Abstract: A method of estimating the true uptake of a tracer in a physiological image acquired with a physiological image modality that has limited spatial resolution comprises: co-registering an anatomical image volume and the physiological image volume such that both image volumes have corresponding voxels; segmenting the anatomical image volume into a number of non-overlapping anatomical regions; combining each of the segmented anatomical regions with a function representative of the limited spatial resolution of the physiological image modality to generate a blurred anatomical region volume for each of the segmented regions; assuming the physiological image in each voxel to be a linear sum of the image intensities of the corresponding voxels in the blurred region volumes in that voxel; estimating, for each voxel, a value representative of the contribution to that voxel from each blurred region volume based on the uptake measured by the physiological image for that voxel and for nearby voxels; and using the estimate

Abstract: The invention relates to detectors for radiological imaging, and more particularly the X-ray matrix detectors, produced in the form of a CMOS technology pixel matrix, associated with a structure for converting X-rays into electrons. Each pixel comprises a reading circuit comprising on the one hand a comparator (COMP1) switching over each time a charge increment arrives resulting from the integration of a charge current generated by the lighting and on the other hand a counting circuit (CPT1, CPT2) for counting the number of switchovers of the comparator. The circuit for reading each pixel comprises a circuit (CMC) for analyzing the rate of the switchovers of the comparator, this analysis circuit acting on the counting circuit to modify its operation according to the result of the rate analysis. For example, the analysis circuit switches the counting pulses to one counter (CPT1) or another counter (CPT2) depending on the result of the analysis.

Abstract: The invention relates to detectors for radiological imaging, and more particularly the X-ray matrix detectors, produced in the form of a CMOS technology pixel matrix, associated with a structure for converting X-rays into electrons. Each pixel comprises a reading circuit comprising on the one hand a comparator (COMP1) switching over each time a charge increment arrives resulting from the integration of a charge current generated by the lighting and on the other hand a counting circuit (CPT1, CPT2) for counting the number of switchovers of the comparator. The circuit for reading each pixel comprises a circuit (CMC) for analyzing the rate of the switchovers of the comparator, this analysis circuit acting on the counting circuit to modify its operation according to the result of the rate analysis. For example, the analysis circuit switches the counting pulses to one counter (CPT1) or another counter (CPT2) depending on the result of the analysis.