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The major goals of the shim design were maximization of shim field accuracy and ease of practical implementation.
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This equipment has been adapted for pediatric use with the provision of shims designed to properly position smaller feet relative to the transducers.
The effective delayed neutron fractions were found to be 8.39 ± 0.0006 × 10−3 and 8.43 ± 0.0006 × 10−3 for the Al shim tray design and the Zr-4 shim tray design respectively.
A final multiplication factor of the Al shim tray design was recorded as 1.00389 ± 0.0006 whilst that of the Zr-4 shim tray design was recorded as 1.00468 ± 0.0006.
An NMR shim coil design method that addresses the severe spatial constraints of miniaturized dipole magnets is introduced.
In addition, Shim also designed its enhanced version (S-GPAKE) using a symmetric encryption algorithm to overcome the attack.
Several examples of gradients and shims were designed and simulated to demonstrate this, as well as to investigate the behaviour of new cost functions.
Shim rods are designed to compensate for the effects of burnup (i.e., energy production).
Gradient and shim coils were designed using boundary element methods with convex optimisation.
The inhomogeneity has a specific spatial symmetry, which scales linearly with temperature, and a single-channel shim coil was designed to compensate for the inhomogeneity.
Parallel radiofrequency (RF) transmission, either in the form of RF shimming or pulse design, has been proposed as a solution to the B+1 inhomogeneity problem in ultra high field magnetic resonance imaging.
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