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The purpose of this study was to compare the diagnostic accuracy of glucose metabolism and amyloid deposition as demonstrated by 18F-FDG and Pittsburg Compound B (PiB) PET to evaluate subjects with cognitive impairment.
Subjects were selected from existing participants in the Mayo Alzheimer’s Disease Research Center or Alzheimer’s Disease Patient Registry programs. A total of 20 healthy controls and 17 amnestic mild cognitive impairment (aMCI), 6 nonamnestic mild cognitive impairment (naMCI), and 13 Alzheimer disease (AD) subjects were imaged with both PiB and 18F-FDG PET between March 2006 and August 2007. Global measures for PiB and 18F-FDG PET uptake, normalized to cerebellum for PiB and pons for 18F-FDG, were compared. Partial-volume correction, standardized uptake value (SUV), and cortical ratio methods of image analysis were also evaluated in an attempt to optimize the analysis for each test.
Significant discrimination (P < 0.05) between controls and AD, naMCI and aMCI, naMCI and AD, and aMCI and AD by PiB PET measurements was observed. The paired groupwise comparisons of the global measures demonstrated that PiB PET versus 18F-FDG PET showed similar significant group separation, with only PiB showing significant separation of naMCI and aMCI subjects.
PiB PET and 18F-FDG PET have similar diagnostic accuracy in early cognitive impairment. However, significantly better group discrimination in naMCI and aMCI subjects by PiB, compared with 18F-FDG, was seen and may suggest early amyloid deposition before cerebral metabolic disruption in this group.
Imaging that can detect functional or pathophysiologic change in the brain holds great promise for diagnostic and therapy assessment uses in patients with Alzheimer disease (AD). 18F-FDG PET can identify patients with a high potential to convert from mild cognitive impairment (MCI), a prodromal stage of neurodegenerative disease, to AD and predict development of AD in elderly patients and other cognitively healthy high-risk groups (1,2). Clinical studies with 18F-FDG PET suggest that the likelihood of a clinical response to therapy can be predicted by 18F-FDG uptake (3), and 18F-FDG PET has been used successfully in phase I neurogenesis trials (4).
Amyloid plaques have been imaged in the human brain using Pittsburg Compound B (PiB) PET (5). The specific pattern of uptake of PiB in human AD subjects has been demonstrated to represent the typical distribution of amyloid-affected regions of the brain, as observed pathologically (6–9). Therefore, PiB PET may offer improved accuracy in the characterization of subjects with memory complaints and may aid in antiamyloid therapy trials.
It has been shown that cortical PiB binding levels in healthy elderly volunteers can be as high as those in AD subjects (10). The significance of this finding is not yet certain, as longitudinal data are still being collected, but 2 possible explanations are nonpathologic amyloid accumulation or preclinical disease amyloid deposition. Recent data have also shown that MCI subjects with PiB accumulation are more likely to convert to AD than those without (11). 18F-FDG and PiB appear, then, to have similar predictive value in this regard, thus warranting a comparison of PiB and 18F-FDG imaging in early neurodegenerative disease.
MCI subjects provide an interesting group in which to investigate the early deposition of brain amyloid. Nevertheless, not all MCI subjects convert to AD. There are notably several subtypes of MCI, some of which may be less likely to progress to probable AD. On both 18F-FDG and PiB, MCI subjects show variable imaging abnormalities, which may reflect the heterogeneous nature of the cohort. Therefore, we included in this evaluation a subset of nonamnestic MCI (naMCI) subjects who may be less at risk for development of AD than amnestic MCI (aMCI) subjects (12,13) and may provide better test-group stratification for evaluating imaging characterization accuracy in the MCI group.
A recent report has described a slightly poorer performance for 18F-FDG, compared with PiB, in characterizing early dementia (14). To further investigate this paradigm, in this project we evaluated the comparative diagnostic performance of PiB and 18F-FDG scans in several early cognitive impairment subtypes. In the data analysis, we also attempted to determine the optimal analysis method for each modality. Many PiB data analyses published to date have reported their results in terms of cortical-to-reference ratios, also known as standardized uptake value ratios (SUVRs) (15). In the wider field of PET body imaging, the standardized uptake value (SUV) is a ratio of the regional activity to a subject-specific scale factor, determined by the injected dose and the patient body weight. In this project, we compared this traditional SUV approach with the results of the alternative SUVR method in 18F-FDG and PiB imaging. The use of dose- and weight-normalized SUV measurements could provide an alternative to cortical ratios in situations in which a standard reference tissue may be suggestive, such as in subjects who may accumulate amyloid in the cerebellum (as can occasionally occur in some familial AD subtypes) (Fig. 1) (16–18). Rarely, amyloid deposition in the cerebellum can also be seen in sporadic AD (19). Both partial-volume correction (PVC) and nonpartial-volume correction of the PiB and 18F-FDG data were also evaluated. 18F-FDG and PiB PET were then compared in terms of their ability to characterize different groups of subjects with and without cognitive impairment.
This study was approved by our Institutional Review Board. All subjects, including the healthy controls, were recruited through the Alzheimer’s Disease Research Center and the Alzheimer’s Disease Patient Registry, Mayo Clinic. Healthy elderly subjects with no cognitive impairment (n = 20), subjects with amnestic MCI (aMCI) (n = 17), subjects with nonamnestic MCI (naMCI) (n = 6), and subjects with mild probable AD (n = 13) were recruited. Subjects with mild probable AD were diagnosed according to DSM-III-R (20) criteria for dementia and National Institute of Neurological and Communicative Disorders and Stroke and the Alzheimer’s Disease and Related Disorders Association criteria for AD (21), and subjects with aMCI and naMCI were classified according to consensus criteria (22). Subjects with structural abnormalities and addictions, psychiatric diseases, or treatments that would affect cognitive function were not included.
Cognitive testing was completed within 4 mo of the PET scans. All of the subjects received identical clinical and neurocognitive evaluations, and all were staged according to the Clinical Dementia Rating (CDR) scale (23). The controls and MCI subjects in the current study were classified as CDR 0 and CDR 0.5, respectively, and the AD subjects were classified as either CDR 0.5 or CDR 1.0. Memory was evaluated by free recall percentage retention scores computed after a 30-min delay for the Wechsler Memory Scale-Revised Logical Memory, Visual Reproduction subtests and the Rey Auditory Verbal Learning Test. Language tests measured confrontation naming and category fluency. The attention or executive measures included the Trail Making Test, parts A and B, and the Wechsler Adult Intelligence Scale-Revised (WAIS-R) Digit Symbol subtest. Visuospatial processing was examined by the WAIS-R Picture Completion and Block Design subtests. All tests were administered by experienced psychometrists and supervised by board-certified clinical neuropsychologists. All raw scores were converted to Mayo Older American Normative Studies (MOANS) age-adjusted scaled scores that are normally distributed and that have a mean of 10 and a SD of 3 in cognitively healthy subjects on whom each test was based (24). In each cognitive domain, a mean MOANS age-corrected scaled score was computed for every participant.
A final consensus diagnosis of MCI subjects was made by a panel (nurse, psychometrist, neuropsychologist, and neurologist) that considered historical, clinical, and neuropsychologic data comprehensively. The subjects’ mean MOANS scores within a certain domain did not strictly define their MCI category, although cognitive tests were used to inform the clinical consensus diagnosis. Subjects were classified as aMCI if the impairment included only the memory domain on the consensus diagnosis or if the impairment was in the memory domain plus 1 or more other domains such as language, attention or executive function, and visuospatial processing (multidomain). A classification of naMCI was assigned when impairment included 1 or more nonmemory domains with relative preservation of memory.
PET images were acquired using 1 of 2 PET/CT scanners (DRX; GE Healthcare) operating in 3-dimensional mode (septa removed). The subjects were injected with PiB (average, 596 MBq; range, 292–729 MBq) and 18F-FDG (average, 540 MBq; range, 366–399 MBq) on the same day with 1 h between the PiB and the PET scan acquisitions. Subjects were prepared for 18F-FDG in a dimly lit room, with minimal auditory stimulation. A CT image was obtained for attenuation correction. After a 40-min (PiB) or 30-min (18F-FDG) uptake period, the subjects were imaged. A 20-min PiB or an 8-min 18F-FDG scan was obtained. The PiB PET acquisition consisted of four 5-min dynamic frames, acquired from 40 to 60 min after injection, and the 18F-FDG image acquisition consisted of four 2-min dynamic frames, acquired from 30 to 38 min after injection. Standard corrections were applied.
PiB was synthesized as described elsewhere (25). The general 11C-labeling method used was an adaptation of that described by Solbach et al. (26). The 11C-PiB product was analyzed by high-performance liquid chromatography to determine radiochemical purity, chemical purity, and specific activity. Endotoxin, pH, and sterility testing were performed. 18F-FDG from ongoing daily production, undergoing the same quality-control testing as was done for PiB, was used for this study.
No adverse events were detected. All subjects or their care-givers were asked in a follow-up phone call about adverse events attributable to the PET scans done as part of this study. Specifically, the following text was used: “Do you have any unexpected pain, tenderness, redness, or swelling in the arm where the injections were performed? Have you had any new fever, rash, breathing difficulties, diarrhea, headache, or muscle pain since your PET scans? If so, how many times, has it interfered with your normal daily activity, and have you needed to see anyone about it or take medications for it?” In all cases, subjects answered no.
The automated anatomic labeling atlas (27) was modified in-house to contain the following labeled regions: right and left parietal, posterior cingulate or precuneus, temporal, prefrontal, orbitofrontal, anterior cingulate, thalamus, striatum, primary sensory–motor, occipital, primary visual, cerebellum, and pons. The high-resolution, T1-weighted, single-subject brain image (27) that the atlas was drawn on was normalized to the Montreal Neurologic Institute (MNI) template using the unified segmentation method in SPM5 (28), giving a discrete cosine transformation, say F, which normalizes the atlas brain to the MNI template space. The static PiB and 18F-FDG image volumes of each subject were coregistered to the subject’s own T1-weighted MRI scan, using a 6 degree-of-freedom affine registration with mutual information cost function. Each MRI scan was then spatially normalized to the MNI template using the unified segmentation model of SPM5 (28), giving a discrete cosine transformation, say Gi, which normalizes the MRI of subject i to the MNI template. Then for each subject, the composite transformation Gi−1(F(.)) was applied to the atlas to warp the atlas to the subject’s anatomic space. Atlas-based parcellation of PiB and 18F-FDG images was, therefore, performed in subject space, to avoid interpolation effects caused by spatial normalization when quantifying PiB and 18F-FDG uptake by region of interest (ROI). For each subject, the sum of the native-space-segmented gray matter (GM) and white matter probability maps generated from the unified segmentation routine was thresholded at a value of 0 to create a binary brain mask. Each subject’s brain mask was then multiplied by the subject-specific warped atlas, to generate a custom brain atlas for each subject, parcellated into the aforementioned ROIs. This step was performed to minimize inclusion of cerebrospinal fluid (CSF) in statistics of all ROIs. Statistics on image voxel values were extracted from each labeled cortical ROI in the atlas.
In 1 variation of the automated ROI parcellation algorithm, PVC was performed on the PiB and 18F-FDG images, using a 2-compartment model. Each subject’s PiB and 18F-FDG images were coregistered with a 6 degree-of-freedom affine registration to that subject’s MRI scan, which was then simultaneously spatially normalized and segmented into GM, WM, and CSF compartments, using the unified segmentation method of SPM5. The GM and WM segmentations were saved in the subject’s native space and combined to form a brain tissue probability mask, which was then resampled to the resolution of the PiB image and smoothed with a 6 mm full width at half maximum gaussian filter, to approximate the point spread function of the PET camera. Finally each PiB and 18F-FDG PET voxel was divided by the corresponding value in this smoothed brain mask, in a manner similar to that recommended by Meltzer et al. (29) for 18F-FDG PET images.
PiB ROI ratios were calculated by dividing each target region cortical ROI median value by the median value in the cerebellar GM ROI of the atlas. A global cortical PiB uptake summary measure was formed by combining the prefrontal, orbitofrontal, parietal, temporal, anterior cingulate, and posterior cingulate or precuneus ratio values for each subject. This measure was determined by the clinical expectations of abnormal regions and selection of regions with the most prominent PiB groupwise separation, as we have done previously (6) (Fig. 2). 18F-FDG ratios were calculated by dividing each target region cortical ROI value by the median value in the pons ROI of the atlas. A global cortical 18F-FDG uptake summary measure was formed by combining the parietal, temporal, and posterior cingulate or precuneus ratio values for each subject. This measure was determined by selecting regions with the most prominent 18F-FDG groupwise separation (Fig. 3). These regions were similar to those identified by previous authors (14) as the most discriminating regions for the 2 PET scans.
We determined the SUVs normalized for body weight and decay-corrected dose of each target cortical ROI. Cortical ROI median SUVs were recorded and compared with cortical or reference region values described above for both 18F-FDG and PiB. The SUVs were calculated as:
All MRI studies were performed with a standardized imaging protocol. All subjects were imaged at 3 T with a 3-dimensional magnetization prepared rapid acquisition gradient-echo imaging sequence as used previously (6). Images were interpreted in a setting masked from clinical information to assess for anatomic abnormalities. All subjects’ MR images were normalized and segmented using the unified segmentation model in SPM5 with custom elderly tissue probability maps developed in-house (30). The normalization parameters obtained were saved for later use in PET data analysis and ROI determinations.
We used the Fisher exact test to assess differences in proportions on categoric variables across the 4 subject groups, investigating cortical ratios and SUVs, both with and without PVC, for both PiB and 18F-FDG. We used nonparametric methods to compare groups on imaging and cognitive impairment due to skewness in the distributions. Specifically, the Kruskal–Wallis test was used to evaluate differences across the 4 groups, whereas 2-sample comparisons were performed using Wilcoxon rank sum tests. A 1-sample Wilcoxon signed rank test gives rise to a distribution-free estimate of central tendency and a 95% confidence interval, which we used to compare within-group averages at the ROI level (31). The ability of a measure to discriminate between controls and AD was assessed using the area under the ROC curve. P values for this 2-sample comparison are reported from the more powerful, but equivalent, 2-sample Wilcoxon rank sum test. We used proportional odds logistic regression to assess the complementary effects of PiB and 18F-FDG on the odds of progressing along the cognitive spectrum represented by the control, aMCI, and AD groups. All tests were performed 2-sided.
The results suggest significant discrimination (P < 0.05) between controls and AD, naMCI and aMCI, naMCI and AD, and aMCI and AD using PiB PET. This discrimination was seen in both partial-volume–corrected and –noncorrected cortical ratio and SUV measurements. PVC led to a small positive bias. The pairwise comparisons of the global PiB cortical ratios and SUVs were not statistically different when evaluated with or without PVC. Notably, similar discriminatory performance was seen between cortical ratio measurements and SUV measurements (Fig. 4). Areas under the ROC curve for controls versus AD subjects (Table 1) reflected the same findings, suggesting a normalization to cerebellum or SUV measurements for PiB could obtain the same diagnostic accuracy.
The result suggests significant discrimination (P < 0.05) between controls and AD, naMCI and AD, and aMCI and AD using 18F-FDG PET. This was seen in both partial-volume–corrected and –noncorrected and cortical ratio measurements. The SUV measurements did not attain statistically significant separation between any of the groups, with or without PVC (Fig. 5). The pairwise comparisons of the global 18F-FDG cortical ratios and SUVs were not statistically different when evaluated with or without PVC. For global 18F-FDG, the ROC areas also showed that pons normalization was superior to SUV measurements in accuracy (Table 1). The ability to discriminate controls from AD was modestly improved for PiB (ROC area, 0.92), as compared with 18F-FDG (ROC area, 0.84), although this was not a statistically significant difference. The improved discrimination between groups by PiB can be seen visually. Figure 6 shows mean images of all subjects in each group for 18F-FDG and PiB scans. The visual separation of the groups is more distinct with PiB. The slightly elevated PiB uptake in the control group relative to the naMCI group is likely due to the small contribution from positive PiB cases in the healthy control.
We used proportional odds logistic regression to determine whether using both tests could improve our groupwise discrimination along the cognitive spectrum represented by the control, aMCI, and AD groups. Global PiB with PVC significantly discriminated among the groups (generalized area under the curve [AUC], 0.79; P < 0.001). Likewise, global 18F-FDG with PVC significantly discriminated among the groups (generalized AUC, 0.74; P < 0.001). When a model is fit that includes global PiB, global 18F-FDG, and the interaction, the interaction is significant (P < 0.03) and generalized AUC increases to 0.84. At a higher level of 18F-FDG (i.e., the 75th percentile), moving from the 25th percentile to the 75th percentile on PiB can be expected to quadruple a subject’s odds of progression to a more impaired diagnosis. However, with 18F-FDG at the 25th percentile, the effect of this increase in PiB is more than 5 times greater. In other words, high 18F-FDG may mitigate the negative effect of higher PiB. High PiB, given low 18F-FDG, is quite disadvantageous. The 18F-FDG effect similarly depends on the subject’s PiB level. At good PiB levels equivalent to the 25th percentile, there is no significant increase in odds of a more impaired diagnosis as 18F-FDG drops from the 75th to the 25th percentile. However, at high PiB levels equivalent to the 75th percentile, the odds of a more impaired diagnosis increased over 6-fold when 18F-FDG drops from the 75th to the 25th percentile.
Subjects with aMCI (n = 17) had significant amyloid uptake as compared with naMCI subjects (n = 6), and the groups showed significant pairwise separation (Fig. 4). This was seen for PiB, whereas the 18F-FDG measures were indistinguishable (Fig. 5). The naMCI subjects did not show PiB accumulation and were not statistically different from the control group with either PiB or 18F-FDG by any of the methods used (Fig. 6). Table 2 shows the subject demographics, with subjects subcategorized into those who were PiB-positive and those who were PiB-negative. A ratio greater than 1.5 was used to indicate PiB positivity and was defined using the methods we have reported previously (6). Interestingly, there is significant attention or executive and visuospatial scoring differences (abnormalities) in the naMCI group (who were all PiB-negative) versus the aMCI PiB-positive group. Although the memory scores for the naMCI group were lower than those of the controls, the consensus diagnosis that assigns the final diagnostic category listed all of these subjects as not showing memory impairment, and hence they were classified as naMCI subjects. The aMCI PiB-negative and aMCI PiB-positive subjects did not score significantly differently, as one might expect, although the attention or executive score differences approach significance.
We found that although PiB and 18F-FDG showed similar accuracy in separating cognitively impaired subjects into the defined clinical categories, there was a trend for improved accuracy with PiB. This improved accuracy was most significantly demonstrated by a pairwise separation of naMCI and aMCI subjects. There was also a slight improvement in ROC curve data from PiB, compared with 18F-FDG, in characterizing control and probable-AD groups. The improved pairwise separation with PiB can be seen graphically in Figures 4 and and55 and is also demonstrated by a greater difference in multiple cortical regions in which such separation would be expected in the subject groups (Figs. 2 and and3,3, respectively). The percentage of change between the control and AD groups is much greater for PiB than for 18F-FDG in different brain ROIs in which the separation is expected. For example, the change from control to AD is a 70% increase generally for PiB, whereas it is in the range of a 20% decrease for 18F-FDG. These factors likely contribute to the improved pairwise separation for PiB. These findings translate into better visual separation of the groups by PiB (Fig. 6).
Our study is supportive of previously published work by Ng et al. (14); in this paper, healthy (n = 15) and probable-AD subjects (n = 15) were included. Although the AD subjects had mild-to-moderate dementia, no early cognitively impaired subjects, such as the MCI subjects, were included. In addition, in the study by Ng et al. (14), visual interpretation was compared with cortical ratios, and they were found to be equivalent in accuracy. Cerebellar regions were used for both PiB and 18F-FDG normalization. There was no mention of using atrophy correction, nor did the analysis use any additional normalization strategy such as dose or weight normalization. Similar to our findings, PiB was found to be superior to 18F-FDG in accurately characterizing healthy and AD subjects.
Given these findings, the question could be posed about the role of 18F-FDG and PiB in dementia imaging. Are they complementary? Recently we showed that PiB and MRI hippocampal W scores were complementary in discriminating among subjects along the cognitive spectrum ranging from control to aMCI to AD (6). Using the same ordinal logistic regression approach but with this slightly larger group, we found that 18F-FDG and PiB are in fact complementary and that we significantly improve our group-wise discrimination when we account for a subject’s PiB and 18F-FDG values. As was found to be the case with PiB and MRI hippocampal W score, the significant interaction between PiB and 18F-FDG means that the effect of 1 PET measure on the odds of a more cognitively impaired diagnosis depends on the level of the other measure.
We evaluated various methods of analysis of PiB and 18F-FDG PET data in this project to assess and optimize the performance of each test. The performance impact of using PVC in evaluating PiB and 18F-FDG images in characterizing subjects with memory impairment was evaluated. We did not find any significant difference between the 2 methods. Small positive biases were seen with PVC, as could be expected. If any conclusion could be made it would be based on subtle trends and would favor using PVC in the data analysis of PiB and 18F-FDG PET. Other methods of PVC could be entertained. These data were based on mildly impaired subjects, and subjects with more severe atrophy could differ more significantly.
We found that PiB PET data analyzed using cortical ratios or SUVs were indistinguishable statistically in terms of pairwise group separation or controls versus AD characterization accuracy. This was not the case for 18F-FDG. This finding may provide data to support SUV image analysis as an alternative evaluation for subjects who have noticeable PiB accumulation in regions such as the cerebellum that are used for cortical region ratio calculation. Also, in respect to future clinical use of the test, as most PET systems can now provide such SUV data in regions selected on the view screens of interpretation workstations, quick regional quantification could be considered during clinical reading as an aid in interpretation.
MCI subjects are of great interest in the context of studying imaging biomarkers of early AD. However, data regarding the performance of PiB PET are limited in MCI subjects. The ability of 18F-FDG PET to accurately characterize MCI subjects is also of some debate. Some reports have shown that only 50% of MCI cases have reduced 18F-FDG uptake (1,32–34), whereas others have found more consistent abnormalities when particular at-risk areas, such as the mesial temporal lobes, are specifically evaluated (1,32–37). Forsberg et al. recently reported a high likelihood of conversion to probable AD in those MCI subjects with positive PiB scans (7 of 20) (38). It appears likely, nonetheless, that MCI subjects with elevated cortical PiB uptake or reduced 18F-FDG uptake are more likely to convert to AD.
A recent publication presented results on PiB and 18F-FDG imaging. In this report 18F-FDG was superior in the classification of controls versus MCI subjects, and PiB and 18F-FDG were similar in their ability to classify AD (39). Various differences between that study and ours may explain the seemingly differing results, including the use by that study of a fully quantitative 18F-FDG metabolic glucose rate calculation and a relatively small group of 7 healthy subjects.
In considering the evaluation of MCI subjects, probable AD may not develop clinically in a significant number of subjects who carry an MCI diagnosis, and only longitudinal study can accurately assess the diagnostic performance or pathophysiologic importance of either 18F-FDG or PiB PET in this cohort. Subcategorizing the MCI cohort as we have done may, therefore, be a better way in the short term for characterizing the risk of AD developing in this cohort and be of more help in understanding the imaging findings in the MCI group.
MCI subjects can be characterized as amnestic or non-amnestic, as described above, with each subtype likely having different risks of conversion to AD. No reports to date have evaluated PiB and 18F-FDG in naMCI and aMCI subjects. In this report, we evaluated MCI subjects with presumed higher risk of converting to probable AD (aMCI) relative to lower-risk naMCI subjects (40). We saw a clear separation of the groups using PiB imaging only with the naMCI subjects having no amyloid accumulation. Granted, the number of subjects was small, but this may suggest that the aMCI subjects exhibiting amyloid deposition, in whom the risk of converting to AD is highest, have early physiologic preservation of glucose metabolism. Therefore, hypometabolism may occur after the amyloid insult. If this is true, the combination of the 2 PET tests may provide a way to study such theories as brain reserve in the presence of amyloid in the pathogenesis of AD (41). Clearly, larger correlative studies would be needed to evaluate this possibility.
In addition, significant attention or executive and visuo-spatial scoring differences (abnormalities) in the naMCI group (who were all PiB-negative) versus the aMCI PiB-positive group were seen. This could suggest that the naMCI group seen here reflected subjects with evolving Lewy body disease because impairment in the domains of attention or executive and visuospatial functioning are characteristic of dementia with Lewy bodies (42). These data highlight the difficulty in clinical decision making and hence the importance of new accurate imaging methods such as PiB PET. These naMCI subjects had low memory scores, and the consensus diagnosis favored less emphasis on the memory score and more emphasis on attention or visuospatial compromise or other clinical findings and listed them as not being memory-impaired. This is likewise a confirmatory finding on the heterogeneous nature of the MCI group, as has been noted on imaging reports previously, and provides a better understanding of the variable PET results that have been seen (9) in MCI subjects when they have been studied as a homogeneous group.
In classifying subjects with memory impairment, PiB showed slightly better separation of subjects, compared with 18F-FDG PET. Significantly better group discrimination in naMCI and aMCI subjects by PiB over 18F-FDG may suggest early amyloid deposition before cerebral metabolic perturbation. The use of PVC for evaluating PiB and 18F-FDG PET data in subjects with memory impairment is not necessary to provide equivalent group separation. The use of cortical-to-reference ratios (SUVR) provides equivalent accuracy to normalization to dose and body weight SUV calculation for PiB. Cortical-to-reference ratios are superior for 18F-FDG data analysis.