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Impact of cerebral blood flow and amyloid load on SUVR bias

EJNMMI Research volume 12, Article number: 29 (2022) Cite this article

Abstract

Background

Despite its widespread use, the semi-quantitative standardized uptake value ratio (SUVR) may be biased compared with the distribution volume ratio (DVR). This bias may be partially explained by changes in cerebral blood flow (CBF) and is likely to be also dependent on the extent of the underlying amyloid-β (Aβ) burden. This study aimed to compare SUVR with DVR and to evaluate the effects of underlying Aβ burden and CBF on bias in SUVR in mainly cognitively unimpaired participants. Participants were scanned according to a dual-time window protocol, with either [18F]flutemetamol (N = 90) or [18F]florbetaben (N = 31). The validated basisfunction-based implementation of the two-step simplified reference tissue model was used to derive DVR and R1 parametric images, and SUVR was calculated from 90 to 110 min post-injection, all with the cerebellar grey matter as reference tissue. First, linear regression and Bland–Altman analyses were used to compare (regional) SUVR with DVR. Then, generalized linear models were applied to evaluate whether (bias in) SUVR relative to DVR could be explained by R1 for the global cortical average (GCA), precuneus, posterior cingulate, and orbitofrontal region.

Results

Despite high correlations (GCA: R2 ≥ 0.85), large overestimation and proportional bias of SUVR relative to DVR was observed. Negative associations were observed between both SUVR or SUVRbias and R1, albeit non-significant.

Conclusion

The present findings demonstrate that bias in SUVR relative to DVR is strongly related to underlying Aβ burden. Furthermore, in a cohort consisting mainly of cognitively unimpaired individuals, the effect of relative CBF on bias in SUVR appears limited. EudraCT Number: 2018-002277-22, registered on: 25-06-2018.

Background

At present, amyloid positron emission tomography (PET) imaging is routinely used in specialized memory clinics to support the diagnosis of Alzheimer’s disease (AD). Routinely, a static acquisition is performed and the resulting image is used to visually determine the presence or absence of amyloid-beta (Aβ) plaques by a trained nuclear medicine physician [1, 2]. In addition to their clinical use, static scans have also been widely used for research purposes, mainly because of their technical and logistical simplicity. From these scans, the commonly used standardized uptake value ratio (SUVR) can be calculated, by simply dividing tracer uptake in the target by that in a reference region. Nevertheless, previous studies have demonstrated that SUVR can be biased compared with the non-displaceable binding potential (BPND) or distribution volume ratio (DVR = BPND + 1) derived from a dynamic scan [3,4,5]. In particular, SUVR can be affected by changes in cerebral blood flow (CBF), tracer clearance, and/or extraction fraction [3, 4, 6]. The effects of relative CBF have been illustrated in a longitudinal observational study that reported a decrease in [11C]PiB SUVR in a clinical population, while DVR remained unchanged, and accompanying simulations demonstrated that this decrease in SUVR was likely related to a decrease in relative CBF (R1) [4]. Nonetheless, the explanatory effect of changes in relative CBF on SUVR needs to be further evaluated in larger clinical data sets and for other (amyloid) tracers, given that each tracer has distinct kinetics.

The degree of bias in SUVR also depends on the extent of the Aβ burden [3], and, in the case of AD, it is known that disease stage and Aβ burden are not linearly correlated [7]. Yet, most AD studies have compared SUVR and DVR only at a (diagnostic) group level, and therefore, the relationship between bias and extent of underlying Aβ burden is not fully characterized [5, 8, 9].

Over the last decade, the focus of amyloid PET studies has shifted to the early phases of AD, emphasizing the importance of understanding the bias in SUVR in a pre-dementia group [10,11,12]. In particular, considering that confounding factors such as changes in CBF, tracer clearance, and extraction fraction may not be constant throughout the disease, their impact on SUVR could also differ in this pre-clinical population compared with AD dementia patients [3, 13, 14].Therefore, the purpose of the present study was to investigate bias in SUVR relative to DVR in elderly individuals and assess to what extent this bias can be explained by underlying Aβ burden and CBF for both [18F]flutemetamol and [18F]florbetaben.

Materials and methods

Participants

The study included N = 121 participants from the AMYloid Imaging to Prevent Alzheimer’s Disease (AMYPAD) Prognostic and Natural History Study (PNHS) [15], who were scanned across four different centres: The University of Edinburgh (UEDIN), Barcelona βeta Brain Research Center (BBRC), Amsterdam University Medical Centre, location VUmc (Amsterdam UMC, VUmc), and University of Geneva (UNIGE). All participants had at least one PET and one T1-weighted MR scan available, and visual assessment of the PET scans was performed locally by a trained nuclear medicine physician according to the manufacturer’s reading guidelines [1, 2]. Readers were blinded to the quantitative outcome measure of the scans. In addition, participants underwent standard neurological screening and neuropsychological assessment (e.g. mini-mental state examination, MMSE) and information regarding their APOE-ε4 status was available. Before participating in the study, all participants provided written informed consent in accordance with the Declaration of Helsinki. Study protocols were approved by all local Medical Ethics Review Committees. EudraCT Number: 2018-002277-22, registered on: 25-06-2018, https://www.clinicaltrialsregister.eu/ctr-search/trial/2018-002277-22/NL.

Image acquisition

Prior to each PET scan, an MR sequence (MRAC) or low-dose CT (ldCT) was acquired for attenuation correction purposes (Additional file 1: Table S1 specifies which centres used an MR and which a CT scanner). Participants then received a bolus injection of either [18F]flutemetamol (N = 90, 186 ± 10 MBq) or [18F]florbetaben (N = 31, 283 ± 20 MBq) and underwent a dynamic PET scan according to a dual-time window protocol [16]. This scanning protocol consisted of an early dynamic scan from 0 to 30 min post-injection (p.i.) followed by a break of 60 min, and then a late dynamic scan from 90 to 110 min p.i. For each scanner, recommended clinical reconstruction settings for that scanner were used and scans were reconstructed into 18 frames (6 × 5, 3 × 10, 4 × 60, 2 × 150, 2 × 300, and 1 × 600 s) for the early scan, and four frames (4 × 300 s) for the late scan. All sites applied the following corrections: detector normalization, dead time, attenuation, scatter, decay, and randoms. Site-specific reconstruction methods can be found in Additional file 1: Table S1.

Image QC and processing

First, a quality control (QC) check of the image meta-data was performed (i.e. frame start times, duration, and the number of frames) and the presence of motion between PET scans, and corresponding MRAC or ldCT, was evaluated. In the case of severe motion (> 5 mm), these scans were excluded from analyses. In addition, it was verified whether the whole brain was in the field of view and whether no technical errors occurred, such as a delay in acquisition start time. Next, presence of between-frame motion was assessed visually. Then, both early and late phases of the PET scan were coregistered to the T1-weighted MR scan using rigid registration and the resulting PET scans were resampled to have the same voxel size as the T1-weighted MR. This was done to prevent changes to the predefined region of interest (ROI) template images, which were already in the same space as the T1-weighted MR scan. Following this step, coregistered PET images were combined and the resulting scan was divided into five blocks of 10 min duration (A: frames 1–15, B: frames 16–17, C: frame 18, D: frames 19–20, and E: frames 21–22). Presence of motion between blocks was assessed visually, by comparing whether contours between blocks were overlapping. Next, using rigid co-registration (based on Elastix software), blocks were co-registered and the registration parameters were saved [17, 18]. Based on a visual assessment and the registration parameters, it was determined whether motion exceeded the maximum allowed threshold (1 mm translation in each direction) and should be corrected for (using Elastix-based rigid co-registration). Subsequently, subject-specific regions of interest generated using Learning Embeddings for Atlas Propagation (LEAP) [19] (in T1-weighted MR space) were applied to the combined PET scan to extract a reference tissue time-activity curve (TAC) of the cerebellar grey matter. As regions of sufficient volume were used (> 5 ml), no partial volume corrections were performed.

Parametric analysis

Interpolation of the missing data points of the reference tissue TAC (corresponding to the 60 min break) was performed using the reversible two tissue compartment model (4-rate constants) with additional blood volume fraction parameter (2T4k_Vb) and a tracer-specific plasma input function as described previously [16]. Visual QC of the interpolated reference tissue TAC was performed to assess whether the interpolation of the missing data points had a smooth connection with the measured data. In the case of sub-optimal interpolation (i.e. clear discontinuity between interpolated and measured data), cubic interpolation was used as alternative (N = 8). Next, parametric modelling was performed using the basisfunction-based implementation of the two-step simplified reference tissue model (SRTM2) [20], as implemented in the PPET software package [21] and validated previously [22], to compute parametric BPND and relative tracer delivery (R1) images. For SRTM2, k2’ was determined by taking the median k2’ across all voxels with a BPND higher than 0.05 from a first run using receptor parametric mapping (RPM) [23, 24]. In addition, SUVR was calculated from 90 to 110 min p.i. To allow for comparability between metrics, DVR was calculated as BPND + 1. Finally, the subject-specific global cortical average (GCA) template, which is a composite region consisting of frontal, temporal, parietal, and insular cortices, precuneus, and striatum [25], was applied to the parametric data to obtain global SUVR and DVR values. In addition, the subject-specific ROIs generated using LEAP were used to extract values for regions that are known to show early accumulation of Aβ plaques: precuneus, posterior cingulate cortex (PCC), and orbitofrontal cortex (OFC) [12, 26, 27].

Statistical analysis

All statistical analyses were performed in R (version:4.0.3; R Foundation for Statistical Computing, Vienna, Austria) and stratified per tracer. A statistically significant result was defined as p < 0.05; no corrections for multiple comparisons were applied.

First, demographic differences between Aβ-positive and negative participants (based on a visual assessment) were investigated using t tests (or in the case of non-normal distribution, Mann–Whitney U-tests) and Chi-square tests.

Relationship between SUVR and DVR

Linear regression analyses were used to assess the relationships between SUVR and DVR. In addition, Bland–Altman analyses [28] were used to assess potential bias between these metrics, and the presence of proportional bias was determined visually for the GCA and three early regions. When present, proportional bias was further evaluated by fitting a regression line through the Bland–Altman plot.

Relationship between (bias in) SUVR and relative CBF

First, bias in SUVR relative to DVR (SUVRbias) was calculated ((SUVR-DVR)/DVR*100%). Then, generalized linear models (GLMs) were constructed to understand whether the relative tracer delivery (R1) could explain the remaining variance of either SUVR or SUVRbias beyond the main predictor, DVR. Note, the covariate “centre” is only included for [18F]flutemetamol.

$$\begin{aligned} & {\text{SUVR}} \sim {\text{DVR}} + R_{1} + {\text{DVR}}*R_{1} + {\text{Age}} + {\text{Sex}} + {\text{APOE}} - \varepsilon 4 + {\text{centre}} \\ & {\text{SUVR}}_{{{\text{bias}}}} \sim {\text{DVR}} + R_{1} + {\text{DVR}}*R_{1} + {\text{Age}} + {\text{Sex}} + {\text{APOE}} - \varepsilon 4 + {\text{centre}} \\ \end{aligned}$$

Before applying the GLMs to the data, all predictors (DVR, R1, and DVR*R1) and covariates (age, sex, APOE-ε4 carriership, and centre in the case of [18F]flutemetamol) were correlated with each other to check for collinearity. This was done using Pearson’s correlation, point-biserial correlation, and Goodman Kruskal’ lambda for continuous, continuous and categorical or categorical variables, respectively. In the case of high overlap (r ≥ 0.70) [29], the variables were correlated with the dependent variable (SUVR and SUVRbias) to determine which one should be deleted from the model to remove redundancy, i.e. the one with the lowest correlation. All analyses with the final model were performed using the GCA, as well as with the three early regions.

Results

Participants

Participant characteristics are shown in Table 1. Most participants were cognitively unimpaired (N = 104), while a minority (N = 17) showed impairment to some extent, based upon the clinical dementia rating (CDR) score (CDR = 0.5). For participants scanned with [18F]flutemetamol, 21.1% (19/90) were visually assessed as Aβ-positive, while for participants scanned with [18F]florbetaben, this was 38.7% (12/31). Furthermore, Aβ-positive participants scanned with [18F]flutemetamol were slightly older than the Aβ-negative group (p < 0.01). As expected, the proportion of APOE-ε4 carriers and the overall amyloid burden (in SUVR and DVR units) were higher among Aβ-positive compared with Aβ-negative participants for both tracers, while no differences were observed in R1 (Fig. 1).

Table 1 Participant demographics
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Fig. 1
figure 1

Parameter distribution across tracers. Violin plots showing the distribution of a DVR, b SUVR and c R1 for Aβ positive and negative scans. Small boxplots inside the violin plots display median and quartile range of the distribution

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Relationship between SUVR and DVR

High correlations were observed between global SUVR and DVR ([18F]flutemetamol: R2 = 0.85 [18F]florbetaben: R2 = 0.95, Fig. 2), as for early regions, with small differences between regions ([18F]flutemetamol precuneus: R2 = 0.85, OFC: R2 = 0.86, PCC: R2 = 0.82, [18F]florbetaben precuneus: R2 = 0.93, OFC: R2 = 0.87, PCC: R2 = 0.85).

Fig. 2
figure 2

Relationship between DVR and SUVR. Correlation and Bland–Altman plots to assess the relationship between global cortical DVR and SUVR for a [18F]flutemetamol and b [18F]florbetaben. Dotted lines corresponds to 95% Limits of Agreement. **p < 0.001, VR: visual read

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SUVR showed an overestimation compared with global DVR for both tracers ([18F]flutemetamol mean bias: 0.29, 95% limits of agreement (LoA) 0.03–0.54, and [18F]florbetaben mean bias: 0.22 95% LoA 0.05–0.38), which was strongly proportional to the underlying amyloid burden, and slightly larger for [18F]flutemetamol ([18F]flutemetamol: R2 = 0.70, slope = 0.56 and intercept = − 0.48, [18F]florbetaben: R2 = 0.65, slope = 0.31 and intercept = − 0.20, Fig. 2). For each of the early regions, a similar pattern in terms of overestimation and proportional bias was observed, although for most early regions, the proportionality was slightly stronger ([18F]flutemetamol precuneus: R2 = 0.81, slope = 0.74 and intercept = − 0.79, OFC: R2 = 0.74, slope = 0.59 and intercept = − 0.54, PCC: R2 = 0.73, slope = 0.66 and intercept = − 0.56, and [18F]florbetaben precuneus: R2 = 0.70, slope = 0.39 and intercept = − 0.32, OFC: R2 = 0.44, slope = 0.31 and intercept = − 0.23, PCC: R2 = 0.61, slope = 0.48 and intercept = − 0.35).

Relationship between independent variables

The univariate correlation analysis between all predictor (DVR, R1, and DVR*R1) and covariate variables (age, sex, APOE-ε4 carriership, and centre in the case of [18F]flutemetamol) demonstrated high correlations only between DVR and DVR*R1 (range r:0.70–0.91). Comparisons with the dependent variables showed higher correlations between DVR and SUVR or SUVRbias (range r:0.91–0.97, 0.24–0.60, respectively) than between DVR*R1 and SUVR or SUVRbias (range r:0.57–0.87, 0.14–0.46, respectively). Therefore, GLMs were constructed without interaction terms, which resulted in the following models (1a and b). Note, the covariate “centre” is only included for [18F]flutemetamol.

$${\text{SUVR}} \sim {\text{DVR}} + R_{1} + {\text{Age}} + {\text{Sex}} + {\text{APOE}} - \varepsilon 4 + {\text{centre}}$$
(1a)
$${\text{SUVR}}_{{{\text{bias}}}} \sim {\text{DVR}} + R_{1} + {\text{Age}} + {\text{Sex}} + {\text{APOE}} - \varepsilon 4 + {\text{centre}}$$
(1b)

Relationship between SUVR and relative CBF

As expected, there was a significant relationship between SUVR and DVR for both tracers across regions (range coefficient estimate [18F]flutemetamol: 1.60–1.84, [18F]florbetaben: 1.31–1.43, p < 0.001, Tables 2 and 3, Additional file 1: Table S2a-f). In addition, for both tracers there were negative associations between SUVR and R1 for the GCA (coefficient estimate [18F]flutemetamol: − 0.20, [18F]florbetaben: − 0.17, Fig. 3), PCC (coefficient estimate [18F]flutemetamol: − 0.20, [18F]florbetaben: − 0.21) and, in the case of [18F]flutemetamol, for the precuneus (coefficient estimate: − 0.20), albeit not statistically significant (ns) (Tables 2 and 3, Additional file 1: Table S2a,b,d). For [18F]flutemetamol specifically, a statistically significant association was also observed between SUVR and centre UNIGE, for the GCA and OFC (coefficient estimate: − 0.13 and 0.16, for both regions, respectively, p < 0.05, Table 2, Additional file 1: Table S2c). No statistically significant associations were observed between SUVR and the other independent variables.

Table 2 Relationship between (bias in) SUVR and independent variables for [18F]flutemetamol
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Table 3 Relationship between (bias in) SUVR and independent variables for [18F]florbetaben
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Fig. 3
figure 3

Relationship between global cortical relative tracer delivery (R1) and amyloid burden. Correlation plots shown for a [18F]flutemetamol and b [18F]florbetaben. VR: visual read

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Relationship between bias in SUVR and relative CBF

For both tracers, positive associations were reported between SUVRbias and DVR across regions (range coefficient estimate [18F]flutemetamol: 13.54–33.49%, p < 0.05 and [18F]florbetaben: 9.46–17.94%, statistically significant only for the precuneus p < 0.05, Tables 2 and 3, Additional file 1: Table S2a-f). In addition, negative associations were observed between SUVRbias and R1 for the GCA (coefficient estimate [18F]flutemetamol: − 14.63%, [18F]florbetaben: − 13.43%, Fig. 3), PCC (coefficient estimate [18F]flutemetamol: − 9.99%, [18F]florbetaben: − 17.63%) and, in the case of [18F]flutemetamol, also for the precuneus and OFC (coefficient estimate: − 8.96% and − 6.77%, for both regions, respectively), albeit not statistically significant (Tables 2 and 3, Additional file 1: Table S2a-c,e). For [18F]flutemetamol, significant, positive associations were observed between SUVRbias and APOE-ε4 (coefficient estimate precuneus: 3.30%, p < 0.05) and age (coefficient estimate PCC: 0.24%, p < 0.05), although with small coefficient estimates. Finally, associations between SUVRbias and centre UNIGE and Amsterdam UMC were observed for the GCA (coefficient estimate: 6.32%, ns and − 10.16%, p < 0.05) and OFC (coefficient estimate: 5.99% and − 12.17%, ns), for both centres, respectively (Table 2, Additional file 1: Table S2c). No statistically significant associations were observed between SUVRbias and the other independent variables.

Discussion

The present study investigated whether bias in SUVR relative to DVR could be explained by factors such as underlying Aβ burden and relative CBF (as measured by R1). For both tracers, strong correlations were observed between SUVR and DVR, although SUVR overestimated DVR, and the magnitude of overestimation was positively associated with the degree of Aβ burden. Furthermore, negative associations were observed between SUVR or SUVRbias and R1, albeit not statistically significant.

For both tracers, the observed proportional overestimation of SUVR relative to DVR is in line with previous work using [11C]PiB, where similar results in terms of overestimation and proportionality of bias were observed when comparing SUVR with DVR [15]. Carson and colleagues have mathematically demonstrated that target to reference tissue ratios (such as SUVR) overestimate true binding (such as DVR in the present work) at transient equilibrium conditions [3]. In particular, the magnitude of overestimation depends on tracer kinetics, with slower kinetics corresponding to larger overestimation. The present findings are in line with this work, given that a larger overestimation was observed for these Fluorine-18 tracers, as compared with [11C]PiB, which has faster kinetics [15, 30]. In addition, Carson and colleagues showed increased overestimation for high binding regions, as a result of the longer time required to reach equilibrium and the lower tissue clearance rates [3], which is in agreement with the present findings. Together, these findings suggest that in cross-sectional analyses including participants with low amyloid burden, the expected bias in global SUVR will be small, although in early binding regions it might already be substantial. Furthermore, in longitudinal analyses, caution is warranted as this proportional bias can falsely inflate SUVR-based accumulation rates [31]. Accordingly, in intervention trials, changes in SUVR-based accumulation rates may over- or underestimate the actual change in Aβ accumulation, leading to biased conclusions regarding the effectiveness of the drug or intervention. Overestimation of the overall signal (i.e. SUVR) might not be a major issue for anti-amyloid drugs with sufficiently large effects on Aβ pathology [32]; however, it could be of major concern when only small effects are expected, such as in lifestyle-related interventions [33]. In such cases, it would be advised to use quantitative instead of semi-quantitative measures of Aβ burden.

In mostly cognitively unimpaired individuals, there was no statistically significant effect of CBF on SUVRbias, although a negative association was observed between SUVR or SUVRbias and CBF, as measured with R1. These findings appear to be in disagreement with a longitudinal [11C]PiB study of van Berckel and colleagues, which reported decreases in global R1 and concomitant decreases in global SUVR [4]. The discrepancy with the present study is likely due to differences in the study populations included. In the present study, the vast majority of participants were cognitively unimpaired, while in the study of van Berckel et al., these findings were related only to patients with AD dementia. It is known that large changes in CBF primarily occur at later disease stages, which could explain the association between R1 and SUVR in AD dementia patients in the study of van Berckel et al. and the lack of significant association in mainly cognitively unimpaired participants in the present study [7]. Interestingly, most regions showed a negative association between R1 and SUVR or SUVRbias in this study, as would be expected with the progression of AD over time [7, 34, 35]. Furthermore, these findings demonstrate that changes in CBF are still small in mostly CU participants and that the effect on bias in SUVR is limited. However, this might not necessarily be the case when following these elderly individuals over time into advanced disease phases or when investigating disease-modifying drugs with unknown effects on CBF. In those scenarios, first quantitative measures should be acquired in at least a sub-sample of participants (e.g. in mono-centre Phase I and II studies) to understand whether changes in CBF play a role, before continuing with larger Phase II/III studies.

It should be noted that there were some between-tracer differences in terms of the relationship between SUVR and DVR (e.g. the association between global cortical SUVR and DVR was R2 = 0.85 for [18F]flutemetamol and R2 = 0.95 for [18F]florbetaben) and the association between R1 and SUVR or SUVRbias. Nevertheless, differences in the relationship between SUVR and DVR appeared to be smaller for the early ROIs. These between-tracer differences may be partially explained by differences in tracer kinetics, related to tracer clearance, degree of non-specific binding, or adherence to reference tissue assumptions [8, 9]. In addition, differences in demographic factors such as the percentage of Aβ-positive participants, age, sex, or APOE-ε4 carriers, also exerted an effect on the observed relationship between SUVR and DVR, as illustrated by the GLM analyses [15]. Furthermore, differences in these variables and the number of scanned participants per institute likely also explain the significant association between centre and SUVR or SUVRbias for some regions (Additional file 1: Table S3). It is important to note that the large difference in sample size between the two tracer cohorts possibly also played a role; the [18F]flutemetamol cohort consisted of almost three times as many participants (N = 90) compared with the [18F]florbetaben cohort (N = 31). In addition, a limitation of the present work is that it investigated only cross-sectional relationships between SUVR, DVR, and R1, as no longitudinal data were available. However, longitudinal data are currently being collected in these subjects. Thus, in the future, it would be interesting to determine the magnitude of change in R1 over time in early AD stages and assess the relationship with bias in SUVR relative to DVR. Finally, it is important to note that the contribution of tracer clearance from plasma on (bias in) SUVR could not be tested, given that no (metabolite corrected) plasma input data were available in this study.

Conclusion

The present findings show that the degree of bias in SUVR relative to DVR in mostly cognitively unimpaired individuals is directly related to the extent of underlying Aβ burden for both [18F]flutemetamol and [18F]florbetaben, which may be particularly problematic for longitudinal study designs. Furthermore, there were no statistically significant associations between R1 and bias in SUVR relative to DVR, likely because changes in CBF are still limited in participants with early Aβ pathology.

Availability of data and materials

Data used in this study are not openly available at this stage due to ongoing data collection in the study. However, these will be made available to the research community upon end of the project (AMYPAD Prognostic and Natural History Study).

Abbreviations

Aβ:

Amyloid-beta

AD:

Alzheimer’s disease

AMYPAD:

AMYloid Imaging to Prevent Alzheimer’s Disease

BP ND :

Non-displaceable binding potential

CBF:

Cerebral blood flow

DVR:

Distribution volume ratio

18F:

Fluorine-18

MMSE:

Mini-mental state examination

OFC:

Orbitofrontal cortex

PCC:

Posterior cingulate cortex

PET:

Positron emission tomography

PNHS:

Prognostic and Natural History Study

QC:

Quality control

ROI:

Region of interest

RPM:

Receptor parametric mapping

SRTM:

Simplified reference tissue method

SUVR:

Standardized uptake value ratio

TAC:

Time activity curve

2T4k_Vb :

Reversible two tissue compartment model (4-rate constants) with additional blood volume fraction parameter

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Acknowledgements

The authors would like to thank all staff of the various centres for skilful acquisition of the scans.

Funding

The author(s) disclosed receipt of the following financial support for the research, authorship, and/or publication of this article: this project received funding from the EU/EFPIA Innovative Medicines Initiative (IMI) Joint Undertaking (EMIF grant:115372) and the EU-EFPIA IMI-2 Joint Undertaking (grant:115952). This joint undertaking receives support from the European Union’s Horizon 2020 research and innovation program and EFPIA. This communication reflects the views of the authors and neither IMI nor the European Union and EFPIA are liable for any use that may be made of the information contained herein. FB is supported by the NIHR biomedical research centre at UCLH. JDG holds a ‘Ramón y Cajal’ fellowship (RYC-2013-13054) from the Spanish Ministry of Science, Innovation and Universities. VG reports grants from the Swiss National Science Foundation (projects:320030_169876, 320030_185028 and IZSEZ0_188355) and the Velux foundation (project:1123).

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Authors and Affiliations

  1. Amsterdam UMC, Vrije Universiteit Amsterdam, Radiology and Nuclear Medicine, Amsterdam Neuroscience, De Boelelaan 1117, 1081 HV, Amsterdam, The Netherlands

    Fiona Heeman, Maqsood Yaqub, Janine Hendriks, Bart N. M. van Berckel, Lyduine E. Collij, Frederik Barkhof, David Vállez García, Isadora Lopes Alves & Adriaan A. Lammertsma

  2. IXICO Plc, London, UK

    Katherine R. Gray, Richard Manber & Robin Wolz

  3. NIMTLab, Faculty of Medicine, Geneva University, Geneva, Switzerland

    Valentina Garibotto

  4. Division of Nuclear Medicine and Molecular Imaging, Geneva University Hospitals, Geneva, Switzerland

    Valentina Garibotto

  5. Edinburgh Imaging, Queen’s Medical Research Institute, University of Edinburgh, Edinburgh, UK

    Catriona Wimberley & Craig Ritchie

  6. UCL, Institutes of Neurology and Healthcare Engineering, London, UK

    Frederik Barkhof

  7. Barcelonaβeta Brain Research Centre, Pasqual Maragall Foundation, Barcelona, Spain

    Juan Domingo Gispert

  8. Centro de Investigación Biomédica en Red de Bioingeniería, Biomateriales y Nanomedicina (CIBER-BBN), Madrid, Spain

    Juan Domingo Gispert

  9. Department of Experimental and Health Sciences, Universitat Pompeu Fabra, Barcelona, Spain

    Juan Domingo Gispert

  10. IMIM (Hospital del Mar Medical Research Institute), Barcelona, Spain

    Juan Domingo Gispert

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  1. Fiona Heeman
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  2. Maqsood Yaqub
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Consortia

on behalf of the AMYPAD Consortium

Contributions

FH, MY, JDG, FB, DVG, ILA, AAL contributed to the concept and design of the study. MY, LEC, BvB, VG, CW, CR were responsible for acquisition of the data. FH, MY, JH, KRG, RM, RW, CW were responsible for data processing and analyses. FH, MY, JDG, FB, DVG, ILA, AAL, CW, FB were responsible for interpretation of the data. FH, MY, JH, BvB, LEC, KRG, RM, RW, VG, CW, CR, FB, JDG, DVG, ILA, AAL drafted or critically revised the work. All authors read and approved the final manuscript.

Corresponding author

Correspondence to Fiona Heeman.

Ethics declarations

Ethics approval and consent to participate

Study protocols were approved by all local Medical Ethics Review Committees. Before participating in the study, all participants provided written informed consent in accordance with the Declaration of Helsinki.

Consent for publication

Before participating in the study, all participants provided written informed consent in accordance with the Declaration of Helsinki.

Competing interests

VG received financial support for research and/or speaker fees through her institution from Siemens Healthineers, GE Healthcare, Life Molecular Imaging, Cerveau Technologies, Roche, Merck.

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Supplementary Information

Additional file 1

. Impact of cerebral blood flow and amyloid load on SUVR bias.

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Heeman, F., Yaqub, M., Hendriks, J. et al. Impact of cerebral blood flow and amyloid load on SUVR bias. EJNMMI Res 12, 29 (2022). https://doi.org/10.1186/s13550-022-00898-8

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Keywords

  • Alzheimer’s disease
  • Amyloid PET
  • Cerebral blood flow
  • Quantification
  • SUVR bias