Puneet Bagga1, Laurie J Rich1, Neil E Wilson1, Mark Elliott1, Mitch D Schnall1, John A Detre2, Mohammad Haris3,4, and Ravinder Reddy1
1Department of Radiology, University of Pennsylvania, Philadelphia, PA, United States, 2Department of Neurology, University of Pennsylvania, Philadelphia, PA, United States, 3Sidra Medicine, Doha, Qatar, 4LARC, Qatar University, Doha, Qatar
Synopsis
1H MR spectroscopy
is currently the only technique that allows the non-invasive detection and quantification
of a wide range of neurochemicals. In this study, we performed 1H
MRS in conjunction with the administration of [2,2,2′-2H3]acetate
to measure turnover kinetics of glutamate, glutamine and GABA in rat brain. As 2H
is invisible on 1H MRS, the turnover of metabolites will lead to a
corresponding drop in their 1H MR signal visualized by subtraction
of the post-[2,2,2′-2H3]acetate administration from the
Pre-administration 1H MR spectra. The fractional enrichment data can
be fitted to evaluate the rates of cerebral glutamatergic and GABAergic
neurotransmitter cycling.
Introduction
Over the last 3 decades, 13C magnetic resonance spectroscopy (MRS) in
conjunction with administration of 13C-labeled substrates has provided great insights
into cerebral energetics and neurotransmitter cycling1,2. Recently, 2H
MRS also referred to as deuterium MRS (DMRS), has been remarkably used to assess tissue metabolic kinetics following administration of
deuterated subtrates3,4. Here we present a novel strategy, which combines the administration of [2,2,2′-2H3]acetate
and 1H MRS to assess cerebral neurotransmission. Acetate is
selectively taken up by glial cells in the brain, followed by the formation of
acetyl-CoA which enters the TCA cycle to form α-ketoglutarate and
glutamate (Figure 1)5,6. The glutamate is rapidly converted into
glutamine by glutamine synthetase (GS). Glutamine is transferred to neurons to
replenish the neuronal glutamate pool by conversion of neuronal glutamine into
glutamate by the action of phosphate-activated glutaminase (PAG). The
administration of [2,2,2′-2H3]acetate
into the bloodstream leads to the transfer of 1H MR invisible 2H
into downstream metabolites of the TCA cycle and neurotransmission. The detection
of exchanged label turnover quantitative measurement
(ELOQUENT) by 1H MRS (eMRS) has given rise to a novel approach for measuring
cellular energetics in vivo. The ability to quantify the metabolites and high
spectral resolution offered by 1H MRS enables the monitoring of kinetics
of label transfer into crucial metabolites, i.e. glutamate (Glu), glutamine
(Gln), g-aminobutyric acid (GABA), and lactate (Lac). In the current report, 1H
MRS studies performed in the brains of normal rats following the administration
of [2,2,2′-2H3]acetate
highlight eMRS as a promising approach to determine cerebral neurotransmission in vivo.Methods
MR experiments on six 3-4-month-old male CDF
rats (220-250
g) were performed on a 9.4T
Bruker scanner using a 35-mm diameter volume coil. Body temperature and respiration rates and
monitored and maintained at 37
°C and 40-60 BPM, respectively. 1H MRS spectra were acquired from a voxel localized in the
mid-brain using PRESS (TR/ TE = 2500/16 ms, spectral width = 4 kHz, 90° pulse bandwidth = 5400 Hz, 180° pulse bandwidth = 2400 Hz, number of points
= 4006, VAPOR water suppression, averages = 128, scan time = 5.5 min). In
addition to the water suppressed spectrum, another spectrum with 4 averages was
acquired without water suppression to obtain the water reference signal for
normalization. Following the
pre-injection 1H MRS scan, the rats were intravenously injected with
[2,2,2′-2H3]acetate for 10 min
via infusion pump using an infusion protocol as described previously. During
and post-[2,2,2′-2H3]acetate
administration, a series of 1H MR spectra were gathered until 60
minutes.
Metabolites
were quantified using LCModel software7. Once metabolite
concentration at each time point was estimated, calculation of metabolite fractional
enrichment (FE) was performed by subtracting post-infusion levels from
pre-infusion levels. All FE enrichment plots report mean values with the standard
error of the mean. Fitted curves for FE plots were generated to provide a
visual aid of labeling using the following exponential plateau equation, Y=YM-(YM-Y0)exp(-kx),
where Y0 is the starting population, YM is the maximum
population, and k is the rate constant. Results and Discussion
Subtraction of the 90-minute post-infusion 1H
MRS spectrum from the pre-infusion spectrum revealed a marked increase in the Glu-H4
resonance (Figure 2). In addition to Glu-H4, other resonances including Glx3, Glu-H4,
Gln-H4, GABA-H2, and Lac-H3 were observed, all of which were well above
background levels. To estimate
the FE for metabolites, post-infusion concentration measurements taken by
LCModel at every time point were subtracted from pre-infusion measurements and
divided by pre-infusion values. eMRS enabled individual quantification of 2H labeling of Glu (Figure
3A) and Gln (Figure 3B), with 0.50 ± 0.12 mM increase in 2H
labeled Glu-4 (glutamate labeled with 2H at carbon 4), and 0.21 ±
0.12 mM increase in Gln-4 (glutamine labeled with 2H at carbon 4) observed
40min post [2,2,2′-2H3]acetate
infusion. These labeling patterns are similar in
regards to fractional enrichment of metabolites with published 13C
MRS literature8,9. The estimation of the metabolic fluxes by
fitting the FE data obtained via eMRS experiments is currently ongoing, we
anticipate these results would compare well with the values already reported in
the literature10,11. The findings reporting rates of glutamatergic,
GABAergic and glial TCA cycles in addition to glutamatergic and GABAergic
neurotransmitter cycling rates in a healthy rat brain will be presented at the
meeting. This approach is expected to enable a wide range
of studies probing metabolic derangements in
vivo across medical disciplines.Acknowledgements
This project was supported by the National Institute of Biomedical Imaging and Bioengineering of the National Institute of Health under award number P41EB015893.
References
1. Shulman,
R. G., & Rothman, D. L. 13C NMR of intermediary metabolism: implications
for systemic physiology. Ann. Rev. Phys. 63, 15-48 (2001)
2. Henry,
P. G., et al. In vivo 13C NMR spectroscopy and metabolic modeling in the brain:
a practical perspective. Magn. Reson. Imaging, 24, 527-539 (2006)
3. Lu,
M., Zhu, X. H., Zhang, Y., Mateescu, G. & Chen, W. Quantitative assessment
of brain glucose metabolic rates using in vivo deuterium magnetic
resonance spectroscopy. J. Cereb. Blood Flow Metab. 37, 3518-3530 (2017)
4. De
Feyter, H. M. et al. Deuterium metabolic imaging (DMI) for MRI-based 3D mapping
of metabolism in vivo. Sci. Adv. 4, eaat7314 (2018)
5. Waniewski RA
and Martin DL Preferential utilization of acetate by astrocytes is
attributable to transport. J Neurosci 18:5225–5233 (1998)
6. Badar-Goffer RS, Bachelard HS, Morris PG Cerebral
metabolism of acetate and glucose studied by 13C-n.m.r. spectroscopy. A
technique for investigating metabolic compartmentation in the brain. Biochem
J 266:133–139 (1990)
7. Provencher,
S. W. Automatic quantitation of localized in vivo 1H spectra with LCModel. NMR
Biomed. 14, 260-264 (2001)
8. de
Graaf, R. A., Mason, G. F., Patel, A. B., Behar, K. L. & Rothman, D. L. In
vivo 1H-[13C]-NMR spectroscopy of cerebral metabolism. NMR
Biomed. 16, 339-357 (2003)
9. van
Eijsden, P., Behar, K. L., Mason, G. F., Braun, K. P., & De Graaf, R. A. In
vivo neurochemical profiling of rat brain by 1H‐[13C] NMR spectroscopy:
cerebral energetics and glutamatergic/GABAergic neurotransmission. J.
Neurochem. 112, 24-33 (2010)
10. Tiwari,
V., Ambadipudi, S., & Patel, A. B. Glutamatergic and GABAergic TCA cycle
and neurotransmitter cycling fluxes in different regions of mouse brain. J.
Cereb. Blood Flow Metab. 33, 1523-1531 (2013)
11. Duarte,
J. M., & Gruetter, R. Glutamatergic and GABAergic energy metabolism
measured in the rat brain by 13C NMR spectroscopy at 14.1 T. J.
Neurochem. 126, 579-590 (2013)