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COSMOS assumes a model-free susceptibility distribution and keeps full fidelity to the measured data. This method has been validated extensively in in vitro, ex vivo and phantom experiments. Quantitative susceptibility maps obtained from in vivo human brain imaging also showed high degree of agreement with previous knowledge about brain anatomy ...
Susceptibility weighted imaging (SWI), originally called BOLD venographic imaging, is an MRI sequence that is exquisitely sensitive to venous blood, hemorrhage and iron storage. SWI uses a fully flow compensated, long echo, gradient recalled echo (GRE) pulse sequence to acquire images.
CONN includes a user-friendly GUI to manage all aspects of functional connectivity analyses, [1] including preprocessing of functional and anatomical volumes, [2] elimination of subject-movement and physiological noise, [3] outlier scrubbing, [4] estimation of multiple connectivity and network measures, and population-level hypothesis testing.
Demonstration of the HARP processing of a tagged cardiac MRI slice. (a) An MR image with vertical SPAMM tags. (b) shows the magnitude of its Fourier transform. By extracting the spectral peak inside the circle, a complex image is produced with a magnitude (c) and a phase (d). A tagged MRI showing motion of a human heart is shown in the image (a).
The FMRIB Software Library, abbreviated FSL, is a software library containing image analysis and statistical tools for functional, structural and diffusion MRI brain imaging data. FSL is available as both precompiled binaries and source code for Apple and PC computers. It is freely available for non-commercial use.
If a series of diffusion gradients (i.e. magnetic field variations in the MRI magnet) are applied that can determine at least 3 directional vectors (use of 6 different gradients is the minimum and additional gradients improve the accuracy for "off-diagonal" information), it is possible to calculate, for each voxel, a tensor (i.e. a symmetric ...
However, these techniques are approximate due to phase errors in the MRI data which can rarely be completely controlled (due to imperfect static field shim, effects of spatially selective excitation, signal detection coil properties, motion etc.) or nonzero phase due to just physical reasons (such as the different chemical shift of fat and ...
In 2010, an extended FLASH method with highly undersampled radial data encoding and iterative image reconstruction achieved real-time MRI with a temporal resolution of 20 milliseconds (1/50th of a second). [4] [5] Taken together, this latest development corresponds to an acceleration by a factor of 10,000 compared to the MRI situation before ...