Abstract: An open magnetic resonance imaging (MRI) magnet having first and second spaced-apart superconductive coil assemblies each including a toroidal-shaped coil housing containing a superconductive main coil at least partially immersed in a cryogenic fluid such as liquid helium. A generally-non-permanently-magnetized ferromagnetic ring is associated with each coil assembly, being generally coaxially aligned with the associated coil assembly and being spaced radially inward and radially apart from the associated coil assembly's superconductive main coil. The ferromagnetic rings overcome the gross magnetic field distortions in the imaging volume of the superconductive main coils (created by the open space between the magnet's superconductive coil assemblies) to produce a magnetic field of high uniformity within the imaging volume.

Abstract: A method for actively and passively shimming a magnet having a magnetic field inhomogeneity, correction coils, and shim locations. The magnetic field is measured, and the inhomogeneity determined. The magnetic field created by a known current in each correction coil and by a known shim at each shim location is determined. Using linear programming, the optimum currents and shim sizes together are determined which minimizes the inhomogeneity plus the total currents used plus the total shim sizes used.

Abstract: A closed magnetic resonance imaging (MRI) magnet has a single superconductive coil assembly including a coil housing containing a cryogenic fluid dewar containing a pair of longitudinally-outermost impregnated superconductive main coils and at-least-one cryostable additional superconductive coil such as a pair of additional main coils, a pair of bucking coils, and/or a pair of shielding coils. An open MRI magnet has two spaced-apart superconductive coil assemblies and an imaging volume having a center. Each coil assembly has a cryostable superconductive main coil and an impregnated bucking coil with the impregnated bucking coil being the closest superconductive coil to the center of the imaging volume.

Abstract: A method for passively shimming a magnet having a magnetic field with an inhomogeneity and having N possible passive shim locations. The magnetic field is mapped. A function is defined related to the mapped field as affected by N shim variables of positive shim strength and M shim variables of negative shim strength. A computer optimization code is run which calculates the positive strengths of the N shim variables and the negative strengths of the M shim variables which minimizes the defined function. Positive strengths of passive shims are added to the magnet corresponding to the calculated positive strengths of the N shim variables and positive strengths of passive shims are removed from the magnet corresponding to the calculated negative strengths of the M shim variables.

Abstract: A superconductive magnet has a superconductive coil surrounded by a thermal shield surrounded by a vacuum enclosure. The thermal shield has one and preferably several flexible layers of thermally conductive material. A first flexible blanket of multi-layer thermal insulation surrounds the thermal shield within the vacuum enclosure, and a second such flexible blanket surrounds the superconductive coil within the thermal shield. A cryocooler coldhead has a first stage in thermal contact with each of the flexible layers of the thermal shield. At least most of the weight of the thermal shield is supported by the flexible blankets.

Abstract: A method for operating a superconductive magnet having a superconductor. The magnet is ramped to generally the design current. After that, the magnet is brought to an annealing temperature which is above the operating temperature and below the critical temperature. After that, the magnet is shimmed at a shimming temperature which is at least as cold as the annealing temperature. After that, the magnet is used, at the operating temperature, for a predetermined purpose, such as MRI imaging for medical diagnosis. Preferably, the superconductor has less than twenty-five superconductive filaments.

Abstract: A method for passively shimming an open magnet having a magnetic field with an inhomogeneity including an amount of positive 2, 0 Legendre polynomial harmonics. The magnetic field is mapped and the amount of positive 2, 0 Legendre polynomial harmonics of the mapped magnetic field is determined. An adjusted magnetic field is defined equal to the mapped magnetic field minus a nonzero portion of the determined amount of positive 2, 0 Legendre polynomial harmonics. A computer shim code is run which calculates adding shims to reduce the inhomogeneity of the adjusted magnetic field. Shims are added to the open magnet as calculated from the running of the computer shim code.

Abstract: A closed magnetic resonance imaging (MRI) magnet has a single superconductive coil assembly including a toroidal-shaped coil housing containing a pair of superconductive main coils and at least one additional superconductive main coil. A pair of generally-non-permanently-magnetized ferromagnetic rings is spaced radially inward and apart from the superconductive main coils. The ferromagnetic rings allow the design of a shorter MRI magnet because the ferromagnetic rings overcome the gross magnetic field distortions in the imaging volume of the magnet (created by removing some of the additional longitudinally-outermost superconductive main coils, otherwise used in the magnet, to make the magnet shorter) to produce a magnetic field of high uniformity within the imaging volume.

Abstract: An open magnetic resonance imaging (MRI) magnet having first and second spaced-apart superconductive coil assemblies each including a toroidal-shaped coil housing containing a superconductive main coil. A generally annular-shaped permanent magnet array is associated with each coil assembly, being generally coaxially aligned with the associated coil assembly and being spaced radially inward and radially apart from the associated coil assembly's superconductive main coil. The permanent magnet arrays overcome the gross magnetic field distortions in the imaging volume of the superconductive main coils (created by the open space between the magnet's superconductive coil assemblies) to produce a magnetic field of high uniformity within the imaging volume.

Abstract: A closed magnetic resonance imaging (MRI) magnet has a single superconductive coil assembly including a toroidal-shaped coil housing containing a pair of superconductive main coils and at least one additional superconductive main coil. A pair of generally annular-shaped permanent magnet arrays is spaced radially inward and apart from the superconductive main coils. The permanent magnet arrays allow the design of a shorter MRI magnet because the permanent magnet arrays overcome the gross magnetic field distortions in the imaging volume of the magnet (created by removing some of the additional longitudinally-outermost superconductive main coils, otherwise used in the magnet, to make the magnet shorter) to produce a magnetic field of high uniformity within the imaging volume.

Abstract: An open magnetic resonance imaging (MRI) magnet having first and second spaced-apart superconductive coil assemblies each including a toroidal-shaped coil housing containing a superconductive main coil in thermal contact with a cryogenic fluid contained in a dewar. Preferably, each main coil is located outside of and in solid-conduction thermal contact with its corresponding dewar (instead of inside the dewar). Preferably, a surrounding single (not double) thermal shield is cooled by liquid cryogen boil-off or by a cryocooler coldhead. All this allows the main coil to be located closer to the magnet's open space which reduces magnet cost by reducing the amount of coil needed for the same-strength magnetic field.

Abstract: A closed magnetic resonance imaging (MRI) magnet has a single superconductive coil assembly including a toroidal-shaped coil housing containing a pair of superconductive main coils. A pair of generally annular-shaped bucking coils, carrying electric current in a direction opposite to that of the superconductive main coils, is spaced radially inward and apart from the superconductive main coils. The bucking coils allow the design of a shorter MRI magnet because the bucking coils overcome the gross magnetic field distortions in the imaging volume of the magnet (created by removing some of the additional longitudinally-outermost superconductive main coils, otherwise used in the magnet, to make the magnet shorter) to produce a magnetic field of high uniformity within the imaging volume.

Abstract: A shielded and open magnetic resonance imaging (MRI) magnet having two spaced-apart, generally toroidal-shaped superconductive coil assemblies. Each coil assembly has a coil housing containing a generally annular-shaped superconductive main and a radially-outwardly spaced-apart shielding coil carrying electric currents in opposing directions. Preferably, supplemental shielding is provided with the addition of: a generally annular permanent magnet configuration internal to, or external of, the coil housings; a generally-non-permanently-magnetized external ferromagnetic shield having at least a portion positioned longitudinally between the coil housings, an external resistive coil; or combinations thereof.

Abstract: An open magnetic resonance imaging (MRI) magnet having longitudinally spaced-apart superconductive main coils surrounded by a dewar containing a cryogenic liquid (e.g., liquid helium) and boiled-off cryogenic gas (e.g., helium vapor). A condenser is in physical contact with the boiled-off vapor and is in thermal contact with a cold stage of a cryocooler coldhead so as to re-liquefy the vapor. This allows the coils to be surrounded by a single (not double) thermal shield which allows the coils structurally to be located closer to the magnet's open space which reduces magnet cost by reducing the amount of coil needed for the same-strength magnetic field.

Abstract: A magnet including spaced-apart first and second pole pieces with generally opposing first and second pole faces. The first pole face has an axis extending generally towards the second pole face and has a surface region which includes at least two frustoconical surfaces. The frustoconical surfaces are generally coaxially aligned about the axis, and radially-adjacent frustoconical surfaces abut each other. In a second embodiment, points on the surface region located an identical radial distance from the axis are also located a common axial distance along the axis, and a graph of axial distance along the axis versus radial distance from the axis for such points is a curve having a continuous slope with at least two sign reversals. Such contoured pole faces allow for a smoother magnetic field to better reduce axisymmetric magnetic field inhomogeneity.

Abstract: An open magnetic resonance imaging (MRI) magnet having first and second spaced-apart superconductive coil assemblies each including a toroidal-shaped coil housing containing a superconductive main coil. A generally annular-shaped resistive coil is associated with each coil assembly, being generally coaxially aligned with the associated coil assembly and being spaced radially inward and radially apart from the associated coil assembly's superconductive main coil. The resistive coils overcome the gross magnetic field distortions in the imaging volume of the superconductive main coils (created by the open space between the magnet's superconductive coil assemblies) to produce a magnetic field of high uniformity within the imaging volume.

Abstract: A superconductive magnet with magnetic shielding has an annularly-cylindrical-shaped housing whose first end wall and outer cylindrical wall are magnetizable (e.g., iron) walls and whose inner cylindrical wall is a non-magnetizable wall. At least one main superconductive coil is positioned within the housing and carries an electric current in a first (e.g., clockwise) direction. An annular first permanent magnet is positioned outside the housing longitudinally proximate the first end wall. The first permanent magnet has a number of equivalent ampere turns and has a magnetic field direction oriented parallel to the axis pointing towards the second end wall so that its magnetic field longitudinally pulls the stray magnetic field of the superconductive coil(s), which leaves the magnet's bore, inward to be captured by the iron first end wall.

Abstract: A superconductive magnet with magnetic shielding has an annularly-cylindrical-shaped housing whose first end wall and outer cylindrical wall are magnetizable (e.g., iron) walls and whose inner cylindrical wall is a non-magnetizable wall. At least one main superconductive coil is positioned within the housing and carries an electric current in a first (e.g., clockwise) direction. A first resistive (e.g., copper) deflection coil is positioned outside the housing radially proximate the outer cylindrical wall and longitudinally closer to the first end wall than to a midpoint located between the two end walls. The first deflection coil carries an electric current in an opposite direction to the first direction so that its magnetic field longitudinally pushes the stray magnetic field of the superconductive coil(s), which leaves the magnet's bore, inward to be captured by the iron first end wall.

Abstract: A magnet including spaced-apart first and second pole pieces with generally opposing first and second pole faces. The first pole face has an axis extending generally towards the second pole face and has a generally circular shim tray generally coaxially aligned with the axis and attached to the first pole face. The circular shim tray has shims each with a shape of generally a trapezoid when viewed facing the first pole face. The trapezoidal shaped shims may be arranged on the circumferences of imaginary concentric circles on the circular shim trays, with trapezoids on the same circumference having generally the same trapezoidal shape and with trapezoids on different circumferences having generally different trapezoidal shapes, to provide a smoother magnetic field to better reduce 3D (three-dimensional) magnetic field inhomogeneity.

Abstract: A cooling system for a superconductive magnet. A dewar, located outside the magnet, includes a vacuum jacket hermetically connected to the magnet's vacuum enclosure and includes liquid helium located within the vacuum jacket. A thermal busbar is located within and spaced apart from the hermetically connected vacuum jacket and vacuum enclosure. The thermal busbar has a first end located within the vacuum jacket and a second end located within the vacuum enclosure and in thermal contact with the magnet's superconductive coil. A cryocooler coldhead, located outside the vacuum enclosure, has a housing located outside the vacuum jacket and has a cold stage extending from the housing to inside the vacuum jacket to re-liquefy any helium boiled-off in cooling the magnet 10.