Quiet mri using alternating gradient sequence

Patent metadata

Field	Value
Publication number	US-2017356972-A1
Application number	US-201615179014-A
Country	US
Kind code	A1
Filing date	Jun 10, 2016
Priority date	Jun 10, 2016
Publication date	Dec 14, 2017
Grant date	—

Abstract

Magnetic resonance imaging (MRI) systems and methods to effect MRI data acquisition with reduced noise are described. A readout gradient, having a first polarity used to acquire and store MRI data in k-space memory during analog-to-digital conversion (ADC) of MR RF signals during one TR interval, is continued at substantially a same amplitude and vector direction and used as an image volume selection gradient during a transmitted RF excitation pulse that begins a next TR interval before the readout gradient transitions to an opposite polarity. The acquired k-space data is then used to generate an MR image.

First claim

What is claimed is:

1 . A magnetic resonance imaging (MRI) apparatus comprising:
static and gradient magnetic field generators and at least one radio frequency (RF) coil disposed within said magnetic field generators; RF transmitter and RF receiver circuits coupled to said at least one RF coil; and at least one MRI sequence control circuit including a k-space memory and at least one processor configured to control said magnetic field generators and said RF transmitter and receiver circuits during execution of an MRI data acquisition sequence including plural successive TR (repetition time) intervals wherein: a readout gradient, having a first polarity used to acquire and store MRI data in k-space memory during analog-to-digital conversion (ADC) of MR RF signals during one TR interval, is continued at substantially a same amplitude and vector direction and used as an image volume selection gradient during a transmitted RF excitation pulse that begins a next TR interval before the readout gradient transitions to an opposite polarity.

2 . The MRI apparatus as in claim 1 wherein the amplitude of said readout gradient is incrementally adjusted by less than 5% between ADC portions of TR intervals to acquire MRI data along different radially directed trajectories in k-space during successive TR intervals.

3 . The MRI apparatus as in claim 1 wherein ADC acquisition of MRI data within said next TR interval begins before echo time (TE) within said next TR interval.

4 . The MRI apparatus as in claim 3 wherein k-space MRI data is acquired along radially directed trajectories in k-space and said readout gradient in the next TR interval is continued after occurrence of said transmitted RF excitation pulse as a pre-winder gradient sufficient to insure an acquired MRI data trajectory in k-space during said next TR interval starts on one side of zero and continues onward, through zero, and beyond to the other side of zero in k-space.

5 . The MRI apparatus as in claim 4 wherein said acquired radially directed lines of k-space data are distributed over a three-dimensional volume in k-space.

6 . The MRI apparatus as in claim 1 wherein alternating gradient polarity transitions are limited to be less than 10 mT/m/ms.

7 . The MRI apparatus as in claim 1 wherein a frequency response of readout gradient amplitude transitions is dimensioned, within the acquisition sequence, to approximate an acoustic frequency null point in a frequency response of the MRI apparatus.

8 . The MRI apparatus as in claim 1 wherein ADC acquisition of MRI data within said next TR interval (a) begins during MR signal occurring after the transmitted RF excitation pulse but before any gradient echoes of said MR signal occur and (b) continues during subsequent occurrence of gradient echoes of said MR signal.

9 . The MRI apparatus as in claim 1 wherein magnetic gradient, RF transmit and RF receive events are coordinated to acquire a substantially balanced steady-state free precession (SSFP) MRI signal.

10 . A method for magnetic resonance imaging (MRI) said method comprising:
controlling MRI gradient magnetic field generators in conjunction with MRI radio frequency (RF) transmitter and receiver circuits during execution of an MRI data acquisition sequence including plural successive TR (repetition time) intervals to execute an MRI data acquisition sequence wherein: (a) a readout gradient, having a first polarity, is used to acquire and store MRI data in k-space memory during analog-to-digital conversion (ADC) of MRI RF signals during one TR interval, and (b) said readout gradient is thereafter continued, at substantially a same amplitude and vector direction, and used as an image volume selection gradient during a transmitted RF excitation pulse that begins a next TR interval before the readout gradient transitions to an opposite polarity.

11 . The MRI method as in claim 10 wherein the amplitude of said readout gradient is incrementally adjusted by less than 5% between ADC portions of TR intervals to acquire MRI data along different radially directed trajectories in k-space during successive TR intervals.

12 . The MRI method as in claim 10 wherein ADC acquisition of MRI data within said next TR interval begins before echo time (TE) within said next TR interval.

13 . The MRI method as in claim 12 wherein k-space MRI data is acquired along radially directed trajectories in k-space and said readout gradient in the next TR interval is continued after occurrence of said transmitted RF excitation pulse as a pre-winder gradient sufficient to insure an acquired MRI data trajectory in k-space during said next TR interval starts on one side of zero and continues onward, through zero, and beyond to the other side of zero in k-space.

14 . The MRI method as in claim 13 wherein said acquired radially directed lines of k-space data are distributed over a three-dimensional volume in k-space.

15 . The MRI method as in claim 10 wherein alternating gradient polarity transitions are limited to be less than 10 mT/m/ms.

16 . The MRI method as in claim 10 wherein a frequency response of readout gradient amplitude transitions is dimensioned, within the acquisition sequence, to approximate an acoustic frequency null point in a frequency response of the MRI apparatus.

17 . The MRI method as in claim 10 wherein ADC acquisition of MRI data within said next TR interval (a) begins during MR signal occurring after the transmitted RF excitation pulse but before any gradient echoes of said MR signal occur and (b) continues during subsequent occurrence of gradient echoes of said MR signal.

18 . The MRI method as in claim 10 wherein magnetic gradient, RF transmit and RF receive events are coordinated to acquire a substantially balanced steady-state free precession (SSFP) MRI signal.

Assignees

• Toshiba Medical Sys Corp

Inventors

• Wheaton Andrew J

Classifications

• G01R33/3854 Primary

  means for active and/or passive vibration damping or acoustical noise suppression in gradient magnet coil systems · CPC title

• G01R33/5614

  using a fully balanced steady-state free precession [bSSFP] pulse sequence, e.g. trueFISP · CPC title

• G01R33/4822

  in three dimensions · CPC title

• G01R33/4826

  in three dimensions · CPC title