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Cerebral metabolic rate of oxygen consumption (CMRO2), cerebral blood flow (CBF), and oxygen extraction fraction (OEF) are important indices of healthy aging of the brain. Although a frequent topic of study, changes of CBF and CMRO2 during normal aging are still controversial, as some authors find decreases of both CBF and CMRO2 but increased OEF, while others find no change, and yet other find divergent changes. In this reanalysis of previously published results from positron emission tomography of healthy volunteers, we determined CMRO2 and CBF in 66 healthy volunteers aged 21 to 81 years. The magnitudes of CMRO2 and CBF declined in large parts of the cerebral cortex, including association areas, but the primary motor and sensory areas were relatively spared. We found significant increases of OEF in frontal and parietal cortices, excluding primary motor and somatosensory regions, and in the temporal cortex. Because of the inverse relation between OEF and capillary oxygen tension, increased OEF can compromise oxygen delivery to neurons, with possible perturbation of energy turnover. The results establish a possible mechanism of progression from healthy to unhealthy brain aging, as the regions most affected by age are the areas that are most vulnerable to neurodegeneration.
Oxygen metabolism in brain (CMRO2), cerebral blood flow (CBF), and oxygen extraction fraction (OEF) in the brain are important indices of healthy aging. Here we review, by means of novel reanalysis, the results of several recent studies of these variables in healthy volunteers, performed by the authors and reported in the literature. This reanalysis follows the practice of (Kety, 1956) who reviewed the first 10 years of results obtained with the nitrous oxide technique of Kety and Schmidt (1945, 1948). The author reported significant declines of whole-brain values of CBF and CMRO2, as well as an increase of OEF with increasing age. Positron emission tomography (PET) later made it possible to study subdivisions of the brain, and several studies revealed regional decreases of both CBF (Borghammer et al, 2008; Leenders et al, 1990; Lenzi et al, 1981; Marchal et al, 1992; Martin et al, 1991; Pantano et al, 1984) and CMRO2 (Ibaraki et al, 2010; Leenders et al, 1990; Lenzi et al, 1981; Marchal et al, 1992; Takada et al, 1992; Yamaguchi et al, 1986). However, a few authors reported no changes or equivocal results for CBF (Ibaraki et al, 2010; Meltzer et al, 2000; Takada et al, 1992; Yamaguchi et al, 1986) and CMRO2 (Burns and Tyrrell, 1992; Pantano et al, 1984). Of the cited studies, four included calculations of OEF, but only Leenders et al (1990) reported significant increase with age, while the remainder of the studies (Ibaraki et al, 2010; Marchal et al, 1992; Pantano et al, 1984) failed to replicate Kety's early observation.
To some observers, the apparent lack of change of OEF in conditions of steady state of the healthily aging brain indicates a close match of CBF to the metabolic demands of neurons, while to other observers, the optimal oxygen homeostasis requires a nonlinear relation between CMRO2 and CBF (Gjedde et al, 2005). Relative changes of CMRO2 and CBF, reflected in the OEF, determine the pressure gradients of oxygen delivery. During activations of the brain, decreases of the OEF generally benefit the oxygen homeostasis in brain tissue because they elevate the average partial pressure of oxygen in capillaries (Buxton and Frank, 1997). Conversely, the same mechanism, operating under conditions of possible deactivation of brain tissue as a consequence of aging, hence may lead to a rise of OEF, although evidence is lacking for this contingency. Thus, if CMRO2 remains constant during healthy aging, a reduction of CBF that exceeds the normal decline in response to reduced metabolic demand necessarily leads to an abnormally large increase in OEF. Also, an increase of OEF at rest with no change of CMRO2 would signify a perturbed regulation of blood flow, at variance with the underlying hypothesis that CBF is adjusted to maintain oxygen tensions consistent with the oxygen demands of the neurons. Therefore, we predict that elevated OEF can impose a limitation on the delivery of oxygen, when average oxygen tensions decline in capillaries as well as in the tissue (Gjedde et al, 2005, 2010).
Early PET studies obtained the values of parametric variables from tomographic records with 16mm isotropic resolution. Spatial resolution of this magnitude limits accurate estimation of CBF and CMRO2 because of signal dispersion to white matter and cerebrospinal fluid, as the cerebral cortex is only 2.5 to 3mm thick (Pakkenberg and Gundersen, 1997; Rabinowicz et al, 2002). This signal dispersion generates the well-known partial volume effect (PVE) of signal dilution. The widening of sulcal spaces during normal aging further compounds the PVE-based bias. However, the improved spatial resolution of modern tomographs allows more accurate estimates of CBF and CMRO2 than previously possible and thus attenuates the bias introduced by aging. Importantly, OEF will not be affected by PVE, since it is calculated as a ratio between CMRO2 and CBF, rather than being measured directly.
Another improvement is statistical parametric mapping, which yields voxel-wise rather than region-wide parametric estimates. This method has the potential of objectively identifying areas of significant change, independently of the volumes-of-interest (VOIs) chosen by the investigators.
Inspired by these limitations and the contradictory or uncertain results of previous studies, we chose to reexamine the adequacy of flow–metabolism coupling for oxygen delivery during healthy aging within a sufficiently large population of healthy volunteers studied with higher-resolution PET instrumentation and up-to-date data analysis. By application of these improved methods, compared with older studies, we expected to find changes of CBF, CMRO2, and OEF with higher significance than previously obtained.
Sixty-six healthy subjects (46 males) aged 21 to 81 years volunteered for the studies included in this reanalysis. Originally excluded were subjects with neurologic or psychiatric disorders by clinical interview and examination. The volunteers took no medication or substances with known effects on brain–blood flow or metabolism. Complete details on the subjects, who had participated in earlier studies, were published previously (Ashkanian et al, 2009; Borghammer et al, 2008; Gjedde et al, 2005; Iversen et al, 2009; Møller et al, 2006). Written informed consent was obtained from all subjects and the protocols were approved by the regional Science Ethics Committee, in accordance with the declaration of Helsinki.
Thirty-eight of the subjects had T1-weighted scans obtained on a 3.0T Signa Excite GE Magnet using a 3DIR-fSPGR sequence (256 × 256, echo time (TE)1=min full, time of inversion (TI)=450, slice thickness=1.5mm) and 28 subjects were scanned with GE MR 1.5-T Echo Speed tomograph (3D-SPGR, 256 × 256, 1 Splap, number of excitations (NEX): 1, slice thickness 1.5).
Sixty-five subjects had one dynamic [15O]H2O emission recording, and 65 had one or two [15O]O2 emission recordings. All recordings were performed with the subjects resting in a supine position in a quiet room with eyes open, except in one study where subjects had their eyes closed. Recordings were acquired in 3D mode with the ECAT EXACT HR47 (CTI/Siemens, Knoxville, TN, USA) whole-body tomograph. The image volumes had an isotropic resolution of 4.6mm. Images were reconstructed as 128 × 128 matrices of 2 × 2mm2 voxels using filtered back projections with a 0.5 per cycle Hann filter. The reconstructed images were corrected for random and scatter events, detector efficiency variations, and dead time. Tissue attenuation scans were performed using a rotating 68Ge source. Dynamic emission recordings lasting 3 minutes (21 frames) were initiated on bolus intravenous injection of [15O]H2O (500MBq) or inhalation of [15O]O2 (500 or 1,000MBq). Catheters (Artflon and Venflon, Becton Dickinson, Swindon, UK) were inserted in the left radial artery and right cubital vein. In all, 50 subjects had arterial blood radioactivity measured by an automated blood sampling system (Allogg AB, Mariefred, Sweden), crosscalibrated with the tomograph, and then corrected for external delay and dispersion. Remaining subjects had arterial blood samples manually drawn to measure radioactivity (21 samples: 12 × 5, 6 × 10, and 3 × 20seconds).
The dynamic PET recordings were smoothed to a full-width half-maximum (FWHM) of 6mm. As labeled water is assumed to undergo rapid distribution in the entire brain tissue volume, the model used to analyze the images had only one tissue compartment. Parametric images of the unidirectional blood–brain clearance of either tracer were calculated with the single-step modified linearizations of the one tissue compartment model of (Blomqvist, 1984) described by Ohta et al (1992, 1996) with Lawson and Hanson (1974) nonnegative least squares solutions of general least squares functions. For CBF, the model yields estimates of K1 and k2 constants for the diffusion of [15O]H2O between the blood and brain tissue compartments. With correct inclusion of a blood compartment Raichle et al (1983) show that for blood flow <55mL/100g per minute (close to the current average), the estimated water clearance from the blood can be regarded as 100% of the true clearance, such that K1 consequently equals CBF. For CMRO2, the model estimates the magnitudes of the clearance K1 and the rate constant k2 for the diffusion of [15O]O2 between the two compartments. It is assumed that oxygen ‘instantly' is metabolized to water, which is freely diffusible between the two compartments. However, the implementation of Ohta et al (1996) does not make use of the k2 estimate.
We did spatial coregistration in two separate ways. The first method derived VOIs; individual MR images were warped to fit (Collins et al, 1995; Collins and Evans, 1997) a template based on 85 brains from young healthy people in ICBM152 space (http://imaging.mrc-cbu.cam.ac.uk/imaging/
MniTalairach). A linear transformation was estimated and then used as input to a nonlinear transformation estimation process to accurately match anatomy between the subject and the template with a hierarchical transformation estimation strategy. Summed PET images were coregistered to individual MR images, and the concatenated transformation files were applied to the dynamic PET images. The second method of coregistration was chosen with the specific purpose of voxel-based statistics; Individual CBF PET images were registered directly to a CBF-PET atlas (SPM2, London, UK). Cerebral metabolic rate of oxygen consumption PET images were coregistered to each individual's CBF images. As above, all images were matched to the CBF-PET atlas with a linear transformation used as input to a hierarchical nonlinear transformation estimation strategy. Rigid body transformations matching the CMRO2 to CBF images were concatenated with each of the CBF-to-atlas transformations.
The automated coregistration algorithm extracted a binary mask of cortical gray matter (GM) from each individual's MR image. These binary masks were then multiplied with generic masks for each VOI, yielding individualized masks for all VOIs. The GM masks were manipulated (isotropic smoothing FWHM 4mm, threshold 0.4) to be of approximately the same thickness as the PET signal from cortical GM (Figure 1). These were used to extract mean GM values from parametric PET images. Where subjects had two CMRO2 images (average time between image acquisition 14 (s.d. 4.3) minutes), we used an average of the two (23 subjects). The cortical GM was divided into five VOI's: frontal lobe excluding the M1 area (F-M1), parietal lobe excluding the S1 area (P-S1), temporal lobe (T), primary motor and sensory cortex (M1S1), and occipital lobe (O)). Regression coefficients with age as an independent variable and y-intercepts at age 50 were calculated for CBF, CMRO2, and OEF. First, a mixed model multilinear regression was performed on logarithmically transformed data to account for differences in mean CBF values among groups of subjects included from earlier studies. Individual PET images were then corrected for group differences, and a linear regression analysis with age as an independent variable, was performed in all VOIs. PaCO2 has been found to positively correlate with CBF (Ito et al, 2000). Therefore, PaCO2 was added as an independent variable in the regression analysis for CBF. Calculations were performed in STATA IC 10 for Mac (College Station, TX, USA).
Coregistered parametric images were normalized with the reference cluster method (Borghammer et al, 2009a; Yakushev et al, 2009). To use this method, we assumed that no brain region displays true increases as a result of aging in neither CBF nor CMRO2. This assumption is justified since no previous quantitative PET study of aging reported absolute increases in perfusion or metabolism anywhere in the brain. Normalized images were blurred to a FWHM of 12 × 12 × 12mm3 and analyzed in fMRIstat (http://www.math.mcgill.ca/keith/fmristat) on MATLAB v 7.7.0 (R2008b) (The MathWorks, Natick, MA, USA). The method has been described elsewhere (Borghammer et al, 2009b). A linear regression model with age as an independent variable was fitted in each voxel for either CBF or CMRO2. The program fMRIstat assigns a t-value in each voxel to reveal the significance of age with the dependent variables using the mixed effect model analysis described by Worsley et al (2002). After the model estimation, t-contrasts were specified to test statistical significance, and the resulting statistical maps were thresholded at P<0.05, corrected for multiple comparisons using Gaussian Random Field Theory in the entire search area (Worsley et al, 1996).
Parametric CBF (adjusted for study and PaCO2) and CMRO2 (adjusted for study) images were divided into three age groups aged 21 to 39 years (‘young,' n=25); 40 to 59 years (‘middle age,' n=19); and 60 to 81 years (‘old,' n=21) and mean images calculated in fMRIstat. Further analysis was performed on data divided into these age groups by extracting mean values in different VOIs from these images, separately for each hemisphere.
Oxygen extraction fraction was calculated by the following formula:
where CaO2 is the arterial content of oxygen (CaO2=hemoglobin concentration • oxygen saturation) (Mintun et al, 1984).
The average maps of the three age groups of CMRO2 and CBF in the three age groups are shown in Figure 2. They show clear patterns of cortical decrease of CBF that are apparent both from young-to-middle age and from middle-to-advanced age. Subcortical structures appeared to maintain relatively constant values of CBF with aging. The images of CMRO2 show some decline in cortex with aging, but the effect is relatively modest compared with the changes of CBF.
As listed in Table 1, values of CBF declined significantly in prefrontal and premotor regions of the frontal lobe in front of the motor cortex (F-M1) and in associative regions of the parietal lobe (P-S1), as well as in temporal (T) and primary motor and sensory (M1S1) cortices. Values of CMRO2, declined significantly only in F-M1, but tended toward significant declines in both P-S1 and temporal cortex. The magnitude of OEF increased significantly in F-M1, P-S1, and temporal cortex, and tended toward increase in M1S1. In Figure 3, we show scatter plots of the values of CBF, CMRO2, and OEF for the regions F-M1, P-S1, temporal cortex, M1S1, and occipital lobe; the frontal lobe in front of motor cortex (F-M1) was the most severely affected region, while values in occipital lobe were unchanged. We note that the variation is considerable, also after correction for the effect of PaCO2 on CBF. Analysis was also performed on data divided into three age groups (see above) for each VOI in each hemisphere and for each hemisphere globally. Results are shown in Table 2. The relationships between CBF, CMRO2, and OEF in the three age groups generally show the same trend as the regression analysis.
The voxel-wise regression revealed changes that generally matched the regional results, with the statistically most significant decreases of CBF in anterior cingulate and the medial part of the superior frontal gyrus, and additional decreases in regions of lateral thalamus, pons, medulla oblongata, cerebellum, occipital lobes, and the superior parts of M1S1 (maximum t-value 11.02, x=6, y=48, z=27, cluster size 1297548 voxels). The decreases of CMRO2 reached the highest levels of significance in the anterior part of the cortex, with less significant declines in subcortical regions of thalamus, caudate, and putamen, while values in white matter, cerebellum, brain stem, and occipital cortex, generally remained unchanged (maximum t-value 10.24, x=10, y=46, z=24, cluster size 1363296 voxels).
We present these results of the reanalysis in Figure 4 as Student's t-maps, where only significant changes in CBF and CMRO2 are shown. In each voxel, regression coefficients of declining CBF or CMRO2 values as a result of age were tested against the null hypothesis that the regression coefficient is zero. We give the results of these tests as Student's t-values, indicating the degree of significance.
In the review and reanalysis of studies of brain energy metabolism reported by this group for healthy volunteers studied at the Aarhus PET Center, we addressed the question of whether or not the variables of CBF, CMRO2, and OEF change as functions of normal aging. To answer the question, we reanalyzed PET data from a large population of volunteers of different ages participating in different studies. To our knowledge, it thus became the first voxel-based analysis of changes of CMRO2 during aging. We now report that values of CBF declined to a greater extent than values of CMRO2, with consequent increase of the magnitudes of OEF in specific parts of the human brain. According to Nemoto et al (2003), values of OEF that exceed 0.60 are so high that they represent potentially pathological declines of oxygen delivery. The increases of the values of OEF in associative areas of the brain in the present data therefore imply that oxygen delivery may indeed approach that threshold with increasing age. The reason for the effect is the inverse relation between extraction and delivery of oxygen that was first described by Suwa (1992a,1992b) who explained how the increased oxygen extraction lowers the average tension of oxygen in capillaries and hence adversely affects the pressure gradient.
This explanation is now the canonical explanation of the beneficial effects of nonlinear coupling of blood flow and oxygen consumption changes during activations and deactivations of brain tissue (Gjedde, 1997; Buxton and Frank, 1997; Vafaee and Gjedde, 2000, 2004; Gjedde et al, 2002). Thus, when brain energy metabolism declines, the steady-state estimates of CBF are expected to decline more than the steady-state estimates of CMRO2 to be consistent with the nonlinear coupling relation expected of a homeostatic mechanism that maintains more or less constant oxygen tensions in brain tissue and at the mitochondria. It is only when the values of CBF decline more than prescribed by the nonlinear coupling mechanism, or when the values of CMRO2 decline less than prescribed, stay constant, or actually rise, that the extraction may rise to levels that are detrimental to adequate oxygen delivery. Lu et al (2011) reported declines of CBF estimates and increases of CMRO2 estimates in normal healthy aging, which would be consistent with abnormal increases of OEF (from 0.34 to 0.40 in that study). However, the estimates of CMRO2 may reflect the use of a constant literature value of arterial oxygen concentration of 8.337mmol/L, which is not consistent with the possible changes of hemoglobin concentration with aging. In the present study, linear regression of hemoglobin concentration on age yielded a nonsignificant decline of hemoglobin concentration of 0.0079mmol/L per year (P=0.149).
The methods as well as the spatial resolution of the tomograph used in the studies included in the present reanalysis were superior to those characteristic of previous reports. In earlier studies of changes of CBF and CMRO2 during healthy aging, the authors generally had tomographs with resolutions in the 11 to 17mm range (Itoh et al, 1990; Meltzer et al, 2000; Pantano et al, 1984), and they located regions of interest with diameters varying from 14 to 20mm (Eustache et al, 1995; Leenders et al, 1990; Marchal et al, 1992; Yamaguchi et al, 1986). Because of some atrophy of the brains of aged subjects, the PVE arguably has a greater effect on the magnitude of parameter estimates from aged subjects than from younger subjects. The increased PVE of older subjects stems from sulcal widening. In young subjects with narrow sulci, PET resolution is less critical as a large sampling region would sample cortex on both sides of a sulcus. In aged subjects with advanced atrophy, however, a sampling region of the same size would on average cover more cerebrospinal fluid, thus leading to attenuation of the signal. Figure 5 shows representative examples of MR images from a young and an aged subject. Meltzer et al (2000) found that the significant decline of CBF with aging disappeared when they corrected the data for the PVE. However, in this study, the in-plane FWHM was no less than 10.3mm. To minimize loss of resolution in the present study, we analyzed the data with a FWHM of 6mm in both the VOI and age group analyses, which is a resolution that is closer to the average thickness of the cerebral cortex of 2.5 to 3mm (Pakkenberg and Gundersen, 1997; Rabinowicz et al, 2002). Part of the decline of the CBF and CMRO2 values observed with the present reanalysis still could be attributable to PVE, but the observation that CBF values declined while CMRO2 values remained unchanged in a region such as M1S1, and that the OEF changed with age in some regions only, implies that not all declines of the signal was due to atrophy.
Masks defined on an atlas brain depend for their accuracy on the quality of coregistration of the atlas brain and on the individual PET images. A potential bias of this method is age-associated atrophy as old brains are smaller than young brains (Pakkenberg and Gundersen, 1997). This fact could influence the adequacy of the fit between atlas and individual brain images. A common approach in early PET studies of aging was the outlining of VOIs directly on the PET images. This method introduces a bias when the investigator samples areas with a strong or a weak signal, depending on the aim of the study. To avoid these pitfalls in this reanalysis, we chose as a third option an automated algorithm for extraction of VOIs that ensured uniform sampling with individualized masks (exemplified in Figure 1), based on magnetic resonance imaging-derived anatomical knowledge of individual subjects' brains.
The magnitude of the reduction of CBF estimates in frontal and parietal cortices without the primary motor and somatosensory areas, and the temporal cortex, is largely consistent with the results of earlier studies (Leenders et al, 1990; Lenzi et al, 1981; Marchal et al, 1992; Martin et al, 1991; Pantano et al, 1984). Leenders et al (1990) found decreases only in frontal cortex and insula and unchanged CBF in temporal and parietal cortices, possibly due to low resolution. In agreement with all previous studies, occipital cortex had unchanged CBF also in the present reanalysis. Primary motor and somatosensory areas displayed some decrease with age, although the slope was less steep than in associative cortices.
We found that CMRO2 estimates decline in primary motor cortex (F-M1) and tend to decline in primary sensory (P-S1) and temporal cortices, while occipital and primary motor (M1S1) cortices remain unchanged during aging. This finding generally is consistent with recent as well as earlier findings (Ibaraki et al, 2010; Leenders et al, 1990; Marchal et al, 1992).
The significant increases of OEF found in the F-M1 and P-S1 cortices and in temporal cortex is the most important difference from the results of earlier studies. In three studies, the authors reported no effect of aging on OEF (Ibaraki et al, 2010; Marchal et al, 1992; Pantano et al, 1984), while in one study, the authors reported increases in frontal cortex and insula (Leenders et al, 1990). We argue that the large study population and age span, and sampling of parametric data with MR-derived individual masks give credibility to the present results. Detecting a change of OEF is made difficult by the presence of biological noise in both the CMRO2 and CBF estimates and the risk of compounding the noise in the calculation of OEF. Small study populations, narrow age ranges, and attenuation of the PET signal by PVE all lower the power of the regression analysis and could have impaired the detection of age-related changes in earlier studies.
In the present reanalysis, we found an apparent coincidence between areas with unchanged CBF and CMRO2 during healthy aging and areas that are heavily myelinated and highly functionally specialized as well as known to be least affected in neurodegenerative diseases such as Alzheimer's and Parkinson's diseases (Braak et al, 2006). In contrast, we found estimates of diminished CBF and increased OEF in associative areas, reported by Braak et al (2006), to be the parts of the brain most vulnerable to unhealthy aging. We interpret this result as an indication that lowering of CBF values with concomitant increases of OEF can be one attributing factor, among others, to unhealthy aging of the brain, perhaps related to changes of neurovascular coupling. In the case of Alzheimer's disease, these changes can be related to amyloid deposits (Smith and Greenberg, 2009).
At the threshold of 60% extraction, oxygen delivery to the tissue becomes compromised with resulting impairment of oxidative phosphorylation and adequate ATP regeneration. We found that values of CMRO2 also tend to be decreased in associative regions, but to less extent than was the values of CBF (hence the increased OEF revealed by the VOI analysis). The increased OEF potentially leaves the neurons susceptible to inadequate energy homeostasis, as argued by Nicholls (2008). Neurons in associative areas of the brain have less myelin than neurons in primary areas and consequently require higher rates of energy turnover for signaling (Hildebrand et al, 1993). This increased energy requirement, superimposed on reduced capacity for ATP production, may leave the cells susceptible to apoptosis.
In the voxel-based analyses, smoothing of data to 12mm FWHM was necessary to minimize noise. The lower resolution can explain the decreased values of CBF and CMRO2 in central areas close to ventricles and the longitudinal fissure due to the PVE, without affecting the lateral aspects of the hemispheres. Meltzer et al (2000) found that PVE correction eliminated the different values of CBF in the groups of young and old subjects. The present data were not corrected for PVE, but the resolution (FWHM 6mm) of the parametric images nevertheless exceeded that of previous studies. However, the residual PVE could influence the results and account for part of the observed decline of estimated values. The main finding in this study is that OEF shows increases in associative cortices. Theoretically, CMRO2 could be unchanged (or even increased) during aging, while CBF could be diminished to a lesser degree by aging than observed in the data, but still this would not change the relationship between the two variables, that is, OEF. The CBF and CMRO2 measurements were performed on the same subjects, with the same methodology, with measurements made only a few minutes apart, so we have no reason to suspect that PVE would affect one of the variables more than the other. The different rates of decline of CBF and CMRO2 (reflected in the increased OEF), thus, argue that although some of the observed decline could be due to PVE, at least some of the decrease in CBF must be due to a real decline in blood flow.
As subjects were not screened for vascular encephalopathy, it is possible that some of the older subjects had undetected cerebrovascular changes that may contribute to some decline of CBF.
The crosssectional design makes it impossible to distinguish between effects of aging per se and the effects of being born at different times (Miller and Corsellis, 1977). We observed large variability of both CBF (COV (coefficient of variation) 0.15) and CMRO2 (COV 0.12), comparable to the variation observed in other studies (Ibaraki et al, 2010; Leenders et al, 1990; Meltzer et al, 2000). This variation makes it difficult to ascertain whether the aging effect is due to some individuals having large changes with age and others having unchanged values, or whether the changes apply to everyone to some degree. Also, it is not possible at this time to determine whether the great variability reflects variable mitochondrial efficiency (uncoupling) in different individuals, or whether the degree of uncoupling is similar in all individuals. The average degree of uncoupling in the human brain appears to be close to 75% but is not related to values of body mass index, as it is in the body as a whole (Gjedde et al, 2011).
We found estimates of CBF and to less extent estimates of CMRO2 to decrease with age in extended regions of the brain, with relative sparing of primary sensory-motor and occipital cortices. This result of the reanalysis is consistent with evidence from previous studies, although we found more widespread declines of the estimates of both CBF and CMRO2. The widespread increases of OEF in F-M1, P-S1, and temporal cortices are novel findings. The large study population and the automated, individualized VOI sampling contribute to the significance of this result. The spatially distributed declines of values of CBF and CMRO2 revealed by the voxel-based analysis and the consequent spatial distribution of increased values of OEF coincide with areas known to be vulnerable in AD and PD.
Although functional magnetic resonance imaging and other modalities for brain imaging have been used increasingly over the past decade, PET remains the gold standard of regionally measured absolute blood flow and metabolism measurements. To distinguish further between the effects of aging and being born at different times, and to evaluate interindividual variability, future studies would focus on estimates of actual ATP turnover and a prospective longitudinal design of the studies.
The authors declare no conflict of interest.
This study was supported by the center-of-excellence Grants from Aarhus University and the Danish National Research Foundation (Danmarks Grundforskningsfond), as well as by the granting agencies acknowledged in the publications reviewed here.