Multi-purpose gradient array for magnetic resonance imaging

• US 10,571,537 B2
• Filed: 09/01/2017
• Issued: 02/25/2020
• Est. Priority Date: 05/21/2015
• Status: Active Grant

• Current Assignee: Bilkent University
• Original Assignee: Bilkent University
• Inventors: Atalar, Ergin, Ertan, Niyazi Koray, Taraghinia, Soheil
• Primary Examiner(s): Vargas, Dixomara
• Application Number:
  US15/694,029
• Publication Number:
  US 20180011156A1
• Time in Patent Office: 907 Days
• CPC Class Codes: G01R 33/385 using gradient magnetic field coils
• CPC Class Codes: G01R 33/3852 Gradient amplifiers; means for controlling the application of a gradient magnetic field to the sample, e.g. a gradient signal synthesizer
• CPC Class Codes: G01R 33/4835 of multiple slices

Abstract

A system for multi-slice magnetic resonance imaging (MRI) comprises a gradient coil array comprising a plurality of independent coils distributed about an enclosure; and a controller configured to concurrently actuate said plurality of coils so as to generate a spatially-varying magnetic field within said enclosure such that for at least first and second volumetric slices, a magnetic field magnitude associated with at least one location in the first volumetric slice is substantially equal to a magnetic field magnitude associated with a respective location in the second volumetric slice.

Claims

1. A system for multi-slice magnetic resonance imaging (MRI), comprising:

a gradient coil array comprising a plurality of independent coils distributed about an enclosure; and

a controller configured to concurrently actuate said plurality of coils so as to generate a spatially-varying magnetic field within said enclosure such that for at least first and second volumetric slices, a magnetic field magnitude associated with at least one location in the first volumetric slice is substantially equal to a magnetic field magnitude associated with a respective location in the second volumetric slice.

2. The system of claim 1, wherein the controller is configured to select a plurality of excitation signals applied to said plurality of coils such that magnitudes of first derivatives of the magnetic field along at least one dimension at said locations of the first and the second volumetric slices are substantially equal.

3. The system of claim 2, wherein said controller is configured to select said plurality of excitation signals applied to said plurality of coils such that the second derivatives of the magnetic fields along said one dimension at said locations of the first and the second volumetric slices are substantially zero.

4. The system of claim 1, further comprising at least one excitation source operating under control of said controller and in electrical communication with said coils for inducing a current therein.

5. The system of claim 4, wherein said excitation source comprises any of a voltage source and a current source.

6. The system of claim 4, wherein said controller is configured to transmit at least one signal to said at least one excitation source to induce different currents in said coils so as to generate said spatially-varying magnetic field.

7. The system of claim 6, wherein said spatially-varying magnetic field satisfies the following relations at said location of said first and second slices:

B<sub>ρ

=0</sub>(z_i)=B<sub>ρ

=0</sub>(z_k)

|B<sub>ρ

=0</sub>′

(z_i)|=G_z

B<sub>ρ

=0</sub>″

(z_i)=0

wherein B relates to a magnetic field, z relates to a position of the magnetic field gradient along a longitudinal axis of said enclosure, p relates to a position of the magnetic field gradient along a vertical axis of said enclosure, and G_z relates to a magnetic field gradient strength along the z axis.

8. The system of claim 1, wherein said at least one location in each of said first and second slices comprises two locations.

9. The system of claim 8, wherein said spatially-varying magnetic field satisfies the following relations:

B<sub>ρ

=ρ

1</sub>(z_i)=B<sub>ρ

=ρ

2</sub>(z_k)

|B<sub>ρ

=ρ

1</sub>′

(z_i)|=|B<sub>ρ

=ρ

2</sub>′

(z_k)|=G_z

wherein B relates to a magnetic field, z relates to a position of the magnetic field gradient along a longitudinal axis of said enclosure, ρ

relates to a position of the magnetic field gradient along a vertical axis of said enclosure, and G_z relates to a magnetic field gradient strength along the z axis.

10. The system of claim 1, wherein said at least one location in each slice is positioned on a longitudinal axis of said enclosure.

11. The system of claim 1, wherein said at least one location in each slice is positioned on an axis orthogonal to said longitudinal axis of the enclosure.

12. The system of claim 1, wherein said spatially-varying magnetic field exhibits a spatially periodic variation.

13. The system of claim 8, wherein a first of said two locations is positioned on the longitudinal axis of the enclosure and the other location is offset relative to the first location along an axis orthogonal to said longitudinal axis.

14. The system of claim 1, wherein said slices have a width along at least dimension in a range of about 0.5 mm to about 10 mm.

15. The system of claim 1, further comprising a set of cables disposed in electrical communication between the controller and the gradient coil array.

16. The system of claim 4, wherein said at least one excitation source comprises a plurality of excitation sources each in electrical communication with one of said coils.

17. The system of claim 16, further comprising a plurality of amplifiers each of which is electrical communication with one of said excitation sources and one of said coils for amplifying excitation signals applied to said coils.

18. The system of claim 1, further comprising at least one radiofrequency (RF) coil configured to apply at least one RF pulse to said volumetric slices.

19. The system of claim 17, further comprising a shield disposed in said enclosure to decouple an RF field generated by said at least one RF coil from the magnetic field generated by said coil array.

20. The system of claim 1, wherein said slices have a width along at least one dimension in a range of about 2 mm to about 20 cm.

21. The system of claim 18, wherein said at least one RF pulse is a single-band RF pulse.

22. The system of claim 18, wherein said at least one RF pulse is a multi-band RF pulse.

23. The system of claim 22, wherein said multi-band RF pulse has a bandwidth in a range of about 100 Hz to about 500 KHz.

24. The system of claim 21, wherein said single-band RF pulse has a bandwidth in a range of about 100 Hz to about 100 kHz.

25. The system of claim 18, wherein said RF pulse has a duration in a range 400 microseconds to 10 milliseconds.

26. The system of claim 6, wherein said controller is configured to select a plurality of excitation signals applied to said coils such that a magnetic field gradient associated with each coil has a gradient strength greater than about 80 mT/m/Amp.

27. The system of claim 1, further comprising a shell providing said enclosure, wherein said coils are coupled to said shell.

28. The system of claim 17, wherein said gradient coils are inductively coupled to one another.

29. The system of claim 28, wherein said controller is configured to apply at least one signal to said amplifiers so that voltages applied to the coils for generating desired currents in the said coils are according to the following relation:

30. A magnetic resonance imaging system, comprising:

a magnetic field generator having a gradient coil array, each coil of the array being configured to generate a magnetic field independent of a magnetic field generated by any of the other coils of the array;

a set of amplifiers, each of which being in electrical communication with one of said coils of the array for applying an excitation signal to said coil; and

a controller in electrical communication with said amplifiers and configured to apply a plurality of signals to said amplifiers such that the amplifiers apply a plurality of excitation signals to said coils for generating a magnetic field such at least first and second volumetric slices associated with at least two of said coils exhibit a magnetic field distribution characterized by substantially similar magnetic field gradients.

31. A method for generating a magnetic resonance image, comprising

applying a static magnetic field to an enclosure configured to receive a sample;

utilizing a plurality of independent coils to generate a gradient magnetic field in said enclosure, said gradient magnetic field characterized by spatial variations such that for at least first and second volumetric slices, a magnetic field magnitude associated with at least one location in the first volumetric slice is substantially equal to a magnetic field magnitude associated with a respective location in the second volumetric slice; and

applying an RF pulse signal to said first and second volumetric slices to excite a selected spin of said sample.

32. The method of claim 31, comprising providing an excitation signal to the plurality of independent coils to generate the magnetic field where the magnetic field magnitude associated with the at least one location in the first volumetric slice is substantially equal to the magnetic field magnitude associated with the respective location in the second volumetric slice.

33. The method of claim 31, wherein said gradient magnetic field characterized by spatial variations satisfies the following relations at said location of said first and second slices:

B<sub>ρ

=0</sub>(z_i)=B<sub>ρ

=0</sub>(z_k)

|B<sub>ρ

=0</sub>′

(z_i)|=G_z

B<sub>ρ

=0</sub>″

(z_i)=0

wherein B relates to a magnetic field, z relates to a position of the magnetic field gradient along a longitudinal axis of said enclosure, ρ

relates to a position of the magnetic field gradient along a vertical axis of said enclosure, and G_z relates to a magnetic field gradient strength along the z axis.

34. The method of claim 31, wherein said gradient magnetic field characterized by spatial variations satisfies the following relations:

B<sub>ρ

=ρ

1</sub>(z_i)=B<sub>ρ

=ρ

2</sub>(z_k)

|B<sub>ρ

=ρ

1</sub>′

(z_i)|=|B<sub>ρ

=ρ

2</sub>′

(z_k)|=G_z

wherein B relates to a magnetic field, z relates to a position of the magnetic field gradient along a longitudinal axis of said enclosure, ρ

relates to a position of the magnetic field gradient along a vertical axis of said enclosure, and G_z relates to a magnetic field gradient strength along the z axis.