in a new tab

In subcortical GM compared with WM, independent of field strength, CVR magnitude was higher (1.5T: 0.142 vs. 0.057%/mmHg, 3T: 0.158 vs. 0.062%/mmHg; B = −0.09, CI = −0.10, −0.08, p < 0.001) and delay less (1.5T: 12 vs. 31 s, 3T: 8 vs. 41 s; B = 26, CI = 22, 31, p < 0.001) (Figures 3A,C).

FIGURE 3.

FIGURE 3

Open in a new tab

Box (A,C) and scatterplots (B,D) of mean cerebrovascular reactivity (CVR) magnitude and delay values in subcortical gray and white matter at 1.5 and 3T. Lines of best fit for the subcortical gray/white matter CVR magnitude and delay are shown separately in pink/blue. (B = effect size, CI = confidence interval, p-values uncorrected for multiple comparisons).

WM and Subcortical GM CVR Magnitude and Delay at 1.5T and 3T

We found no material difference in subcortical GM and WM CVR magnitude between 1.5 and 3T using Wilcoxon signed rank tests: subcortical GM (1.5T vs. 3T: 0.142 vs. 0.158%/mmHg; r = −0.30, CI: −0.044, 0.016, p = 0.212); WM (3 vs. 1.5T: 0.057 vs. 0.062%/mmHg; r = −0.33, CI: −0.013, 0.003, p = 0.167) (Figure 3A and Supplementary Table 1).

At 3T, delay tended to be shorter in subcortical GM (1.5 vs. 3T: 8 vs. 12 s; r = 0.33, CI: −2, 9, p = 0.164) and was longer in WM (1.5 vs. 3T: 31 vs. 41 s; r = −0.59, CI: −16, −2, p = 0.010) than at 1.5T (Figure 3C and Supplementary Table 1).

Scatterplots showed that the distribution of CVR magnitude values were narrower at 3T than 1.5T in both subcortical GM (CVR magnitude range at 3T: 0.107, 0.204; at 1.5T: 0.040, 0.235) and WM (CVR magnitude range at 3T: 0.035, 0.093; at 1.5T: 0.016, 0.094) (Figure 3B and Supplementary Table 1). Univariable linear regressions showed patients with higher CVR at 3T had higher CVR at 1.5T in both subcortical GM (B = 0.23, CI: 0, 0.46, p = 0.046) and WMr (B = 0.55, CI: 0.30, 0.80, p < 0.01).

The distribution of CVR delay values was similar at 3T and 1.5T in both subcortical GM (CVR delay range at 3T: −6, 24; at 1.5T: −1, 28) and WM (CVR delay at 3T: 12, 56; at 1.5T: 6, 50) (Figure 3D and Supplementary Table 1). Patients with longer delays at 3T tended to have longer delays at 1.5T in WM (B = 0.40, CI: −0.06, 0.85, p = 0.085), but not subcortical GM using univariable linear regressions.

Regional Differences in CVR Magnitude and Delay

In individual regions, the scatter of CVR magnitude values was mostly, but not always, larger at 1.5T than 3T though there was no obvious pattern for delay values (Figure 4 and Supplementary Table 1). Although regional CVR magnitude values were generally comparable at 3T and 1.5T, delay at 3T tended to be longer in WM and shorter in subcortical GM than at 1.5T.

FIGURE 4.

FIGURE 4

Open in a new tab

Boxplots comparing of (A) CVR magnitude (mag) and (B) delay values in subcortical gray and white matter regions at 1.5 and 3T (L = left, R = right).

Effect of Field Strength on Associations With Demographic and SVD Imaging Variables

Although age, systolic blood pressure, and sex showed similar associations whether measured at 3T or 1.5T, the confidence intervals were broad, and none reached conventional significance (Supplementary Table 2).

We found CVR magnitude tended to be lower in patients with higher WMH volumes, Fazekas scores, and total SVD score at both 1.5 and 3T (Table 3 and Supplementary Figure 1).

TABLE 3.

Associations of cerebrovascular reactivity (CVR) magnitude in subcortical gray and white matter at 1.5T and 3T with key SVD variables using multiple linear regression controlling for age, sex, and systolic blood pressure (n = 18).

1.5T CVR
 3T CVR
White matter Subcortical gray matter White matter Subcortical gray matter
Log transformed WMH volume (norm to ICV) B = −0.033 (−0.065, −0.001) p = 0.045 B = −0.055 (−0.144, 0.035) p = 0.211 B = −0.024 (−0.049, 0.002) p = 0.069 B = −0.013 (−0.061, 0.036) p = 0.578
Periventricular Fazekas score B = −0.017 (−0.033, −0.002) p = 0.034 B = −0.030 (−0.075, 0.015) p = 0.173 B = −0.013 (−0.026, −0.001) p = 0.043 B = −0.011 (−0.035, 0.012) p = 0.320
Deep Fazekas score B = −0.011 (−0.026, 0.005) p = 0.160 B = −0.015 (−0.057, 0.026) p = 0.444 B = −0.008 (−0.020, 0.005) p = 0.201 B = −0.004 (−0.025, 0.018) p = 0.727
Total Fazekas score B = −0.007 (−0.015, 0.001) p = 0.073 B = −0.012 (−0.034, 0.011) p = 0.281 B = −0.005 (−0.012, 0.001) p = 0.093 B = −0.004 (−0.016, 0.008) p = 0.503
SVD score (high vs. low) B = −0.004 (−0.031, 0.024) p = 0.782 B = −0.001 (−0.071, 0.070) p = 0.983 B = −0.013 (−0.033, 0.008) p = 0.197 B = −0.011 (−0.046, 0.025) p = 0.519
Open in a new tab

Results presented as unstandardized B-values (effect size, change in CVR in %/mmHg per unit change in the independent variable), confidence interval and p-value without multiple comparison correction. Small vessel disease (SVD) score dichotomized as high, >1, and low, ≤1.

Discussion

We measured CVR magnitude and delay at 1.5 and 3T in a well-defined SVD cohort considering summary measures for averaged subcortical GM, WM, and 14 ROI-based measurements. CVR magnitude was similar, though more variable, at 1.5T vs. 3T in subcortical GM and WM. Delay was shorter at 3T in subcortical GM and longer at 1.5T in WM. Independent of field strength, we found CVR magnitude was higher and delay shorter in subcortical GM than WM, reflecting previous work (Thomas et al., 2014; Thrippleton et al., 2018).

Effect of Field Strength on CVR Magnitude

Studies investigating the effect of field strength on CVR measurements using BOLD are limited. CVR magnitude was found to be higher at 3T than 1.5T using fixed inhalation hypercapnia (Triantafyllou et al., 2011) and breath-hold paradigms (Peng et al., 2020). Similarly, R2∗-derived CVR magnitude was higher at 7T than 3T using a targeted breathing ETCO2 paradigm (Driver et al., 2010). By contrast, we found that CVR magnitude did not differ materially between 3T and 1.5T though trending higher at 3T. However, there are several technical and methodological differences. Peng et al. (2020) used a breath-hold challenge that depends on compliance reported percentage rather than absolute changes (Tancredi and Hoge, 2013) and did not adjust for ETCO2, which can affect repeatability (Bright and Murphy, 2013). Additionally, they analyzed the signal in cortical GM, which may be more prone to vascular contamination than the subcortical GM regions considered in this work. BOLD CVR is known to be affected by echo time (Triantafyllou et al., 2011) and signal-to-noise ratio (SNR) (Triantafyllou et al., 2005), which can improve sensitivity and specificity to parenchymal response, particularly at 3T. However, the sequences used for this comparison were not independently optimized to maximize sensitivity to CVR-induced changes in the BOLD signal unlike in Triantafyllou et al. (2011). There are also benefits to lower field strengths as 1.5T scanners can show less geometric distortion and signal dropout due to susceptibility effects than at higher field strengths, affecting comparability in regions close to air–tissue boundaries, including the sinuses and base of the skull (Krüger et al., 2001). Blooming artifacts around large veins are also more severe at 3T (Chen et al., 2010).

Differences in Delay

We found that average delay was shorter at 3T in subcortical GM and at 1.5T in WM. Although primarily a biological quantity, which would not be expected to vary with field strength, delay is challenging to measure (Thrippleton et al., 2018). We define delay as the optimal shift between ETCO2 and the BOLD signal, but due to the low SNR in WM (Thomas et al., 2014), particularly at 1.5T, delay values may approach a random distribution over the permitted range. Hence, delay measurements at 3T may better reflect underlying delay values. Although longer delays at 3T tended to be associated with longer delays at 1.5T in WM, there was no obvious association in subcortical GM. However, univariable linear regression is vulnerable to outliers, especially at extreme values, and although the range of delays was similar at both field strengths, the distribution was tighter and trended lower at 3T. The BOLD sequences acquired at 1.5T and 3T also differed in voxel size (4 × 4 × 4 vs. 3 × 3 × 3 mm3); therefore, differing levels of partial volume effect may influence the delay measurements. Overall, differences in delay values should be interpreted cautiously, and direct validation work in isolated vessel preparations or preclinical models to validate the influence of lower SNR and partial volume effect on delay measurements would be beneficial (Stringer et al., 2020).

Regional Differences

Within the individual ROIs, we found generally similar results to the averaged values: mean CVR magnitude was comparable though marginally higher at 3T vs. 1.5T; delay in subcortical GM regions tended to be shorter at 3T than 1.5T; delay in WM regions was typically longer at 3T than at 1.5T. Although region-based measurements improve SNR relative to voxelwise measurements, they are still vulnerable to local BOLD signal differences, which must be accounted for in interpreting results. Venous blooming may affect CVR magnitude and delay values in the caudate head and thalamus; although we excluded voxels for which prominent vessels were visible in the ROIs, less prominent vessels were retained (Thrippleton et al., 2018). Smaller regions, including the caudate head, may be less stable given the small size. Meanwhile, in periventricular WM, CVR magnitude and delay may be altered by nearby venous structures (Nonaka et al., 2003), enhancing signal changes during the CVR paradigm. The higher spatial resolution of the BOLD sequence at 3T vs. 1.5T may allow more accurate identification of tissue boundaries and exclusion of contaminating large vascular structures while also reduce partial volume effect, which may contribute to reduced variance at 3T (Thrippleton et al., 2018).

Associations Between CVR Magnitude, Demographic, and Other SVD Imaging Variables

Although CVR magnitude tended to be lower in patients who were older, male, and had higher blood pressure at both 1.5T and 3T, none of the associations reached conventional statistical significance, likely due to lack of power in this subset of the main study. Nevertheless the direction of effect was broadly consistent with previous work showing lower CVR in older patients (Hund-Georgiadis et al., 2003; Conijn et al., 2012; Gauthier et al., 2015; Blair et al., 2020), males than females (Kastrup et al., 1997; Cupini et al., 2001; Tallon et al., 2020), and in patients with higher blood pressure (Conijn et al., 2012; Haight et al., 2015).

We found that subcortical GM and WM CVR tended to be lower in patients with higher WMH volume, Fazekas (deep, periventricular, and total), and SVD score at both 3T and 1.5T, replicating previously published findings in a larger cohort (of which these patients formed a subgroup) scanned at 1.5T (Blair et al., 2020). Effect sizes were generally similar at 1.5T and 3T, but tended to be marginally higher at 1.5T than 3T for all associations except SVD score, which may be attributable to the small sample size and wider distribution of CVR magnitude values at 1.5T than 3T.

Strength and Limitations

It was impractical to randomize scan ordering; therefore, habituation effects or time between scans may have influenced the results. Although the sample size was higher than for previously reported comparisons between CVR measurements at 3T and 1.5T (n = 9 and 4) (Triantafyllou et al., 2011; Peng et al., 2020), it was lower than some SVD studies using CVR (Blair et al., 2016, 2020). The exploratory multiple linear regression analyses may, therefore, have insufficient statistical power to detect more subtle effects though the results were consistent with previous work (Blair et al., 2020). Larger sample sizes and inclusion of other populations would be beneficial and, along with preclinical validation, may aid the development and wider applicability of CVR. The wider applicability of this comparison is also limited by the specific imaging protocols used though the sequences were appropriate for measuring CVR. We acquired CVR scans with a higher spatial resolution at 3T to mitigate higher blooming effects at 3T, which may also contribute to lower variance in the CVR magnitude. Approaches to sampling tissue vary, including ROI analyses (Triantafyllou et al., 2011) and whole-brain tissue segmentation approaches (Driver et al., 2010; Peng et al., 2020). We manually drew anatomically well-defined ROIs to obtain representative tissue volumes, potentially reducing the partial volume effect at tissue boundaries, the influence of venous blooming (Thrippleton et al., 2018), and atrophy (Catchlove et al., 2018). However, this may affect comparability with some previous studies. Additional analyses considering further regions, including cortical GM, or using voxelwise analysis methods would be worthwhile. Lastly further methodological work is required to assess comparability and encourage greater consensus on best practice. Although the reported CVR magnitude and delay values are comparable to previously reported values (Thrippleton et al., 2018), wider comparisons are challenging due to heterogeneity in the acquisition and processing methods (Sleight et al., 2021). Additionally, we have not explored reproducibility of CVR measurements using fixed CO2 inhalation at 3T although we previously tested reproducibility and different durations of CO2 exposure at 1.5T (Thrippleton et al., 2018).

Conclusion

We demonstrate similar CVR magnitude values at 3T and 1.5T, which showed comparable tissue differences and associations with certain key clinical variables. We found wider scatter of magnitude values at 1.5T than 3T. Although delay differed between 1.5T and 3T depending on the brain regions sampled, this may result from differences in SNR, partial volume effect, and blooming artifact. Measuring and interpreting CVR delay, therefore, remains challenging. Regional variability highlights the importance of optimizing the tissue sampling strategy when designing studies.

Data Availability Statement

The datasets presented in this article are not readily available because the data is stored on an internal database. However, the full individual anonymized dataset supporting the conclusions of this article, along with the study protocol, is available to bona fide researchers via the University of Edinburgh’s Cerebrovascular Diseases Database without undue reservation. Access requests should be submitted to JW along with a description of any planned analyses.

Ethics Statement

The studies involving human participants were reviewed and approved by the UK Health Research Authority National Research Ethics Service Committee East Midlands, Nottingham 1. The patients/participants provided their written informed consent to participate in this study.

Author Contributions

MS: data analysis, drafting, and revision of manuscript. GB: patient recruitment and revision of manuscript. YS: data acquisition, data analysis, and revision of manuscript. IH: data acquisition. DD: data analysis and revision of manuscript. FD: study design, development of the CVR procedure, and revision of manuscript. IM: study design, development of the CVR procedure and analysis techniques, data analysis, and revision of the manuscript. MT: data acquisition, development of the CVR procedure and analysis techniques, data analysis, and revision of the manuscript. JW: study conceptualization and design, development of the CVR procedure and analysis techniques, data analysis, and revision of the manuscript. All authors contributed to the article and approved the submitted version.

Conflict of Interest

The authors declare that the research was conducted in the absence of any commercial or financial relationships that could be construed as a potential conflict of interest.

Acknowledgments

We are grateful to Dr. Francesca Chappell for her advice on the statistical methodology, the radiographers at EIF (WGH), and EIF (QMRI) for their efforts and the patients for taking part.

Footnotes

Funding. Funding for the study was provided by the Chief Scientist Office (Scotland), grant reference ETM/326 and the Wellcome Trust—University of Edinburgh Institutional Strategic Support Fund. Additional support is provided by the European Union Horizon 2020 project No. 666881, “SVDs@Target” (MS, GB, and JW), The Stroke Association Princess Margaret Research Development Fellowship scheme (GB), Alzheimer’s Society (Ref: 252(AS-PG-14-033), GB and JW), the Stroke Association Garfield Weston Foundation Senior Clinical Lectureship (FD), NHS Research Scotland (FD), the Stroke Association Postdoctoral Fellowship (TSAPDF2017/01, DD), the China Scholarships Council/University of Edinburgh (YS), NHS Lothian Research and Development Office (MT), and the Scottish Funding Council through the Scottish Imaging Network, A Platform for Scientific Excellence (SINAPSE) Collaboration (JW). Funding is gratefully acknowledged from the Fondation Leducq (ref no. 16 CVD 05), the Edinburgh and Lothians Health Foundation, and the UK Dementia Research Institute as UK DRI which was funded by the MRC, Alzheimer’s Society and Alzheimer’s Research UK (all JW).

Supplementary Material

The Supplementary Material for this article can be found online at: https://www.frontiersin.org/articles/10.3389/fphys.2021.644837/full#supplementary-material

Click here for additional data file. (207.3KB, docx)

References

  1. Atwi S., Shao H., Crane D. E., da Costa L., Aviv R. I., Mikulis D. J., et al. (2019). BOLD-based cerebrovascular reactivity vascular transfer function isolates amplitude and timing responses to better characterize cerebral small vessel disease. NMR Biomed. 32:e4064. 10.1002/nbm.4064 [DOI] [PubMed] [Google Scholar]
  2. Bernstein M. A., Huston J., III, Ward H. A. (2006). Imaging artifacts at 3.0T. J. Magn. Reson. Imaging 24 735–746. [DOI] [PubMed] [Google Scholar]
  3. Blair G. W., Doubal F. N., Thrippleton M. J., Marshall I., Wardlaw J. M. (2016). Magnetic resonance imaging for assessment of cerebrovascular reactivity in cerebral small vessel disease: a systematic review. J. Cereb. Blood Flow Metab. 36 833–841. 10.1177/0271678x16631756 [DOI] [PMC free article] [PubMed] [Google Scholar]
  4. Blair G. W., Thrippleton M. J., Shi Y., Hamilton I., Stringer M., Chappell F., et al. (2020). Intracranial hemodynamic relationships in patients with cerebral small vessel disease. Neurology 26 e2258–e2269. [DOI] [PMC free article] [PubMed] [Google Scholar]
  5. Bright M. G., Murphy K. (2013). Reliable quantification of BOLD fMRI cerebrovascular reactivity despite poor breath-hold performance. Neuroimage 83 559–568. 10.1016/j.neuroimage.2013.07.007 [DOI] [PMC free article] [PubMed] [Google Scholar]
  6. Catchlove S. J., Parrish T. B., Chen Y., Macpherson H., Hughes M. E., Pipingas A. (2018). Regional cerebrovascular reactivity and cognitive performance in healthy aging. J. Exp. Neurosci. 12:1179069518785151. [DOI] [PMC free article] [PubMed] [Google Scholar]
  7. Chen Z., Caprihan A., Calhoun V. (2010). Effect of surrounding vasculature on intravoxel BOLD signal. Med. Phys. 37 1778–1787. 10.1118/1.3366251 [DOI] [PMC free article] [PubMed] [Google Scholar]
  8. Conijn M. M., Hoogduin J. M., van der Graaf Y., Hendrikse J., Luijten P. R., Geerlings M. I. (2012). Microbleeds, lacunar infarcts, white matter lesions and cerebrovascular reactivity – a 7 T study. Neuroimage 16 950–956. 10.1016/j.neuroimage.2011.08.059 [DOI] [PubMed] [Google Scholar]
  9. Cupini L. M., Diomedi M., Placidi F., Silvestrini M., Giacomini P. (2001). Cerebrovascular reactivity and subcortical infarctions. Arch. Neurol. 58 577–581. [DOI] [PubMed] [Google Scholar]
  10. Driver I., Blockley N., Fisher J., Francis S., Gowland P. (2010). The change in cerebrovascular reactivity between 3 T and 7 T measured using graded hypercapnia. Neuroimage 51 274–279. 10.1016/j.neuroimage.2009.12.113 [DOI] [PubMed] [Google Scholar]
  11. Friston K. J. (2007). “A short history of SPM,” in Statistical Parametric Mapping: The Analysis of Funtional Brain Images 1st ed., eds Penny W. D., Friston K. J., Ashburner J. T., Kiebel S. J., Nichols T. (Boston, MA: Academic Press; ). [Google Scholar]
  12. Gati J. S., Menon R. S., Ugurbil K., Rutt B. K. (1997). Experimental determination of the BOLD field strength dependence in vessels and tissue. Magn. Reson. Med. 38 296–302. 10.1002/mrm.1910380220 [DOI] [PubMed] [Google Scholar]
  13. Gauthier C. J., Lefort M., Mekary S., Desjardins-Crepeau L., Skimminge A., Iversen P., et al. (2015). Hearts and minds: linking vascular rigidity and aerobic fitness with cognitive aging. Neurobiol. Aging. 36 304–314. 10.1016/j.neurobiolaging.2014.08.018 [DOI] [PubMed] [Google Scholar]
  14. Haight T. J., Bryan R. N., Erus G., Davatzikos C., Jacobs D. R., D’Esposito M., et al. (2015). Vascular risk factors, cerebrovascular reactivity, and the default-mode brain network. Neuroimage 115 7–16. 10.1016/j.neuroimage.2015.04.039 [DOI] [PMC free article] [PubMed] [Google Scholar]
  15. Heye A. K., Thrippleton M. J., Armitage P. A., Hernández M. D. C. V., Makin S. D., Glatz A., et al. (2016). Tracer kinetic modelling for DCE-MRI quantification of subtle blood–brain barrier permeability. Neuroimage 125 446–455. 10.1016/j.neuroimage.2015.10.018 [DOI] [PMC free article] [PubMed] [Google Scholar]
  16. Hund-Georgiadis M., Zysset S., Naganawa S., Norris D. G., Von Cramon D. Y. (2003). Determination of cerebrovascular reactivity by means of FMRI signal changes in cerebral microangiopathy: a correlation with morphological abnormalities. Cerebrovasc. Dis. 16 158–165. 10.1159/000070596 [DOI] [PubMed] [Google Scholar]
  17. Jenkinson M., Bannister P., Brady M., Smith S. (2002). Improved optimization for the robust and accurate linear registration and motion correction of brain images. Neuroimage 17 825–841. 10.1006/nimg.2002.1132 [DOI] [PubMed] [Google Scholar]
  18. Kastrup A., Thomas C., Hartmann C., Schabet M. (1997). Sex dependency of cerebrovascular CO2 reactivity in normal subjects. Stroke 28 2353–2356. 10.1161/01.str.28.12.2353 [DOI] [PubMed] [Google Scholar]
  19. Krüger G., Kastrup A., Glover G. H. (2001). Neuroimaging at 1.5 T and 3.0 T: comparison of oxygenation-sensitive magnetic resonance imaging. Magn. Reson. Med. 45 595–604. 10.1002/mrm.1081 [DOI] [PubMed] [Google Scholar]
  20. Liu P., De Vis J. B., Lu H. (2019). Cerebrovascular reactivity (CVR) MRI with CO2 challenge: a technical review. Neuroimage 187 104–115. 10.1016/j.neuroimage.2018.03.047 [DOI] [PMC free article] [PubMed] [Google Scholar]
  21. Nonaka H., Akima M., Hatori T., Nagayama T., Zhang Z., Ihara F. (2003). Microvasculature of the human cerebral white matter: arteries of the deep white matter. Neuropathology 23 111–118. 10.1046/j.1440-1789.2003.00486.x [DOI] [PubMed] [Google Scholar]
  22. Peng S. L., Yang H. C., Chen C. M., Shih C. T. (2020). Short- and long-term reproducibility of BOLD signal change induced by breath-holding at 1.5 and 3 T. NMR Biomed. 33:e4195. [DOI] [PubMed] [Google Scholar]
  23. Rothman K. J. (1990). No adjustments are needed for multiple comparisons. Epidemiology 1 43–46. 10.1097/00001648-199001000-00010 [DOI] [PubMed] [Google Scholar]
  24. Sam K., Conklin J., Holmes K. R., Sobczyk O., Poublanc J., Crawley A. P., et al. (2016). Impaired dynamic cerebrovascular response to hypercapnia predicts development of white matter hyperintensities. Neuroimage Clin. 11 796–801. 10.1016/j.nicl.2016.05.008 [DOI] [PMC free article] [PubMed] [Google Scholar]
  25. Saville D. J. (1990). Multiple comparison procedures: the practical solution. Am. Stat. 44 174–180. 10.1080/00031305.1990.10475712 [DOI] [Google Scholar]
  26. Silvennoinen M. J., Clingman C. S., Golay X., Kauppinen R. A., Van Zijl P. C. M. (2003). Comparison of the dependence of blood R2 and R on oxygen saturation at 1.5 and 4.7 Tesla. Mag. Reson. Med. 49 47–60. 10.1002/mrm.10355 [DOI] [PubMed] [Google Scholar]
  27. Sleight E., Stringer M. S., Marshall I., Wardlaw J. M., Thrippleton M. J. (2021). Cerebrovascular reactivity measurement using magnetic resonance imaging: a systematic review. Front. Physiol. 12:643468. 10.3389/fphys.2021.643468 [DOI] [PMC free article] [PubMed] [Google Scholar]
  28. Staals J., Makin S. D., Doubal F. N., Dennis M. S., Wardlaw J. M. (2014). Stroke subtype, vascular risk factors, and total MRI brain small-vessel disease burden. Neurology 83 1228–1234. 10.1212/wnl.0000000000000837 [DOI] [PMC free article] [PubMed] [Google Scholar]
  29. Stringer M. S., Lee H., Huuskonen M. T., MacIntosh B. J., Brown R., Montagne A., et al. (2020). A review of translational magnetic resonance imaging in human and rodent experimental models of small vessel disease. Transl. Stroke Res. 12 15–30. 10.1007/s12975-020-00843-8 [DOI] [PMC free article] [PubMed] [Google Scholar]
  30. Tallon C. M., Barker A. R., Nowak-Fluck D., Ainslie P. N., McManus A. M. (2020). The influence of age and sex on cerebrovascular reactivity and ventilatory response to hypercapnia in children and adults. Exp. Physiol. 105 1090–1101. 10.1113/ep088293 [DOI] [PubMed] [Google Scholar]
  31. Tancredi F. B., Hoge R. D. (2013). Comparison of cerebral vascular reactivity measures obtained using breath-holding and CO2 inhalation. J. Cereb. Blood Flow Metab. 33 1066–1074. 10.1038/jcbfm.2013.48 [DOI] [PMC free article] [PubMed] [Google Scholar]
  32. Thomas B. P., Liu P., Park D. C., van Osch M. J., Lu H. (2014). Cerebrovascular reactivity in the brain white matter: magnitude, temporal characteristics, and age effects. J. Cereb. Blood Flow Metab. 34 242–247. 10.1038/jcbfm.2013.194 [DOI] [PMC free article] [PubMed] [Google Scholar]
  33. Thrippleton M. J., Shi Y., Blair G., Hamilton I., Waiter G., Schwarzbauer C., et al. (2018). Cerebrovascular reactivity measurement in cerebral small vessel disease: rationale and reproducibility of a protocol for MRI acquisition and image processing. Int. J. Stroke 13 195–206. 10.1177/1747493017730740 [DOI] [PubMed] [Google Scholar]
  34. Triantafyllou C., Hoge R. D., Krueger G., Wiggins C. J., Potthast A., Wiggins G. C., et al. (2005). Comparison of physiological noise at 1.5 T, 3 T and 7 T and optimization of fMRI acquisition parameters. Neuroimage 26 243–250. 10.1016/j.neuroimage.2005.01.007 [DOI] [PubMed] [Google Scholar]
  35. Triantafyllou C., Wald L. L., Hoge R. D. (2011). Echo-time and field strength dependence of BOLD reactivity in veins and parenchyma using flow-normalized hypercapnic manipulation. PLoS One 6:e24519. 10.1371/journal.pone.0024519 [DOI] [PMC free article] [PubMed] [Google Scholar]
  36. van Niftrik C. H. B., Piccirelli M., Bozinov O., Pangalu A., Fisher J. A., Valavanis A., et al. (2017). Iterative analysis of cerebrovascular reactivity dynamic response by temporal decomposition. Brain Behav. 7:e00705. 10.1002/brb3.705 [DOI] [PMC free article] [PubMed] [Google Scholar]
  37. Wardlaw J. M., Doubal F., Armitage P., Chappell F., Carpenter T., Muñoz Maniega S., et al. (2009). Lacunar stroke is associated with diffuse blood–brain barrier dysfunction. Ann. Neurol. 65 194–202. 10.1002/ana.21549 [DOI] [PubMed] [Google Scholar]
  38. Wardlaw J. M., Smith C., Dichgans M. (2019). Small vessel disease: mechanisms and clinical implications. Lancet Neurol. 18 684–696. 10.1016/s1474-4422(19)30079-1 [DOI] [PubMed] [Google Scholar]
  39. Wardlaw J. M., Smith E. E., Biessels G. J., Cordonnier C., Fazekas F., Frayne R., et al. (2013). Neuroimaging standards for research into small vessel disease and its contribution to ageing and neurodegeneration. Lancet Neurol. 12 822–838. [DOI] [PMC free article] [PubMed] [Google Scholar]

Associated Data

This section collects any data citations, data availability statements, or supplementary materials included in this article.

Supplementary Materials

Click here for additional data file. (207.3KB, docx)

Data Availability Statement

The datasets presented in this article are not readily available because the data is stored on an internal database. However, the full individual anonymized dataset supporting the conclusions of this article, along with the study protocol, is available to bona fide researchers via the University of Edinburgh’s Cerebrovascular Diseases Database without undue reservation. Access requests should be submitted to JW along with a description of any planned analyses.

Articles from Frontiers in Physiology are provided here courtesy of Frontiers Media SA

RESOURCES