Correcting for main magnetic field inhomogeneity in MRI scanners

• US 10,018,700 B2
• Filed: 07/10/2015
• Issued: 07/10/2018
• Est. Priority Date: 07/11/2014
• Status: Active Grant

• Current Assignee: The General Hospital Corporation (Mass General Brigham, Inc.), University Of Cape Town
• Original Assignee: The General Hospital Corporation (Mass General Brigham, Inc.), University Of Cape Town
• Inventors: Alhamud, Alqadafi Ali, Meintjes, Ernesta Maria, Van Der Kouwe, Andre Jan Willem
• Primary Examiner(s): Assouad, Patrick
• Assistant Examiner(s): Zhang, Haidong
• Application Number:
  US14/796,268
• Publication Number:
  US 20160047876A1
• Time in Patent Office: 1,096 Days
• CPC Class Codes: G01R 33/243 Spatial mapping of the polarizing magnetic field
• CPC Class Codes: G01R 33/4828 Resolving the MR signals of different chemical species, e.g. water-fat imaging
• CPC Class Codes: G01R 33/5616 using gradient refocusing, e.g. EPI
• CPC Class Codes: G01R 33/56341 Diffusion imaging
• CPC Class Codes: G01R 33/56509 due to motion, displacement or flow, e.g. gradient moment nulling G01R33/567 takes precedence
• CPC Class Codes: G01R 33/56563 caused by a distortion of the main magnetic field B0, e.g. temporal variation of the magnitude or spatial inhomogeneity of B0 G01R33/56509, G01R33/56518, G01R33/56536 take precedence

Abstract

A method for correcting for main magnetic field (B0) inhomogeneity in a Magnetic Resonance Imaging (MRI) scanner is disclosed. The method includes applying a first and a second three-dimensional volumetric navigator after an acquisition of a volume in a scanning sequence and before the next volume is acquired. From a resultant pair of navigator images, a magnetic field map is obtained by complex division of the pair of navigator images, and the field map is used to determine parameters to adjust the MRI scanner to compensate for B0 inhomogeneity. The navigators may excite only a portion of an entire object to be imaged, so that adjustment of the MR scanner can be done slice-by-slice or slab-by-slab. Motion correction can also be implemented by comparing the first navigator to a stored reference image and updating for motion before acquisition of the next volume in the scanning sequence.

Claims

1. A method of correcting for main magnetic field (B0) inhomogeneity in a Magnetic Resonance Imaging (MRI) scanner during a scanning sequence which includes the acquisition of successive volumes by means of Magnetic Resonance (MR) pulse sequences, comprising:

after an acquisition of a volume in the scanning sequence;

applying, by the MRI scanner, a first three-dimensional volumetric navigator and obtaining a first navigator image,

applying, by the MRI scanner, a second three-dimensional volumetric navigator after the first navigator and obtaining a second navigator image, wherein the first and second navigators have different echo times;

after the first and second navigator images have been obtained and before the acquisition of the next volume in the scanning sequence;

determining a magnetic field map by complex division of the first and second navigator images;

using the magnetic field map to determine parameters required to adjust the homogeneity of the main magnetic field (B0), the determined parameters including a zero order shim which is estimated from the magnetic field map based on a least-squares fit; and

adjusting the MRI scanner based on the determined parameters by adjusting a system central frequency of the MRI scanner, the system central frequency being adjusted by adjusting a phase and frequency for a Numerically Controlled Oscillator (NCO) of the MRI scanner for all radiofrequency (RF) excitation pulses of the MRI scanner and for Analog to Digital Converter (ADC) pulses of the MRI scanner for both the scanning sequence and for the first and second navigators.

2. The method as claimed in claim 1, wherein the determined parameters include first or higher order shims which are estimated from the magnetic field map, and wherein the MRI scanner is adjusted by adjusting one or more shim coils of the MRI scanner with the determined parameters.

3. The method as claimed in claim 1, which includes:

after obtaining the first navigator image, and during the course of acquiring the second navigator, estimating motion parameters which include three translations and three rotations by comparing the first navigator image to a stored reference image; and

after applying the second navigator and before acquisition of the next volume in the scanning sequence, updating for motion,

so as to correct for motion of an object being imaged.

4. The method as claimed in claim 1, wherein the first and second navigators are echo planar imaging (EPI) navigators, and where the EPI navigators are identical except for having different echo times.

5. The method as claimed in claim 4, wherein the difference in the echo times for the first EPI navigator and second EPI navigator is chosen so that a resultant signal produced by the excitation of fat and water by the two EPI navigators is in phase, so that any phase offset in the filed map is attributable to inhomogeneity in the main magnetic field.

6. The method as claimed in claim 5, wherein the main magnetic field (B0) strength is about 3 Tesla and wherein echo times of about 6.6 milliseconds and about 9 milliseconds are chosen for the first and second navigators.

7. The method as claimed in claim 1, wherein the scanning sequence is one of:

a Functional Magnetic Resonance Imaging (fMRI) scanning sequence, and a Diffusion Tensor Imaging (DTI) scanning sequence.

8. The method as claimed in claim 1, wherein the navigators have low flip angles to ensure that an MRI contrast of the navigators do not influence a contrast of the MRI scanning sequence.

9. The method as claimed in claim 8, wherein the flip angle is about 2°

.

10. The method as claimed in claim 1, wherein the first and second navigator pulse sequences have a spatial resolution of between 6×

6×

6 mm³ and 10×

10×

10 mm³.

11. The method as claimed in claim 10, wherein the first and second navigator pulse sequences have a spatial resolution of approximately 8×

8×

8 mm³ and the navigator images are obtained in about 0.48 seconds.

12. The method as claimed in claim 1, wherein each three-dimensional volumetric navigator excites substantially an entire object to be imaged.

13. The method as claimed in claim 1, wherein the scanning sequence includes a series of substantially two-dimensional slices of an object to be imaged.

14. The method as claimed in claim 13, wherein the parameters include zero, first or higher order shims which are estimated from the magnetic field map only for a sub-region of the magnetic field map that corresponds to a slice that is to be acquired next, so that adjustment of the MR scanner is done slice-by-slice to account for main magnetic field (B0) inhomogeneity in the next slice to be imaged.

15. The method as claimed in claim 1, wherein the scanning sequence includes a series of substantially three-dimensional portions, called slabs, of the object to be imaged.

16. The method as claimed in claim 15, wherein the parameters include zero, first or higher order shims which are estimated from the magnetic field map only for a sub-region of the magnetic field map that corresponds to a slab that is to be acquired next, so that adjustment of the MR scanner is done slab-by-slab to account for main magnetic field (B0) inhomogeneity in the next slab to be imaged.

17. The method as claimed in claim 1, in which the method is applied after the acquisition of every volume in the scanning sequence.

18. The method as claimed in claim 1, in which the method is applied after one out of every fixed number of volume acquisitions in the scanning sequence.