“Authors: Daniel Kalthoff and Mathias Hoehn, In-vivo NMR Laboratory, Max-Planck-Institute for Neurological Research, Cologne, Germany”
Functional magnetic resonance imaging (fMRI) of the brain’s “resting state” (rsfMRI), and its measurement of functional connectivity, has gained significant attention over the last 15 years.
It is believed that low-frequency fluctuations observed in the BOLD signal reflect spontaneous neural activity, and that synchronized fluctuations in distinct brain regions thus point to a functional connection between them (Fig. 1).
First demonstrated for the human motorcortex (Biswal et al., 1995), numerous connectivity networks have been identified in the human brain and have been shown to change in various neurological and psychiatric diseases. This renders functional connectivity MRI (fcMRI) a highly interesting technique to further our understanding of brain function in health and disease.
Establishing fcMRI in animal models has only begun a few years ago. Particularly in rodents, the technique is highly attractive as it is expected to provide a functional readout for disease progression, therapy and repair in a large number of existing animal models. In contrast to fMRI, fcMRI does not rely on stimulation and can probe brain networks that are not accessible through external stimuli. It also takes on the key advantages of MRI regarding non-invasiveness and suitability for longitudinal studies. We therefore evaluated the feasibility and potential of fcMRI applied to imaging of the rat brain using a high field, small animal MRI system.
Experimental Protocol MRI System – 117/16 Bruker BioSpec (1H @ = 500 MHz); BGA9s gradient system (Gmax=750 mT/m; min. ramp time of 125 μs); Avance II electronics; quadrature volume resonator (inner diameter 72 mm) for transmission; rat brain quadrature surface coil (~30×30 mm2) for reception; ParaVision 5
Physiological Monitoring – Monitoring system (SA Instruments): respiratory pad, pulse oxymeter, fiber optic temperature probe; display and recording (synced to MRI acquisition) of respiration, pulse and temperature using a custom-made data acquisition software (DasyLab).
Imaging Protocol– TurboRARE for T2-weighted anatomical reference (RARE-factor 8, 28 slices á 0.5 mm, 256 ^2 matrix, 125 x 125 μm2, TR 4.0 s, TEeff 32.5 ms, 2 averages, acq. time 4m16s); FieldMap acquisition and local MapShim; single-shot gradient echo EPI for functional image acquisition (see table).
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Anaesthesia Protocol– Initial anaesthesia using 1.5 % Isoflurane; transition to Medetomidine sedation: subcutaneous 0.5 ml bolus and subsequent infusion of 1 ml/h of Domitor® solution (Pfizer; 0.1 ml/kg ad 10 ml saline solution); cf. Weber et al. (2006) and Kalthoff et al. (2011) for details.
Processing & Analysis– Motion correction and coregistration to rat brain template using FSL tools; removal of physiological noise using regression of motion and physiological parameters (Kalthoff et al., 2011); connectivity analysis with custom-made ImageJ Software and FSL tools.
Results & Discussion
High field BOLD functional MRI data of the resting rat brain reliably achieve a quality convenient for functional connectivity analysis. Employing the given EPI imaging protocol, voxel time courses typically exhibit signal fluctuations on the order of 1.5% that stem from various sources (Fig. 2).
One third of the fluctuation is owed to intrinsic raw noise of the system (primarily thermal noise from sample, coil and electronics). The majority (~ 40%) of fluctuations is due to physiological noise originating from the cardio-respiratory cycle and related pseudo-motion. In order to minimize falsepositive (non-neuronal) correlations in subsequent analyses, physiological noise should be corrected by motion correction and regression, which can improve tSNR by ~ 30% (cf. Kalthoff et al. 2011 for details). The residual ~ 25% of fluctuations may be attributed to actual neurovascular fluctuations at which the subsequent functional connectivity analysis is aimed.
Seed based connectivity analysis (SCA) can create connectivity maps that visualize the temporal correlation of voxels with á priori defined seed regions. Rat brain functional connectivity maps from seed regions in cortex and striatum show distinctly bilateral regions, indicative of strong interhemispheric connectivity between homologous regions (Fig. 3). It must be noted that observation of strong, reliable and specific connectivity networks may not be possible using conventional Isoflurane anaesthesia, but requires physiologically more sensitive experimental protocols such as Medetomidine sedation (Weber 2006, Pawela 2008, Williams 2010).
The topology of functional connectivity networks can also be explored using data-driven techniques such as independent component analysis (ICA, cf. e.g. Beckmann 2005). ICA reliably identifies segregated rat brain functional networks in cortical and subcortical structures on a per-subject basis (Fig. 4). Such techniques are particularly interesting to compare network topologies without á priori hypotheses in pathologies or between species (cf. Jonckers 2011 for rat / mouse comparison).
It is known from human studies that functional connectivity is sensitive to a variety of neurological disorders. Preliminary studies show that this holds true for several animal models, for example in the longitudinal assessment of network remodelling after stroke (Fig. 5).
Conclusion & Directions
Functional connectivity MRI of the rodent brain can provide a highly interesting functional readout for disease progression, therapy and repair in a large number of existing animal models. With the technical advancement and widespread availability of high field systems, the challenge of fcMRI has shifted towards innovative data analysis strategies and maintenance of an appropriate physiological state.
Functional connectivity – particularly in combination with other modalities – will become a central concept for neuroscientific research in the near future. One of the next pivotal steps to exploit this potential is the establishment of routine protocols for mouse fcMRI to access the rich variety of transgenic animal models.
Biswal B, Yetkin FZ, Haughton VM, Hyde JS (1995) Functional connectivity in the motor cortex of resting human brain using echo-planar MRI. Magn Reson Med 34:537-41 Weber R, Ramos-Cabrer P, Wiedermann D, van Camp N, Hoehn M (2006) A fully noninvasive and robust experimental protocol for longitudinal fMRI studies in the rat. Neuroimage 29:1303-10 Kalthoff D, Seehafer JU, Po C, Wiedermann D, Hoehn M (2011) Functional connectivity in the rat at 11.7T: Impact of physiological noise in resting state fMRI. Neuroimage 54:2828-39 Pawela CP, Biswal BB, Cho YR, Kao DS, Li R, Jones SR, Schulte ML, Matloub HS, Hudetz AG, Hyde JS (2008) Resting-state functional connectivity of the rat brain. Magnetic Resonance in Medicine 59:1021-9 Williams KA, Magnuson M, Majeed W, LaConte SM, Peltier SJ, Hu X, Keilholz SD (2010) Comparison of alpha-chloralose, medetomidine and isoflurane anesthesia for functional connectivity mapping in the rat. Magn Reson Imaging 28:995-1003 Beckmann CF, DeLuca M, Devlin JT, Smith SM (2005) Investigations into resting-state connectivity using independent component analysis. Philosophical Transactions of the Royal Society B-Biological Sciences 360:1001-13 Jonckers E, Van Audekerke J, De Visscher G, Van der Linden A, Verhoye M (2011) Functional Connectivity fMRI of the Rodent Brain: Comparison of Functional Connectivity Networks in Rat and Mouse. PLoS One 6:e18876
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