Quantitative basal CBF and CBF fMRI of rhesus monkeys using three-coil continuous arterial spin labeling
Introduction
Non-invasive cerebral blood flow (CBF) measurement using MRI is widely used to study normal physiology and pathophysiology. Quantitative CBF can be obtained at high temporal and spatial resolution. Functional MRI based on CBF change is spatially more specific to the site of increased neural activity, capable of resolving cortical columns (Duong et al., 2001), is easier to interpret than the blood-oxygenation-level-dependent (BOLD) fMRI signals, has less susceptibility to pathologic perturbations, and less inter-subject and cross-day variability (Barbier et al., 2001). Combined cerebral blood flow and BOLD fMRI measurements offer the means to estimate the stimulus-evoked changes in cerebral metabolic rate of oxygen in a totally non-invasive manner (Kim and Ugurbil, 1997, Davis et al., 1998, Hoge et al., 1999). The main drawbacks of quantitative CBF and CBF fMRI measurements are relatively low temporal resolution, low signal-to-noise ratio (SNR) per unit time, and greater susceptibility to motion artifacts (Calamante et al., 1999, Barbier et al., 2001).
CBF can be measured by using an exogenous intravascular contrast agent or by magnetically labeling the endogenous water in blood (Calamante et al., 1999, Barbier et al., 2001). The former is efficient but it is incompatible with dynamic CBF fMRI because the long half life of the contrast agent allows only one CBF measurement per bolus injection. Arterial spin labeling (ASL) techniques, on the other hand, are totally non-invasive, and the labeled water has a short half-life (∼ blood T1) making it possible to perform repeated measurements which can be used to augment spatial resolution and/or signal-to-noise ratio. ASL is compatible with dynamic CBF fMRI studies.
ASL can be performed using pulsed labeling (Detre et al., 1994, Wong et al., 1998, Wang et al., 2005) or continuous labeling (Silva et al., 1995, Zaharchuk et al., 1999, Talagala et al., 2004); both are capable of multislice and whole-brain imaging. Continuous ASL (cASL) can be achieved with the same radiofrequency (RF) coil used for imaging or a separate neck coil. cASL with a separate neck coil is generally more sensitive relative to the single-coil technique (Kim, 1995, Wong et al., 1998, Wang et al., 2005), particularly in small animals such as rodents which have short arterial transit time (Silva et al., 1999, Duong et al., 2000b). With the separate neck coil, magnetization-transfer effect is eliminated if the coils are properly decoupled, resulting in a larger signal difference between labeled and non-labeled images, and thus improved CBF SNR. RF power deposition is localized to the neck area and unlabeled images can be acquired without labeling RF, reducing specific absorption rate (SAR) (Zhang et al., 1995). While cASL technique for measuring quantitative basal CBF and CBF-based MRI is more readily available on animal scanners for rodent imaging (Silva et al., 1999, Duong et al., 2000b), similar studies on humans and large non-human primates are sparse because clinical scanners generally lack the necessary hardware and software. cASL using a separate neck coil has been reported on General Electric scanners for human studies (Zaharchuk et al., 1999, Talagala et al., 2004), although its advantage over the single-coil arterial spin labeling technique remains to be demonstrated because of the long arterial transit time in humans. The typical spatial resolution of basal ASL CBF measurements on human scanners was ~ 70 mm3 (Zaharchuk et al., 1999, Talagala et al., 2004). CBF-based fMRI using cASL with a separate neck coil on human scanners remains to be demonstrated.
The goal of this study was to implement a three-coil arterial spin-labeling technique on a Siemens 3T Trio clinical scanner for non-human primate (rhesus monkey) studies. Due to the difficulty and safety concerns in re-configuring the Siemens hardware, we instead constructed a stand-alone hardware unit for cASL using a separate neck coil. Hardware components which included an external RF amplifier, control electronics, optical–electrical relays, active decoupling circuits and radiofrequency probes were built, interfaced and tested on a Siemens 3T Trio. This approach was demonstrated by obtaining: (i) high-resolution (1.5-mm isotropic resolution or 3.3 mm3 resolution) quantitative basal CBF in 3 min, and (ii) high-resolution combined CBF and BOLD fMRI with 8-s temporal resolution associated with hypercapnic and hyperoxic challenges. Technical issues associated with performing CBF measurements on rhesus monkeys are detailed.
Section snippets
Animal preparations
Rhesus monkeys (n = 6, 5.6–8.3 kg) were initially anesthetized with ketamine (10 mg/kg, i.m.) and intubated. The animals breathed on their own under 0.9–1.1% isoflurane delivered to a non-rebreathing circuit. Gas flow to the animals was delivered at a rate of 2–3 ml/min. Animal was positioned on the stomach with the eyes facing along the magnet bore, stabilized in an animal holder with ear bars and mouth bar. Body temperature was maintained by a feedback-regulated circulating warm-water blanket.
Optimizing ASL parameters
Locations of the brain and neck RF coils and the imaging slabs are shown in Fig. 2A. This MR image was acquired using a “volume coil” which were not used in our subsequent CBF measurements. Fig. 2B shows the head-holder setup, brain and neck RF coils. Cross-sectional images of the neck using the neck coil were acquired to ensure sufficient coverage and, thus, proper labeling of the carotid and vertebral arteries (Fig. 2C). To verify proper coil-to-coil electromagnetic decoupling, images were
Discussion
A three-coil continuous arterial-spin-labeling technique using a separate neck coil was implemented on a Siemens 3T Trio for quantitative CBF MRI and CBF-based fMRI measurements. Multislice and quantitative basal CBF images were obtained in 3 min at 1.5-mm isotropic resolution. The optimal labeling RF power, labeling efficiency and post-labeling delay were determined. Quantitative GM and WM CBF were obtained. Combined BOLD and CBF fMRI measurements were made with an 8-s temporal resolution at
Conclusions
This study reports quantitative CBF measurements with 3-min resolution and the combined CBF and BOLD fMRI with 8-s resolution in rhesus monkeys at 1.5-mm isotropic resolution. Further improvements in spatial and temporal resolution are expected. With its unique advantages, quantitative perfusion imaging and perfusion-based fMRI using cASL with a separate neck coil are expected to have increasing applications in both experimental research and clinical setting. These results set the stage for
Acknowledgments
This work is supported in part by a Venture Grant from the Center for Behavioral Neuroscience (NSF IBN-9876754). The Yerkes Imaging Center is supported in part by a base grant from the NIH/NCRR (P51 RR000165). TQD is supported in part by a Scientist Development Grant from the American Heart Association (SDG-0430020N).
References (47)
- et al.
Gender differences in brain volume and size of corpus callosum and amygdala of rhesus monkey measured from MRI images
Brain Res.
(2000) - et al.
Anatomical and functional MR imaging in the macaque monkey using a vertical large-bore 7 Tesla setup
Magn. Reson. Imag.
(2004) - et al.
Effects of hypoxia, hyperoxia and hypercapnia on baseline and stimulus-evoked BOLD, CBF and CMRO2 in spontaneously breathing animals
NeuroImage
(2005) - et al.
Quantitation of regional cerebral blood flow increases during motor activation: a steady-state arterial spin tagging study
NeuroImage
(1997) - et al.
Reduced transit-time sensitivity in noninvasive magnetic resonance imaging of human cerebral blood flow
J. Cereb. Blood Flow Metab.
(1996) - et al.
Processing strategies for time-course data sets in functional MRI of human brain
Magn. Reson. Med.
(1993) - et al.
Methodology of brain perfusion imaging
J. Magn. Reson. Imaging
(2001) - et al.
Measurement of regional cervical–cerebral transit time at high temporal resolution using dynamic susceptibility contrast
Int. Soc. Med. Reson.
(2002) - et al.
Measuring cerebral blood flow using magnetic resonance imaging techniques
J. Cereb. Blood Flow Metab.
(1999) - et al.
Effect of basal conditions on the magnitude and dynamics of the blood oxygenation level-dependent fMRI response
J. Cereb. Blood Flow Metab.
(2002)
Calibrated functional MRI: mapping the dynamics of oxidative metabolism
Proc. Natl. Acad. Sci. U. S. A.
Tissue specific perfusion imaging using arterial spin labeling
NMR Biomed.
Spatio-temporal dynamics of the BOLD fMRI signals in cat visual cortex: toward mapping columnar structures using the early negative response
Magn. Reson. Med.
Functional MRI of calcium-dependent synaptic activity: cross correlation with CBF and BOLD measurements
Magn. Reson. Med.
Localized blood flow response at sub-millimeter columnar resolution
Proc. Natl. Acad. Sci. U. S. A.
Cerebral normoxia in the rhesus monkey during isoflurane- or propofol-induced hypotension and hypocapnia, despite disparate blood-flow patterns. A positron emission tomography study
Acta Anaesthesiol. Scand.
Transfer insensitive labeling technique (TILT): application to multislice functional perfusion imaging
J. Magn. Reson. Imaging
What is the correct value for the brain–blood partition coefficient for water?
J. Cereb. Blood. Flow Metab.
Linear coupling between cerebral blood flow and oxygen consumption in activated human cortex
Proc. Natl. Acad. Sci.
The effects of altered arterial tensions of carbon dioxide and oxygen on cerebral blood flow and cerebral oxygen consumption of normal young men
J. Clin. Invest.
Quantification of relative cerebral blood flow change by flow-sensitive alternating inversion recovery (FAIR) technique: application to functional mapping
Magn. Reson. Med.
Comparison of blood oxygenation and cerebral blood flow effects in fMRI: estimation of relative oxygen consumption change
Magn. Reson. Med.
Cited by (28)
Longitudinal evaluation of the functional connectivity changes in the secondary somatosensory cortex (S2) of the monkey brain during acute stroke
2023, Current Research in NeurobiologyEffects of alfaxalone on cerebral blood flow and intrinsic neural activity of rhesus monkeys: A comparison study with ketamine
2021, Magnetic Resonance ImagingCitation Excerpt :In contrast, ketamine has vasodilation effect and would increase CBF substantially in spontaneously-breathing goats [35] and rabbits [34] and humans [33,64,65], in agreement with our present findings. Isoflurane is also well-known for its vasodilation effect [66–68]. Accordingly, alfaxalone and ketamine showed contrary effects on CBF of the monkey brain.
Biophysically based method to deconvolve spatiotemporal neurovascular signals from fMRI data
2018, Journal of Neuroscience MethodsCitation Excerpt :To interpret and exploit the BOLD signal, uncovering the dynamics of its underlying physiological processes, i.e., neural activity, astrocytic dynamics, cerebral blood flow (CBF), cerebral blood volume (CBV), and deoxygenated hemoglobin (dHb) concentration, is crucial. The conventional way to study these processes is through other neuroimaging modalities such as electroencephalography (EEG), positron emission tomography (PET), invasive optical imaging, arterial spin labeling (ASL), vascular space occupancy (VASO), near infrared spectroscopy (NIRS), or diffuse optical tomography (DOT) (Feng et al., 2004; Newberg et al., 2005; Hillman et al., 2007; Zhang et al., 2007; Talagala et al., 2004; Boas et al., 2001). These modalities have a variety of spatial and temporal resolutions, each of which reveals particular structural and functional features of the brain.
Ultra-high spatial resolution basal and evoked cerebral blood flow MRI of the rat brain
2015, Brain ResearchCitation Excerpt :CBF in the entire corpus callosum was 0.32 ml/g/min, compared to cortical gray mater CBF of 0.89–1.16 ml/g/min, with the GM:WM CBF ratio ranging from 2.8 to 3.6. By comparison, previous GM:WM CBF ratios have been reported to be 2.3 in baboon (Wey et al., 2011), 2.3 in rhesus by MRI (Zhang et al., 2007), and 2.0 by PET (Ye et al., 2000). A high-resolution autoradiographic CBF study also reported a GM:WM ratio of 2.5–3.2 (calculated based on their data) (Iadecola and Xu, 1994).
Effect of high dose isoflurane on cerebral blood flow in macaque monkeys
2014, Magnetic Resonance ImagingCitation Excerpt :The arterial-spin-labeling (ASL) MRI technique is a non-invasive approach to measure CBF quantitatively by using intrinsic blood water as a freely diffusible tracer [18]. Continuous ASL (CASL) technique with separate labeling coil is an optimal setting for CBF measurements in preclinical research scanners and has been implemented successfully in clinic scanners [19,20]. However, the CASL technique with separate labeling coil is not accessible in most clinical scanners as it requires additional RF hardware.
- 1
These authors contributed equally to this work.