Evgueni G Kholmovski

7511495, Mar 31, 2009

Apr 25, 2006

11/412073

Evgueni G. Kholmovski - Salt Lake City UT, US
Dennis Lee Parker - Centerville UT, US
Edward V. R. Dibella - Salt Lake City UT, US

University of Utah - Salt Lake City UT

G01V 3/00

324310, 324309, 324307

Methods and systems in a parallel magnetic resonance imaging (MRI) system utilize sensitivity-encoded MRI data acquired from multiple receiver coils together with spatially dependent receiver coil sensitivities to generate MRI images. The acquired MRI data forms a reduced MRI data set that is undersampled in at least a phase-encoding direction in a frequency domain. The acquired MRI data and auto-calibration signal data are used to determine reconstruction coefficients for each receiver coil using a weighted or a robust least squares method. The reconstruction coefficients vary spatially with respect to at least the spatial coordinate that is orthogonal to the undersampled, phase-encoding direction(s) (e. g. , a frequency encoding direction). Values for unacquired MRI data are determined by linearly combining the reconstruction coefficients with the acquired MRI data within neighborhoods in the frequency domain that depend on imaging geometry, coil sensitivity characteristics, and the undersampling factor of the acquired MRI data.

7884604, Feb 8, 2011

Mar 30, 2009

12/414632

Evgueni G. Kholmovski - Salt Lake City UT, US
Dennis Lee Parker - Centerville UT, US

University of Utah Research Foundation - Salt Lake City UT

G01V 3/00
A61B 5/05

324309, 324307, 324310, 324312, 600410

Methods and systems in a parallel magnetic resonance imaging (MRI) system utilize sensitivity-encoded MRI data acquired from multiple receiver coils together with spatially dependent receiver coil sensitivities to generate MRI images. The acquired MRI data forms a reduced MRI data set that is undersampled in at least a phase-encoding direction in a frequency domain. The acquired MRI data and auto-calibration signal data are used to determine reconstruction coefficients for each receiver coil using a weighted or a robust least squares method. The reconstruction coefficients vary spatially with respect to at least the spatial coordinate that is orthogonal to the undersampled, phase-encoding direction(s) (e. g. , a frequency encoding direction). Values for unacquired MRI data are determined by linearly combining the reconstruction coefficients with the acquired MRI data within neighborhoods in the frequency domain that depend on imaging geometry, coil sensitivity characteristics, and the undersampling factor of the acquired MRI data.

8155389, Apr 10, 2012

Aug 12, 2008

12/190287

Dennis Lee Parker - Centerville UT, US
Evgueni G. Kholmovski - Salt Lake City UT, US

The University of Utah Research Foundation - Salt Lake City UT

G06K 9/00

382107, 382128

A method, a system, and a computer-readable medium are provided which perform motion correction of image data. A first set of data and a second set of data of k-space data of an object to be imaged are received. The first set of data and the second set of data include a plurality of phase encoded lines that encompass the object to be imaged. The first set of data correlates with the second set of data. A cross-correlation is calculated by multiplying the first set of data and the second set of data in k-space. A value of the motion of the object to be imaged that occurred between acquisition of the first set of data and acquisition of the second set of data is calculated using the cross-correlation. The second set of data is corrected using the calculated value to remove the motion. The correction process is repeated until the k-space data is completely processed.

8406849, Mar 26, 2013

Apr 2, 2007

11/732382

Eun-Kee Jeong - North Salt Lake City UT, US
Dennis L. Parker - Centerville UT, US
Kim Seong-Eun Choi - Salt Lake City UT, US
Evgueni G. Kholmovski - Salt Lake City UT, US

University of Utah Research Foundation - Salt Lake City UT

A61B 5/05

600410, 600407, 600413, 324300, 324307, 324309

Methods and apparatus for operating an MRI system is provided. The disclosure provides a diffusion-prepared driven-equilibrium preparation for an imaging volume and acquiring 3-dimensional k-space data from said prepared volume by a plurality of echoplanar readouts of stimulated echoes. An excitation radio-frequency signal and first and second inversion RF signals are provided to define a field-of-view (FOV).

8427156, Apr 23, 2013

Dec 17, 2010

12/972192

Evgueni G. Kholmovski - Salt Lake City UT, US
Dennis Lee Parker - Centerville UT, US
Edward V. R. DiBella - Salt Lake City UT, US

University of Utah Research Foundation - Salt Lake City UT

G01V 3/00
A61B 5/05

324310, 324307, 324309, 324312, 600410

Methods and systems in a parallel magnetic resonance imaging (MRI) system utilize sensitivity-encoded MRI data acquired from multiple receiver coils together with spatially dependent receiver coil sensitivities to generate MRI images. The acquired MRI data forms a reduced MRI data set that is undersampled in at least a phase-encoding direction in a frequency domain. The acquired MRI data and auto-calibration signal data are used to determine reconstruction coefficients for each receiver coil using a weighted or a robust least squares method. The reconstruction coefficients vary spatially with respect to at least the spatial coordinate that is orthogonal to the undersampled, phase-encoding direction(s) (e. g. , a frequency encoding direction). Values for unacquired MRI data are determined by linearly combining the reconstruction coefficients with the acquired MRI data within neighborhoods in the frequency domain that depend on imaging geometry, coil sensitivity characteristics, and the undersampling factor of the acquired MRI data.

20070241751, Oct 18, 2007

Apr 18, 2006

11/406573

Evgueni Kholmovski - Salt Lake City UT, US
Stephan Kannengiesser - Erlangen, DE

G01V 3/00

324307000

In a PPA MRT method and apparatus, a selected region of k-space containing respective portions of some of the incomplete, measured data lines and respective portions of some of the complete, reconstructed data lines is designated. For each data line in the selected region, a level of the noise therein is identified. For each reconstructed, complete data line in the selected region, a scaling factor is calculated that is dependent on the noise level in that reconstructed, complete data line and the noise level in at least one neighboring incomplete, measured data line in the selected region. The scaling factor is then applied to the reconstructed, complete data line in question, so that the contribution of that line to the overall reconstructed image is adjusted according to the scaling factor. The scaling factor can be limited dependent on where the selected region is located in k-space.

20130158384, Jun 20, 2013

Feb 19, 2013

13/769917

Eun-Kee Jeong - North Salt Lake UT, US
Dennis L. Parker - Centerville UT, US
Kim Seong-Eun Choi - Salt Lake City UT, US
Evgueni G. Kholmovski - Salt Lake City UT, US

A61B 5/055

600410

Methods and apparatus for operating an MRI system is provided. The disclosure provides a diffusion-prepared driven-equilibrium preparation for an imaging volume and acquiring 3-dimensional k-space data from said prepared volume by a plurality of echoplanar readouts of stimulated echoes. An excitation radio-frequency signal and first and second inversion RF signals are provided to define a field-of-view (FOV).

20180303374, Oct 25, 2018

Jun 25, 2018

16/016984

- Salt Lake City UT, US
Evgueni G. Kholmovski - Salt Lake City UT, US

A61B 5/055
G01R 33/50
G01R 33/567
G01R 33/56
G01R 33/48
G01R 33/54
A61B 5/0452
A61B 5/046

A method of optimizing scan parameters for LGE-MRI. At least one cardiac MRI TI scout scan is performed by applying an inversion pulse every predetermined heartbeat of a patient. An initial value of an inversion time TIis determined by assessing a set of images generated from the scout scan. A first multiple of a duration between successive indicia of ventricular depolarization is selected, and a relaxation time T is determined based on the initial value Tand the first multiple of duration. An optimized inversion time TIfor LGE-MRI is determined based on the relaxation time T and a second multiple of a duration between successive indicia of ventricular depolarization. A correction factor is determined based on the optimized inversion time TIfrom the initial value of the inversion time TI.