Abstract: The present invention is directed to a method of shimming a magnet assembly of an MR imaging system such that a desired B0 field strength may be created with minimal inhomogeneities therethrough. With this method, sufficient shimming of the magnet assembly may be achieved without requiring mechanical variations to the magnet assembly after the magnet assembly has been assembled. The invention analyzes variations from the desired B0 field and inhomogeneities at a number of target points along the magnet assembly or B0 field. A comparison is then made at each point to determine a shimming or weighting factor such that the desired overall B0 field strength and targeted field homogeneity is achieved. Active and/or passive shim elements may then be incorporated into the magnet assembly at each target point to achieve the desired overall field strength and minimum overall field homogeneity.

Abstract: The present invention relates to techniques for enlarging an opening, which accommodates a subject, in a superconducting magnet apparatus for use in MRI system, so as to prevent the subject from feeling claustrophobic, and for realizing low magnetic field leakage therefrom, and for reducing the weight thereof, and for realizing a large high magnetic field strength uniform magnetic field region. Static magnetic field generating sources of the superconducting magnet apparatus are constituted by two sets of superconducting coils, the respective sets of which are placed in such a manner as to face each other across a uniform magnetic field generating region. Each of the sets of superconducting coils consists of a main coil for feeding electric current in a specific direction, a bucking coil for feeding electric current in a direction opposite to the direction of the electric current flow passing through the main coil, and a coil for correcting magnetic homogeneity.

Abstract: Effect of vibration of a refrigerator on a superconducting coil is reduced to reduce disturbance in an image. A coolant tank for supplying a coolant to coil containers is provided separately from the coil containers, and the refrigerator is placed in the coolant tank, and a coolant circulation passage connects between the coolant tank and the coil containers.

Abstract: The subject invention pertains to a method and apparatus for Nuclear Magnetic Resonance (NMR) imaging. The subject method and apparatus are advantageous with respect to the use of RF coils for receiving signals in NMR scanners. The subject invention can utilize multiple coils to, for example, improve the signal to noise, increase the coverage area, and/or reduce the acquisition time. The use of multiple smaller surface or volume coils to receive NMR signals from the sample can increase the signal to noise ratio compared to a larger coil that has the same field of view and coverage area.

Abstract: The present invention provides a magnetic field generator for MRI in which, by simplifying the component parts of the pole pieces incorporated therein, the magnetic field generator for MRI can be manufactured at a lower cost without detracting from its magnetic characteristics. Specifically, the present invention provides an inclined magnetic field generation coil for use in a magnetic field generator for MRI, the coil comprising a plurality of magnetic field regulating holes (17), an electric conductor in coiled form, and a resin base.

Abstract: An apparatus is disclosed for generating a magnetic field of high field strength, spatial uniformity and minimal drift of magnetic field intensity over a temperature range of about 0° C. to 175° C. This apparatus may be used in a standard modular logging tool for direct downhole NMR measurements of various parameters of fluid samples of geologic formations near the walls of a borehole. In one embodiment, the apparatus is composed of two tubular permanent magnets made of different magnetic materials with different magnetic temperature coefficients to provide temperature compensation. The apparatus preferably also utilizes a pressure barrel that surrounds the magnets and provides a return path for magnetic flux lines, thereby increasing flux density within the measurement volume.

Abstract: A phase correction method for MR devices includes collecting non-phase encoded reference data, calculating phase coefficients, and then phase correcting the regular phase-encoded image dataset based on these coefficients. The phase correction method can be used for two dimensional or three dimensional FSE imaging and variants thereof. As the method is conducted after signal acquisition, it is considered a retrospective phase correction.

Abstract: In a shim tray, a gradient coil system and a magnetic resonance apparatus for the acceptance of the shim tray, the shim tray is sub-divided, in the direction of insertion into the gradient coil system or the magnetic apparatus into at least two sub-boxes that can be released from one another.

Abstract: A gradient coil system for a magnetic resonance apparatus has an area for receiving an examination subject and at least one gradient coil with an conductor arrangement for generating a magnetic gradient field having a main field component collinear to a basic magnetic field and at least one accompanying component that is perpendicular to the main field component, and at least one further conductor arrangement for feeding electrical current and which is fashioned and arranged for generating a non-homogeneous magnetic field such that the main field component, at least in the area, is approximately unaltered and such that the accompanying field component is reduced.

Abstract: An imaging system 10 is provided comprising an imaging magnet 16 having a magnet bore 18. A plurality of passive shims 26 is positioned within the magnet bore 18. A plurality of resistive shims 46 is also positioned within the magnet bore 18. A plurality of thermometers 28 is coupled thermally to a select number of the plurality of passive shims 26 and read a passive shim temperature 36. A controller 32 is in communication with the plurality of thermometers 28 and the plurality of resistive shims 46. The controller 32 includes logic adapted to adjust control currents 40 sent to each of the plurality of resistive shims 46 in response to the resistive shim temperatures 36 received from each of the thermometers 28 such that the strength of the magnetic field and its homogeneity is maintained.

Abstract: A radio frequency (RF) detector array and a MRI system are provided. The detector array comprises a plurality of conductive array elements being substantially parallel to a conductive ground plane, a plurality of capacitors, wherein at least one capacitor is shunted from each array element to the ground plane to adjust a corresponding electrical length of each conductive array element, and, wherein a combination of each respective array element, at least one corresponding capacitor and the ground plane forms a resonator that resonates at a selected frequency. The detector array further a decoupling interface, and a plurality of matching boxes for matching each decoupled conductive strip to a selected impedance. A MRI system is provided including a detector array as described herein to produce MR images of the object to be imaged.

Abstract: A superconducting magnet apparatus. By forming one or more holes in each of platelike ferromagnetic substances forming a magnetic shield for focusing the magnetic flux generated by superconducting coils, the flow of lines of magnetic flux is adjusted. Thereby, a static magnetic field in a measurement space is corrected. By disposing coupling tubes for supporting two cooling vessels housing superconducting coils on the rear side with respect to a central axis (Z axis) of the measurement space of the vertical direction, access to the subject is facilitated. In addition, the magnetic shield has an opening portion wider than the superconducting magnet on its side face. After the magnetic shield has been assembled, the superconducting magnet can be inserted from the opening portion.

Abstract: A magnetic field generator comprises a pair of plate yokes opposed to each other with a space in between. Each plate yoke has a main surface on which a permanent magnet is disposed. A shielding magnet is provided each at a forward portion on an open side and at a rearward portion, of another main surface in the plate yoke. A magnetic spacer is placed between the plate yoke and the shielding magnet. When assembling, a shielding magnet is mounted on a main surface of the spacer, and then another main surface of the spacer is placed on the main surface of the plate yoke. The shielding magnet is covered by a nonmagnetic cover member. A distance not smaller than 2 mm is provided between an outer surface of the cover member and a surface of the shielding magnet. The plate yoke is provided with nonmagnetic legs.

Abstract: The present invention is intended to provide a magnetic pole, a magnet apparatus, and a magnetic resonance imaging apparatus that the magnetic structure of the magnet apparatus for generating a uniform magnetic field is formed in a lower burst mode, and the profitability is increased, and at the same time, the uniformity of the magnetic field is improved.

Abstract: A method of manufacturing a magnetic resonance imaging (MRI) device is provided including providing at least one magnet positioned between a keeper device and a yoke, the keeper device being positioned at a pole region of the at least one magnet, positioning at least one pole device at the pole region of the at least one magnet, and removing the keeper device from the pole region to allow the at least one pole device to be positioned at the pole region of the at least one magnet.

Abstract: A detection coil for use in nuclear resonance magnetic (NMR) spectroscopy and a method of manufacture thereof. At least two film layers of material are deposited on an outer surface of a cylindrical tube of dielectric material. The layers are patterned to form a solenoid on the tube. At least one of the deposited materials is a conductor.

Abstract: For the purpose of efficiently correcting a quadratic term component of a static magnetic field, when an inhomogeneity error of a static magnetic field generated by a pair of magnets supported by yokes so that the magnets face each other across a space is to be corrected, a quadratic term component of the static magnetic field is corrected by a quadratic term component of a magnetic field generated by a pair of circular loop coils, and a zero-th order term component of the magnetic field from the pair of circular loop coils is compensated by a zero-th order term component of a magnetic field generated by coils wound around the yokes.

Abstract: An open magnetic resonance imaging (MRI) device is provided with at least one main coil for generating a magnetic field for imaging a volume, and at least one shaping coil. The at least one shaping coil is positioned relative to the at least one main coil to shape the magnetic field in the volume.

Abstract: Superconducting birdcage coil with low-pass and high-pass coil configurations are formed by using strips each with an elongated sapphire substrate with a layer of a high temperature superconductor (HTS) material grown in a wavy pattern over its entire length on one of its main surfaces. A low-pass coil is formed with a pair of ring elements made of an electrically conductive metal and a plurality of such strips arranged parallel to one another and interconnecting these ring elements at junctions which are spaced peripherally along each of the rings. At each of the junctions, the ring element and the HTS layer form a capacitance. A high-pass coil is formed by a plurality of such strips each with electrodes of the HTS material also grown at two end positions separated from each other on the other main surface of its sapphire substrates. These strips are arranged parallel to each other and sequentially around a central axis, each lying in a plane which includes the center axis.

Abstract: A radio frequency (RF) detector array assembly for use in a magnetic resonance imaging (MRI) system comprises at least one RF detector array, wherein the array has a plurality of RF detector elements for use in simultaneously acquiring radio frequency (RF) signals from the MRI system, and, a decoupling interface coupled to each of the plurality of detector elements for decoupling each detector element from the remaining detector elements. A method for decoupling radio frequency (RF) detector array elements in a magnetic resonance imaging (MRI) system is provided. The method comprises the steps of providing at least one RF detector array, wherein the detector array has a plurality of RF detector elements, and, providing a decoupling interface coupled to each of the plurality of detector elements for decoupling each detector element from the remaining detector elements.

Abstract: An antenna arrangement for a magnetic resonance device has a first antenna group, which includes at least one antenna element, and a second antenna group separated from the first antenna group, which likewise includes at least one antenna element. The antenna groups have respective cooperating coupler antenna parts that are fashioned and/or arranged such that, given a specific adjacent arrangement of the antenna groups with respect to one another, the coupler antenna parts form, by inductive coupling, a common boundary antenna element of the two antenna groups, which is inductively decoupled from the further antenna elements within the appertaining antenna groups. A corresponding method for coupling two antenna groups separated from one another employs such an antenna arrangement.

Abstract: An open magnetic structure comprising a conical magnetic structure that generates an NMR imaging field around the head of a patient, and a transition magnetic structure including a cylindrical magnet connected to the conical magnetic structures that extends the uniform field generated in the head magnet cavity to the shoulders of the patient. The overall geometry is designed to integrate the magnetic structure in a surgical suite with a minimum interference with surgical procedures, which typically involve surgery on the brain of the patient.

Abstract: In order to nullify the adverse effect of an external magnetic field on a static magnetic field generated in an MRI system, small-size coils are used to generate a compensation magnetic field. Thus, the component of the static magnetic field to be applied to a magnetic sensor is canceled. The magnetic sensor can therefore detect the external magnetic field highly precisely. A correction current proportional to the external magnetic field detected highly precisely is fed to BO correction coils. Eventually, the external magnetic field that adversely affects the static magnetic field is canceled.

Abstract: A magnetic field generator comprises a pair of plate yokes connected by a column yoke. The pair of plate yokes has a pair of opposed surfaces each provided with a permanent magnet including a plurality of neodymium magnets. In a method in which the neodymium magnets are demagnetized and adhesive is ground, the magnetic field generator is heated to 200° C.˜350° C. After the neodymium magnets are demagnetized, the adhesive is removed and the neodymium magnets are removed and collected from the magnetic field generator. In a method in which the adhesive is carbonized, the magnetic field generator is heated to 350° C.˜1000° C. After carbonizing the adhesive, the neodymium magnets are removed and collected. Surfaces of the collected neodymium magnets are polished and the neodymium magnets are reused. Further, the collected neodymium magnets are re-aged and reused.

Abstract: Asymmetric, compact non-superconducting magnets for magnetic resonance imaging are provided. The magnets have a homogeneous region (the “dsv”) which can be located close to one end of the magnet so as to reduce the sensation of claustrophobia experienced by patients undergoing MRI procedures. The magnets can be designed using a hybrid process in which current density analysis is performed to obtain an initial coil configuration which is then refined using non-linear optimization techniques to obtain a final coil configuration. The hybrid method can incorporate various constraints, including, the location and size of the dsv, the uniformity and strength of the B0 field, stray field strengths outside of the non-superconducting magnet, and field strengths within the magnet's coils. The hybrid technique can also be used to design compact symmetric non-superconducting magnets.

Abstract: An MRI scanner generates a temporally constant (B0) magnetic field through an examination region (10), as well as a surrounding fringe field. The fringe field tends to decrease in strength with distance from the examination region and includes a 5 Gauss line (70, 70′) and a 1 Gauss line (74). In a vertical field magnet, the 5 Gauss line can extend more than 3 or 4 meters above and below upper and lower pole assemblies (12, 14). By placing permanent magnets (70, 76) above and below the upper and lower pole assemblies, respectively, with an opposing magnetic polarity, the fringe field is shaped and controlled reducing a distance (d) of the 5 Gauss line above the scanner to about 2 meters and reducing an amount of ferrous material in a ferrous flux return path (24).

Abstract: In a magnet arrangement (M, D, P1, . . . , Pn) having a magnet coil system (M) with at least one current-carrying superconducting magnet coil, with an additional current-carrying coil system (D) which can be fed by an external current source to produce a magnetic field in the working volume which differs substantially from zero, and optionally with additional superconductingly closed current paths (P1, . . . , Pn), wherein the magnetic fields in the z direction, generated by the additional current paths (P1, . . . , Pn) due to currents induced during operation and the field of the additional current-carrying coil system (D) do not exceed 0.1 Tesla in the working volume, the additional coil system (D) is designed such that its field contribution to the working volume is determined taking into account the diamagnetism of the superconductor in the main coil system. This permits as large as possible an effective field efficiency of the additional coil system (D).

Abstract: A magnet for magnetic resonance imaging has a box-like ferromagnetic frame with vertical side walls, poles connected to the side walls and top and bottom walls forming flux return structures between the side walls. The frame has open front and rear sides defining patient entry openings, and has top and bottom openings in the top and bottom walls. A patient can be positioned in a vertical, horizontal or intermediate orientation within the frame. When the patient is in the vertical orientation, the patient can be raised or lowered so that parts of the patient's body protrude into the top or bottom openings, so as to align any part of the patient's body with the poles. The apparatus allows imaging of any part of the anatomy while the patient is in a standing position.

Abstract: A shield for controlling a magnetic field emanating from a magnetic in a magnetic medical treatment instrument has the form of a circular shaped band with opposite open ends and a center axis extending perpendicularly between the open ends. The magnet in the magnetic medical treatment instrument moves about an operating table having a surface upon which a patient being operated on by a physician reposes. The circular shaped shield surrounds the magnet and is spaced away from the magnet in a manner to allow the physician to enter the interior of the band and operate on the patient. The band has opposite first and second parallel planar portions. The top surface of the operating table and the first and second planar portions of the band are parallel to each other. The operating table has a length and a width, and the length of the operating table is parallel to the center axis of the band.

Abstract: In a magnetic resonance apparatus having a magnet arrangement which generates: a basic magnetic field in a horizontal direction, an imaging volume with a central region that is freely accessible in at least one horizontal direction substantially orthogonal to the basic magnetic field, upper and lower elements that are spaced apart in a vertical direction and between which the imaging volume is disposed, and a connector element that connects the upper and the lower elements, at least one gradient coil is provided which extends at least in regions of the upper element, the lower element and the connector element.

Abstract: Effect of vibration of a refrigerator on a superconducting coil is reduced to reduce disturbance in an image. A coolant tank for supplying a coolant to coil containers is provided separately from the coil containers, and the refrigerator is placed in the coolant tank, and a coolant circulation passage connects between the coolant tank and the coil containers.

Abstract: Disclosed herein is a method for assembling a magnetic field generator for a magnetic resonance imaging system. The method comprises: establishing an arrangement for a permanent magnet of a magnet assembly comprising a ferromagnetic yoke plate and a permanent magnet, wherein the arrangement includes a portion of a cavity formed from placement of a portion of a plurality of retainers attached at substantially the perimeter of the yoke plate. The method also includes populating the first portion of the cavity with a set of rails attached to the yoke plate and affixing a plurality of gliders to a plurality of magnet blocks and magnetizing the gliders and magnet blocks to form a plurality of block assemblies. Finally, the method includes sliding each block assembly of the plurality of block assemblies along a rail of the set of rails; initiating with an outermost rail and concluding with an innermost, securing each successively filled rail with a retainer.

Abstract: A magnetic resonance tomography apparatus, in particular an iron-guided or permanently magnetic, short or open magnetic resonance tomography apparatus, has thermally highly sensitive components and a temperature controller, formed by a foil heater which is provided with a control device and can be controlled in opposition to the internal dynamic heat sources.

Abstract: A superconducting magnetic resonance imaging magnet assembly is provided. The assembly includes an axial imaging bore to receive patients and a coil housing surrounding the axial bore. A main magnet coil assembly is disposed within the housing. The main magnet coil assembly includes a plurality of main magnet coils to produce a magnetic field. At least three pairs of superconductive coils are provided. In one aspect, each of the coils in at least one of the pairs comprises a superconductor wire carrying an electric current in a direction opposite to the direction of current carried by the coils of another of the superconductive pairs. The superconductor wire comprises a superconductor core and a stabilizer having a channel. The wire is wound so that the channel has a radially outward facing opening.

Abstract: The present invention is directed to a coil assembly capable of producing a flexible FOV for use with an MRI system. The coil assembly includes a gradient coil disposed about an imaging axis and a plurality of higher order gradient coils, or shim coils, positioned about the primary gradient coil such that the plurality of higher gradient order coils have a radius greater than the radius of the primary gradient coil. A change in the FOV is realized by modulating the current in the higher order gradient coils or shim coils.

Abstract: NMR apparatus for achieving construction of improved patient access desirably including a generally C-shaped yoke, and devices for reducing the field asymmetry caused by the C-shaped yoke.

Abstract: Signal recovery in functional magnetic resonance imaging (fMRI) is provided by generating a single excitation pulse and exciting a target region of a subject with the generated excitation pulse. A first image is obtained using a first partial k-space frame of the target region. A compensation pulse is generated and the target region excited with the compensation pulse. A second, compensated, image is obtained subsequent to the excitation by the compensation pulse using a second partial k-space frame of the target region. The first and second images are combined to form a combined image of the target region. The first and second obtaining steps are carried out sequentially during a single quadratic excitation pulse.

Abstract: A magnet device is provided with two static magnetic field generating sources 14a and 14b disposed so as to oppose each other while placing a person to be inspected therebetween, a vessel 15 containing the static magnetic field generating source 14a and a vessel 16 containing the static magnetic field generating source 14b, and the vessels 15 and 16 are disposed at positions asymmetric with respect to the person to be inspected. Thereby, a magnet device and an MRI device using the same which can extend a space above the person to be inspected on a bed while avoiding introduction of a large scale device which causes to increase the manufacturing cost thereof.

Abstract: Magnetic apparatus for MRI/MRT probes and methods for construction thereof are disclosed. One embodiment includes a pair of opposed magnet assemblies defining an open region therebetween, a transmitting RF coil having at least a portion thereof disposed within the open region, at least one receiving RF coil disposed within the open region and X, Y and Z gradient coils. At least one of the X, Y and Z gradient coils is disposed outside of the open region. Another embodiment of the apparatus includes a single magnet assembly having a first surface and a second surface opposing the first surface, a transmitting RF coil having at least a portion thereof opposing the first surface, at least one receiving RF coil and X, Y and Z gradient coils. At least one of the X, Y and Z gradient coils opposes the second surface. In another embodiment the magnet assembly generates a permanent z-gradient magnetic field and therefore includes only X and Y gradient coils, at least one of which opposes the second surface.

Abstract: An apparatus and method that tests an NMR system, including MRI scanners, by taking H-B measurements for the apparatus at any stage during the manufacture thereof, to thereby detect any defects of the NMR system at any point during the manufacture thereof.

Abstract: The invention relates to a process for manufacturing magnetic field generating devices in Nuclear Magnetic Resonance imaging apparatuses and to an image generating device according to said method. According to the invention, at least one layer of each pole piece is composed a plurality of adjacent or overlapping sheets, electrically insulated from each other. These sheets or foils may have slots, notches or apertures which cause bridges of a material having a lower electric conductivity to be formed between the areas separated by the notches and/or apertures. The bridges of material may be removed after sheet assembly by a cutting operation, particularly by laser cutting.

Abstract: The present invention relates to techniques for enlarging an opening, which accommodates a subject, in a superconducting magnet apparatus for use in MRI system, so as to prevent the subject from feeling claustrophobic, and for realizing low magnetic field leakage therefrom, and for reducing the weight thereof, and for realizing a large high magnetic field strength uniform magnetic field region. Static magnetic field generating sources of the superconducting magnet apparatus are constituted by two sets of superconducting coils, the respective sets of which are placed in such a manner as to face each other across a uniform magnetic field generating region. Each of the sets of superconducting coils consists of a main coil for feeding electric current in a specific direction, a bucking coil for feeding electric current in a direction opposite to the direction of the electric current flow passing through the main coil, and a coil for correcting magnetic homogeneity.

Abstract: An MRI magnet assembly includes a pair of cryostat enclosures each housing a superconducting primary shield coil. The primary shield coil is dimensioned with an outer diameter greater than that of the main coil and is axially spaced away from the magnet pole significantly farther than is the main coil. This design provides for increased accessibility and visibility within the gap defined between the cryostat enclosures, and allows for reduced amounts of superconducting material in the coils. A set of field shaping coils is mounted radially inwardly and closely axially adjacent to the magnet pole and axially between the main coil and the shield coil.

Abstract: A method for assembling a thermal shield suspension assembly including a plurality of straps, wherein the straps are arranged in an alternately cross hatch arrangement such that a plurality of first straps extend at a first orientation with regards to the cryogenic vessel and a plurality of second straps extend at a second orientation with regards to the cryogenic vessel, and wherein the first orientation is different from the second orientation and each second strap is disposed between the adjacent first strap is provided, the method comprising securing the first strap including the tensioning block to a thermal shield flange and a cryogenic vessel flange and securing the second strap to the thermal shield flange and the cryogenic vessel flange.

Abstract: An MRI static field magnet coil is symmetrical along the z-axis direction with a static field uniform region center substantially coincident with the center of the coil. However, the gradient field coil has asymmetrical density along the z-axis direction with the gradient field linear region center displaced from the center of the coil. One end of the gradient magnetic field coil in the z-axis direction forms the linear field region and the other end forms u current return portion. In order to make the gradient magnetic field linear region and the static magnetic field uniform region coincident with each other, the center of the gradient magnetic field coil is displaced from the center of the static field magnet. Thus, the gradient magnetic field coil can be extended from one end of the static field magnet until one end is aligned with one end of the static magnetic field uniform region. This permits the bore end of the gantry to be opened accordingly for greater patient comfort and/or medical access.

Abstract: The energy supply device for a signal pickup or signal generator for use in or at a magnetic resonance tomography device has a double layer capacitor of high capacitance and high power density. Charging of the double layer capacitor can occur via an integrated charging coil that derives charging energy from the high-frequency and/or gradient fields of the device.

Abstract: A thermal radiation shield 44 and a method for applying the same includes a first coating layer 46, a second coating layer 48, and a thermal shield layer 50. The first coating layer 46 is applied to a first surface. The second coating layer 48 is applied to a second service. The thermal shield layer 50 is positioned between the first coating layer 46 and the second coating layer 48 to form the thermal radiation shield 44. The thermal radiation shield 44 has non-interfering electrical properties.

Abstract: A magnetic resonance apparatus has a gradient coil system having at least one gradient coil for generating a magnetic gradient field and an electrically conductive structure that is arranged and fashioned such that the gradient field is damped in a region outside the imaging volume of the magnetic resonance apparatus, and such that a magnetic field of the structure caused by the gradient field via induction effects is similar in structure to the gradient field, at least within the imaging volume.

Abstract: The magnetic field in the working volume of an apparatus for measuring the magnetic resonance, in particular nuclear magnetic resonance, is homogenized in that shim plates are disposed at predetermined positions about the working volume and, in sum, do not generate a field in the center of the working volume. The summed effect of the shims is preferably inductively decoupled from the coil generating the magnetic field.

Abstract: A cylindrical magnet assembly for use in magnetic resonance imaging apparatus has a radially compact construction which eliminates prior manufacturing steps. Recesses are formed in insulation layers for receiving complimentary shaped bus bars. Because the bus bars are dimensioned to fit flush within the recesses, they do not add to the radial growth of the magnet assembly.