An approach to high resolution diffusion tensor imaging in fixed primate brain
Introduction
Numerous factors affect the final quality of diffusion tensor imaging (DTI) or high angular resolution diffusion imaging (HARDI) scans of brain tissue. Parameters such as spatial resolution, b-value, q-space sampling (e.g. spherical shells, Cartesian, etc.), pulse sequence type, brain coverage, etc. can be traded off against each other, however the ultimate constraints are the magnet’s gradient system and the total time available for the scan. The maximum gradient strength sets the relationship between the maximum b-value and TE, and hence links diffusion contrast with SNR. The gradient duty cycle limit constrains the number of slices (for multislice acquisitions) or the minimum TR (for 3D acquisitions). Typically therefore, one would scan using both the maximum gradient strength and maximum duty cycle available. As with all MRI scans, SNR scales with the total imaging time available. For fixed tissue samples this is limited only by the scanner's stability and local scheduling issues. As a result, there have been numerous high resolution structural MRI studies of fixed human and animal brains, both as a means of relating MRI contrast to standard pathology and histopathology (Augustinack et al., 2005, Boyko et al., 1994, Fatterpekar et al., 2002, Fernando et al., 2004, Jacobs et al., 1999, Johnson et al., 1993, Pfefferbaum et al., 2004) and as a method of morphological phenotyping in genetically modified animals (Benveniste and Blackband, 2002, Johnson et al., 2002a, Johnson et al., 2002b).
Most MR microscopy scans on fixed neural tissue derive image contrast from variations in T2* and proton density (Augustinack et al., 2005, Blamire et al., 1999, Fatterpekar et al., 2002), however there has been growing interest in the use of diffusion weighted imaging and DTI as an important source of contrast in fixed brains (D’Arceuil et al., 2005, de Crespigny et al., 2005b, Englund et al., 2004, Guilfoyle et al., 2003, Jacobs et al., 1999, Johnson et al., 1993, Kroenke et al., 2005, Kroenke et al., 2006, Larsson et al., 2004, Mori et al., 2001, Pfefferbaum et al., 2004, Schwartz et al., 2003, Shepherd et al., 2006, Shepherd et al., 2003a, Shepherd et al., 2003b, Sun et al., 2005, Sun et al., 2003, Tyszka et al., 2006, Verma et al., 2005, Yen et al., 2005). Evidence from rat brain (Sun et al., 2003), and human brain (Guilfoyle et al., 2003) and spinal cord (Mamata et al., 2006) suggests that while the apparent diffusion coefficient (ADC, taken hereafter to mean the mean diffusivity, or Trace/3 of the diffusion tensor), is reduced in fixed tissue, the fractional diffusion anisotropy (FA) is preserved, even after stroke (Sun et al., 2005). Another key advantage of ex vivo MRI of the brain is the ability to use exogenous contrast agents (e.g. Gd-DTPA) to enhance image contrast throughout the tissue (as opposed to just vessels and certain pathologies) (Benveniste and Blackband, 2002, Johnson et al., 1993). For DTI, where image contrast is not directly dependent upon tissue relaxation times, contrast agents can be used to permit more rapid scanning and/or improved SNR (D’Arceuil et al., 2005, Tyszka et al., 2006). Specifically, it allows us to optimize the tissue relaxation parameters to best suite the MRI scanner/imaging sequence, rather then only optimizing the pulse sequence to suit the sample as is the case in vivo.
Given the growing interest in diffusion MRI of fixed neural tissue, we have explored some of the major factors affecting image quality and SNR in such acquisitions, with the ultimate aim of generating optimum data for high resolution ex vivo diffusion tractography studies. In particular, we investigated the use of a Gd-based contrast agent for DTI in fixed primate brain, and compared in vivo and ex vivo DTI in the same brains. We also evaluated the effect of sample temperature upon the SNR of the DTI data, and studied the effect of the contrast agent on standard histopathological examination of brain sections.
Section snippets
Brain specimens
Brain tissue was obtained from an ongoing study of stroke in nonhuman primates (de Crespigny et al., 2005a). All procedures were conducted with approval of the committee on research animal care at our institution. The brains from 6 adult male macaques (M. fasicularis, 7–9 kg) were removed following euthanasia (overdose of sodium pentobarbital) at the end of the stroke study and fixed by immersion in 10% formaldehyde solution for at least 4 weeks. For the purpose of the present study, we only
Relaxivity measurements
Fig. 1A shows 4.7 T relaxation time maps of tissue slices soaked in formalin and increasing concentrations of contrast agent. Relaxation times decreased with increasing Gd concentration, however the grayscale of the images in Fig. 1A was individually adjusted to highlight gray and white matter contrast. Gray/white T2 contrast was reduced at 5–10 mM Gd, and similarly for T2* contrast though to a lesser degree. Gray/white T1 contrast was least at 1 mM and reversed (i.e. longer T1 in white matter
Relaxation times
An appreciation of tissue relaxation parameters is an important component of pulse sequence optimization for any purpose. Relaxation parameters have been reported for live macaque brain at 4.7 T (Pfeuffer et al., 2004): 1520/67.5/31.3 ms for T1/T2/T2* in gray matter and 1080/63.8/30 ms in white matter. In Formalin fixed brain we measured 494/46/38 ms for T1/T2/T2* in gray matter and 423/34/22 ms in white matter (Fig. 2). The decrease in gray matter T1 in fixed tissue was much greater than the
Conclusions
We have described our approach to DTI in fixed brain tissue, and described several of the ancillary factors affecting image quality. The relaxation properties of fixed tissue can be modified to suit the hardware limitations of the scanner, which allowed us to approximately double the SNR per unit time for 3DFT DTI scans on our 4.7 T system. The approach can be generalized to other tissue types, field strengths and scanner hardware with comparable results, although the gradients on typical
Acknowledgments
This work was supported in part by NIH Grants NS41285, EB00790, an Established Investigator Award from the American Heart Association (AdC), and the Athinoula A. Martinos Center for Biomedical Imaging (P41RR14075, S10RR016811 and the MIND Institute). We are also very grateful for help from George Dai, Joe Mandeville and Thomas Benner.
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2021, NeuroImageCitation Excerpt :In addition, ex vivo specimens permit very long scanning times that are not biased by physiological noise (respiratory movements or blood pulsation) or motion (Augustinack et al., 2010; McNab et al., 2009; Miller et al., 2011). Conversely, death and specimen fixation induce dramatic changes in T2 relaxation time and diffusion coefficients (D'Arceuil and de Crespigny, 2007; D'Arceuil et al., 2007; Leprince et al., 2015), such as postmortem tissues depicting diffusion coefficients two to five times lower than in vivo conditions (D'Arceuil et al., 2007). This must be instrumentally compensated by more powerful gradients - also available in preclinical scanners - to obtain access to high diffusion sensitizations (up to 10,000 s/mm²) while keeping the echo time very short (typically smaller than 20 ms).