Classifications

• • H—ELECTRICITY
  • H01—ELECTRIC ELEMENTS
  • H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
  • H01F6/00—Superconducting magnets; Superconducting coils
• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
  • G01R33/00—Arrangements or instruments for measuring magnetic variables
  • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
  • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
  • G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
  • G01R33/381—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using electromagnets

Definitions

• the present invention generally relates to open magnets used in magnetic resonance imaging (MRI) systems and, more particularly, to such an open magnet with recessed field shaping coils.
• MRI magnetic resonance imaging
• an open magnet of a MRI system typically includes two spaced-apart coil assemblies which are substantially mirror images of one another.
• the space between the coil assemblies contains an imaging volume and allows for positioning of a patient in that volume and access by medical personnel for surgery or other medical procedures during magnetic resonance imaging.
• Each coil assembly typically has an annular-shaped main coil with a longitudinal axis, an annular-shaped shielding coil coaxially aligned along the longitudinal axis and spaced longitudinally outward and apart from the main coil, and a cylindrical-shaped magnetizable pole piece disposed about the longitudinal axis between the main and shielding coils.
• the magnetizable pole pieces of the coil assemblies enhance the strength of the magnetic field produced by the main coils. Further, by selectively configuring the inner surfaces of the pole pieces, the open magnet is magnetically shimmed so as to improve homogeneity of the magnetic field.
• the current practice is to form several annular steps on the inner surfaces of the pole pieces which protrude to different heights or distances into the space between the coil assemblies in order to control the magnetization distributions of the pole pieces and thus shape the magnetic field to create the homogeneous field volume in the space between the coil assemblies for MRI imaging.
• such magnetic field shaping annular steps occupy some of the space between the coil assemblies thus reducing the imaging volume of the MRI system and complicating the magnet ciyogenic structure design.
• the field shaping capacity of the step technique is limited and reduced as the main field increases since more load areas of the stepped pole pieces become magnetically saturated.
• An actively shielded open magnet useful for MRI applications comprises magnetized pole pieces, superconducting main and bucking coils, and recessed field shaping coils to provide a highly homogeneous, high field, open field of view for MR imaging with a wellcontained stray field.
• the magnetized pole pieces comprise a ferromagnetic material and have superconducting field-shaping coils situated in annular grooves formed in the pole face.
• the magnetized pole pieces with annular recessed field-shaping coils are placed inside a cryogenic helium vessel of the magnet.
• the uniform cryogenic temperature inside the cryogenic vessel avoids the field fluctuation that would otherwise result from temperature changes of the pole pieces.
• a pair of superconducting main coils generates the high magnet field in the imaging volume.
• the cold magnetized pole pieces do not fo ⁇ n a return path for the magnetic flux. Instead, the stray field is contained by the superconducting bucking coils.
• the recessed field shaping coils advantageously result in more usable space between the two coil assemblies of the open magnet, enable higher field and simplify the manufacturing of the pole pieces and the magnet cryostat structure.
• FIG. 1 is a schematic view of an open MRI magnet showing an imaging volume of the magnet.
• FIG. 2 is a schematic cross-sectional view of a prior art open magnet having field shaping annular steps formed on the inner surfaces of the pole pieces thereof.
• FIG. 3 is a plan view of one of the prior art pole pieces as seen along line 3-3 of FIG. 2.
• FIG. 4 is a schematic cross-sectional view of pole pieces in accordance with a preferred embodiment of the present invention for use in the open magnet of FIG. 2 with the pole pieces having field shaping coils inserted in annular grooves recessed in the inner surfaces of the pole pieces.
• FIG. 5 is a plan view of one of the pole pieces as seen along line 6—6 of FIG. 4.
• the prior art open magnet 10 includes a pair of spaced-apart coil assemblies 12 which are substantially mirror images of one another and form a space 14 therebetween that contains an imaging volume 16.
• Each coil assembly 12 typically has an annular-shaped main coil 18 with a longitudinal axis 20, an annular-shaped shielding, or bucking, coil 22 coaxially aligned along the longitudinal axis 20 and spaced longitudinally outward and apart from the main coil 18, and a cylindrical-shaped magnetizable pole piece 24 disposed about the longitudinal axis 20 between the main and shielding coils 18, 22.
• a support member 26 interconnects the two coil assemblies 12 and is made of a nonmagnetizable material, such as stainless steel.
• the main and shielding coils 18, 22 are typically superconductive and thus cooled to a temperature below their critical temperature to achieve and sustain superconductivity by cryogenic cooling thereof.
• the open magnet 10 also includes cryogenic vessels 28 containing a liquid cryogen, such as liquid helium, and surrounding the main and shielding coils 18, 22.
• the pole pieces 24 are disposed outside of and spaced apart from the cryogenic vessels 28 and are made of a ferromagnetic material, such as iron.
• the open magnet 10 is not limited to a superconductive magnet but rather can be a resistive magnet or a combination resistive and superconductive magnet.
• the main and shielding coils 18, 22 are not limited to superconductive coils but rather can be resistive or a combination of resistive and superconductive coils.
• the magnetizable pole pieces 24 of the spaced coil assemblies 12 enhance the strength of the magnetic field produced by the main coils 18.
• the pole pieces 24 comprise magnetizable bodies 30 made of ferromagnetic material and of desired configurations, such as generally cylindrical configurations, with inner surfaces 32 facing toward one another.
• the inner surfaces 32 of the pole pieces 24 have several annular steps 34, 36, 38 formed thereon which shape the magnetic field of the open magnet 10.
• a problem with pole pieces 24 is that they protrude into the space 14 between the coil assemblies 12 and thus reduce the usable volume of the space 14.
• the field shaping capacity of the steps technique decreases as the main magnet fields increase, thus tending to produce an unsatisfactory (i.e., non-homogeneous) imaging field for high field open MRI magnets.
• Another problem is the field fluctuation in the imaging volume due to temperature changes. As room temperature changes, the magnetization of the pole pieces changes, resulting in field fluctuation in the imaging volume and image quality issues.
• pole pieces 40 according to a preferred embodiment of the present invention for use in open magnet 10.
• the pole pieces 40 of FIG's. 4 and 5 have generally cylindrical-shaped magnetizable bodies 42 with respective outer surfaces 44 and inner surfaces 46 facing in a direction generally opposite that of the outer surfaces 44 such that the inner surfaces 46 face toward one another.
• pole pieces 40 of FIG's. 4 and 5 have at least one annular-shaped groove 48 recessed in inner surfaces 46, and an annular-shaped coil 50 , either superconductive
• a plurality of annular-shaped, concentrically-arranged, radially-spaced grooves 48 are recessed in inner surfaces 46, and a plurality of annular-shaped coils 50, either superconductive or resistive, are inserted into the respective grooves 48, so as to shape the magnetic field of the open magnet 10.
• Coils 50 can be pre-wound prior to their insertion into the grooves 48 and then retained in the grooves 48 by means generally indicated at 52, such as by mechanical fastening elements, an interference fit, or an epoxy bond with the magnetizable bodies 42.
• Pole pieces 24 are placed inside the cryogenic helium vessels 28, thus forming an integrated magnet assembly with the superconducting main coils 18 and bucking coils 22.
• Such assembly provides a complete electromagnetic design to satisfy all MRI requirements, including a highly uniform high-field volume for imaging and the containment of the stray field for siting.
• the advantages of the present invention include a larger unoccupied volume in the space 14 between the coil assemblies 12 and simpler manufacturing of the pole pieces 40 and the magnet cryostat structure.
• temperature induced field fluctuation is avoided by placing pole pieces 40 inside helium vessel 28 in order to operate at a constant liquid helium temperature.
• pole pieces 40, and the main and bucking coils 18, 22 are structurally connected to form an integrated cold magnet assembly, it is easier to position precisely all the electro-magnetic components, advantageously resulting in a highly uniform field in the image volume 16. Furthermore, axial corrections coils (not shown) can be easily co-wound with the field shaping coils to shim inhomogeneity due to manufacturing tolerances.

Landscapes

• Physics & Mathematics (AREA)
• Engineering & Computer Science (AREA)
• Power Engineering (AREA)
• Electromagnetism (AREA)
• Condensed Matter Physics & Semiconductors (AREA)
• General Physics & Mathematics (AREA)
• Magnetic Resonance Imaging Apparatus (AREA)

Priority Applications (2)

Applications Claiming Priority (4)

Publications (1)

Family

ID=27102644

Family Applications (1)

Country Status (4)

Families Citing this family (8)

Citations (6)

Family Cites Families (5)

• 2001
  • 2001-09-10 US US09/949,623 patent/US6504461B2/en not_active Expired - Lifetime
• 2002
  • 2002-03-25 JP JP2002575657A patent/JP3861058B2/ja not_active Expired - Fee Related
  • 2002-03-25 EP EP02733892A patent/EP1373918A1/en not_active Ceased
  • 2002-03-25 WO PCT/US2002/009272 patent/WO2002077658A1/en active Application Filing

Patent Citations (6)

Also Published As

Similar Documents

Legal Events