Over-shoulder MRI magnet for human brain imaging

• US 5,416,415 A
• Filed: 08/05/1994
• Issued: 05/16/1995
• Est. Priority Date: 08/05/1994
• Status: Expired due to Fees

• Current Assignee: General Electric Company
• Original Assignee: General Electric Company
• Inventors: Laskaris, Evangelos T., Ogle, Michele D., Dorri, Bizhan
• Primary Examiner(s): ARANA, LOUIS M
• Application Number:
  US08/286,364
• Time in Patent Office: 284 Days
• Field of Search: 324/318, 324/319, 324/320, 324/322, 128/653.5, 335/299, 335/300
• US Class Current: 324/318
• CPC Class Codes: G01R 33/3806 Open magnet assemblies for improved access to the sample, e.g. C-type or U-type magnets
• CPC Class Codes: G01R 33/3815 with superconducting coils, e.g. power supply therefor
• CPC Class Codes: G01R 33/3875 using correction coil assemblies, e.g. active shimming

Abstract

A magnetic resonance imaging (MRI) magnet having an annularly cylindrical-shaped vacuum enclosure with a longitudinal axis, first and second longitudinal ends, a first larger diameter bore extending from the first towards the second longitudinal end, and a second smaller diameter bore extending from the second longitudinal end to the first bore. First and second superconductive coils are placed in the vacuum enclosure with the first coil generally circumferentially surrounding the first bore and the second coil circumferentially surrounding the second bore, wherein the radial distance of the radially innermost portion of the second coil from the axis is smaller than the radius of the first bore. The first longitudinal end of the vacuum enclosure fits over a patient'"'"'s shoulders with the patient'"'"'s head at least partially passing through the first bore and extending into the second bore for MRI brain imaging.

Claims

1. A magnetic resonance imaging magnet comprising:

a) a generally annularly cylindrical-shaped vacuum enclosure having;

(1) a generally longitudinally extending axis,

(2) first and second longitudinal ends,

(3) a first bore generally coaxially aligned with said axis, extending with a generally constant radius from said first longitudinal end towards said second longitudinal end, and spaced apart from said second longitudinal end, and

(4) a second bore generally coaxially aligned with said axis and extending with a generally constant radius from said second longitudinal end to said first bore, wherein said radius of said second bore is smaller than said radius of said first bore;

b) a plurality of longitudinally spaced-apart superconductive coils generally coaxially aligned with said axis and disposed within and spaced apart from said vacuum enclosure, said superconductive coils including a first coil and a second coil each carrying an electric current in generally the same direction, said first coil generally circumferentially surrounding said first bore and said second coil generally circumferentially surrounding said second bore, said second coil having a radially innermost portion, and wherein the radial distance of said radially innermost portion of said second coil from said axis is smaller than said radius of said first bore; and

c) a gradient coil disposed generally in said second bore.

2. The magnet of claim 1, also including a radio-frequency coil disposed generally in said second bore radially inward of said gradient coil.

3. The magnet of claim 1, wherein said first coil is disposed proximate said first longitudinal end, and said second coil is disposed proximate said second longitudinal end.

4. The magnet of claim 3, wherein said first and second coils each extend a longitudinal length and a radial length, wherein said longitudinal length of said first coil is greater than said radial length of said first coil, and wherein said longitudinal length of said second coil is greater than said radial length of said second coil.

5. The magnet of claim 4, wherein said second coil has a radially outermost portion, and wherein the radial distance of said radially outermost portion of said second coil from said axis is smaller than said radius of said first bore.

6. The magnet of claim 1, wherein said first and second bores are sized such that said first longitudinal end fits over a patient'"'"'s shoulders with the patient'"'"'s head at least partially passing through said first bore and extending into said second bore and such that said second bore has a diameter which is smaller than the width of the patient'"'"'s shoulders.

7. The magnet of claim 6, wherein said superconductive coils generate a magnetic resonance imaging volume in the region of the patient'"'"'s brain when the first longitudinal end is fitted over the patient'"'"'s shoulders with the patient'"'"'s head at least partially passing through said first bore and extending into said second bore.

8. The magnet of claim 7, wherein said imaging volume has a shape of generally a sphere having a center disposed in said second bore and generally on said axis.

9. The magnet of claim 8, wherein said center is disposed generally longitudinally equidistant from said first and second longitudinal ends.

10. The magnet of claim 1, also including a thermal shield disposed within and spaced apart from said vacuum enclosure, wherein said superconductive coils are disposed within and spaced apart from said thermal shield, and further including a cryocooler coldhead having a first stage and a second stage, wherein said second stage is colder than said first stage, wherein said second stage is in thermal contact with said superconductive coils, and wherein said first stage is in thermal contact with said thermal shield.

11. The magnet of claim 1, wherein said first bore has a diameter of generally 53 centimeters, said second bore has a diameter of generally 35 centimeters.