Variable precision registration via wavelets: Optimal spatial scales for inter-subject registration of functional MRI
Introduction
Image registration has a central role in the fMRI processing pipeline, correcting for subject motion in preprocessing and, moreover, differences in inter-subject anatomy. The low signal-to-noise ratio of BOLD activation (Parrish et al., 2000) leads inevitably to the necessity for multi-subject studies. To identify regions activated by a particular stimulus or cognitive task across a group of subjects, or regional differences between groups, the image data are mapped onto a reference image in a known coordinate system. In doing so, it is implicitly assumed that each voxel location represents the same anatomical location in all images and statistical inference then typically proceeds on a voxelwise basis.
Image registration algorithms that deform an image onto a fixed template have three essential components: a cost function that measures the similarity between images, a parameterised mapping from the native space of the deformable image to the standard space of the fixed template and a strategy for searching the parameter space of the mapping. The intention is then to search for the optimal parameters of the mapping that minimise (or maximise) the cost function. This cost function may either be based on the intensity of all non-zero voxels or on the correspondence of anatomical landmarks. It may also be constrained to avoid unphysical mappings that contain features such as ‘foldings’ or ‘tearings’.
Image registration is central in the debate over the origins of differences observed with tissue morphometry; that is, the statistical analysis of spatially normalised, segmented, high-resolution structural MRI data (Bookstein, 2001, Ashburner and Friston, 2001, Friston and Ashburner, 2004, Davatizikos, 2004). In this context, criticism has been focused on whether the differences observed are so confounded by residual mis-alignment as to be uninterpretable. More fundamentally, the question has been raised as to whether it is possible to automatically determine any neuroanatomically meaningful mapping at all. If such an ideal mapping were indeed available, there would still remain the mis-registration of anatomy across a population due to the marked biological variability of brain structures between individuals (Thompson et al., 1998, Juch et al., 2005). Whilst this debate has been conducted in relation to structural data, the arguments can be translated to discussions of functional data. The dilemma we are thus presented with is how to obtain patterns of activation (or differential activation) elicited by cognitive paradigms, eschewing inter-subject variability, without the prospect of an algorithm capable of exact one-to-one mappings.
The effect of inhomogeneous spatial normalisation on patterns of brain functional activation has not been extensively considered. Gee et al. (1997) noted that an inhomogeneous deformation yields improved performance over affine mappings alone in fMRI, with similar results in PET (Crivello et al., 2002). It would therefore appear that insufficient alignment of images results in a loss of sensitivity. But is it possible to ‘over-register’ the data? That is, would a mapping parameterised to operate at finer spatial scales than the coarsest common features of the images actually provide a non-optimal solution?
We describe a method of registration that poses the problem of anatomical mapping in the wavelet domain. This multi-resolution basis for registration means that the lower and upper spatial scales of the displacement field can be varied systematically in a search for the mapping that maximises the observed activation. To illustrate this approach, we apply it to fMRI data acquired from two groups of subjects (young and older healthy volunteers) during performance of a paired associate learning task. The quality of registration achieved by using various ranges of scales of the wavelet transform is quantified in terms of the final value of the cost function as well as geometric measures of the overlap between the image volumes. These metrics can also be compared to a “bottom line” measure—the number of generically activated voxels identified following variable precision registration.
Section snippets
Overview
Twelve young and 12 older healthy volunteers were each scanned using fMRI during performance of a paired associate learning task. Estimates of the overall activation elicited by the task were made at each voxel in the native (acquisition) space of each subject. A high-resolution anatomical image of each subject was interpolated to the same image dimensions as the Montreal Neurological Institute (MNI) standard “EPI” template image [SPM99, http://www.fil.ion.ucl.ac.uk/spm] and initially mapped to
Anatomical metrics of variable precision registration
For each group of subjects considered separately, the mean and standard deviations of the final value of the cost function and the geometric parameters G1 and G2 (Eqs. (10), (11)) were plotted for the complete set of initial/final scales (Fig. 1). The cost function was significantly reduced compared to the affine transform, for all wavelet-mediated deformation mappings (affine relative to scales {4/7} for younger subjects: t = 2.89, df = 11, P = 1.46 × 10−2, and for older subjects: t = 4.91, df
Discussion
There are a number of key findings from this study. First, we have replicated prior reports that substantial improvements in sensitivity to detect functionally activated voxels can be achieved in analysis of fMRI data by using inhomogeneous deformation algorithms, in addition to an affine transform, for coregistration of individual statistic maps in a standard space. Specifically, here, we have found that the number of activated voxels can be increased by a factor of 4 or more (depending on the
Acknowledgments
This neuroinformatics research was supported by a Human Brain Project grant from the National Institute of Biomedical Imaging and Bioengineering and the National Institute of Mental Health. Functional MRI data acquisition was supported by a grant from GlaxoSmithKline. We thank colleagues in the MRI Unit, Maudsley Hospital, London UK for data collection and technical assistance.
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