Abstract: Radio frequency (RF) shields used with magnetic resonance imaging (MRI) apparatus may experience gradient field induced eddy currents and RF field induced eddy currents. These eddy currents can cause the RF shield to heat up at an undesirable rate. RF shields are designed to have a desired degree of RF shielding and a desired heating attribute. Design goals for RF shields include gradient field transparency and RF field opacity, both of which can be influenced by eddy currents. Example methods identify a gradient field that will induce eddy currents and identify an RF field that will induce eddy currents. If a region on the RF shield is identified where the desired heating attribute will not be achieved, then a pattern of axial cuts and azimuthal cuts can be made in the RF shield to reduce gradient eddy current heating in the RF shield while maintaining desired RF shielding.

Abstract: A radio frequency coil is disclosed that is suitable for use with a magnetic resonance imaging apparatus. The radio frequency coil comprises first and second conductive loops connected electrically to each other by a plurality of conductive rungs. The conductive rungs each include a section that is relatively thin that will result in less attenuation to a radiation beam than other thicker sections of the rungs. Insulating regions are also disposed in areas of the radio frequency coil that are bound by adjacent rungs and the conductive loops. Portions of the insulating regions can be configured to provide a substantially similar amount of attenuation to the radiation beam as the relatively thin sections of the conductive rungs.

Abstract: Radio frequency (RF) shields used with magnetic resonance imaging (MRI) apparatus may experience gradient field induced eddy currents and RF field induced eddy currents. These eddy currents can cause the RF shield to heat up at an undesirable rate. RF shields are designed to have a desired degree of RF shielding and a desired heating attribute. Design goals for RF shields include gradient field transparency and RF field opacity, both of which can be influenced by eddy currents. Example methods identify a gradient field that will induce eddy currents and identify an RF field that will induce eddy currents. If a region on the RF shield is identified where the desired heating attribute will not be achieved, then a pattern of axial cuts and azimuthal cuts can be made in the RF shield to reduce gradient eddy current heating in the RF shield while maintaining desired RF shielding.

Abstract: The present invention relates to an element configuration within an RF coil for use for MRI. The invention provides for an inherently electromagnetically decoupled solenoid element pair for receiving radio frequency magnetic resonance signals within a vertical field MRI system. The elements of the solenoid element pair described herein are typically positioned in a coplanar, side-by-side position. The decoupling of the solenoid pair can be accomplished through numerous methods including but not limited to an overlapping between the elements of the solenoid pair, use of a capacitor shared between the elements of the solenoid pair, or the use of overlapped inductors between the elements of the solenoid pair.

Abstract: Mortgage fraud detection systems and methods are provided. A fraud detection system can generally comprise a database operator, a database manager, one or more users, and a database. Database components can be implemented as hardware, software, or a combination of both. A fraud detection method can generally comprise providing a database for maintaining a plurality of records. Data records can be continually received by a database in batchwise or single submission protocols. Records can be compared to determine whether they contain common data in one or more predetermined fields. If records contain common data in one or more predetermined fields, records can be examined for inconsistencies in one or more other data fields. Discovered inconsistencies and magnitudes of inconsistencies can be warning signs of fraud. Results of comparisons can be reported to system users to enable such users to investigate additional circumstances. Other embodiments and features are also claimed and described in the application.

Abstract: An MRI system includes a receive coil having a coil element. Two preamplifiers are used in relation to the coil element, thus placing a large impedance in series with the coil element. The optimal noise impedance of each preamplifier is matched to that of the other preamplifier.

Abstract: Mortgage fraud detection systems and methods are provided. A fraud detection system can generally comprise a database operator, a database manager, one or more users, and a database. Database components can be implemented as hardware, software, or a combination of both. A fraud detection method can generally comprise providing a database for maintaining a plurality of records. Data records can be continually received by a database in batchwise or single submission protocols. Records can be compared to determine whether they contain common data in one or more predetermined fields. If records contain common data in one or more predetermined fields, records can be examined for inconsistencies in one or more other data fields. Discovered inconsistencies and magnitudes of inconsistencies can be warning signs of fraud. Results of comparisons can be reported to system users to enable such users to investigate additional circumstances. Other embodiments and features are also claimed and described in the application.

Abstract: Mortgage fraud detection systems and methods are provided. A fraud detection system can generally comprise a database operator, a database manager, one or more users, and a database. Database components can be implemented as hardware, software, or a combination of both. A fraud detection method can generally comprise providing a database for maintaining a plurality of records. Data records can be continually received by a database in batchwise or single submission protocols. Records can be compared to determine whether they contain common data in one or more predetermined fields. If records contain common data in one or more predetermined fields, records can be examined for inconsistencies in one or more other data fields. Discovered inconsistencies and magnitudes of inconsistencies can be warning signs of fraud. Results of comparisons can be reported to system users to enable such users to investigate additional circumstances. Other embodiments and features are also claimed and described in the application.

Abstract: The present invention relates to an element configuration within an RF coil for use for MRI. The invention provides for an inherently electromagnetically decoupled solenoid element pair for receiving radio frequency magnetic resonance signals within a vertical field MRI system. The elements of the solenoid element pair described herein are typically positioned in a coplanar, side-by-side position. The decoupling of the solenoid pair can be accomplished through numerous methods including but not limited to an overlapping between the elements of the solenoid pair, use of a capacitor shared between the elements of the solenoid pair, or the use of overlapped inductors between the elements of the solenoid pair.

Abstract: A magnetic resonance imaging scanner (10) includes a main magnet (20) generating a spatially uniform main magnetic field at least over a field of view, a plurality of gradient coils (30) selectively generating magnetic field gradients at least over the field of view, and a radio frequency coil (32, 34) for performing at least one of exciting and detecting magnetic resonance at the selected resonance frequency in an imaging subject disposed in the field of view. A radio frequency trap (60, 60?) connected with the radio frequency coil (32, 34) includes helically grooved dielectric formers (62, 62) around which a coaxial cable (64) is wrapped. A plurality of electrically conductive tuning elements such as screws or rods (84, 90) are selectively inserted into the dielectric formers (62, 62) to tune the radio frequency trap (60, 60) to a selected resonance frequency by adjusting the inductance of the trap.

Abstract: A low profile radio frequency coil (32, 44, 441, 442, 443) for use in a magnetic resonance imaging system includes a low profile antenna (34, 102, 202, 302) that is configured to resonate at about a magnetic resonance frequency of the magnetic resonance imaging system. A generally planar inductor (110, 112, 210, 240, 310) is electrically connected or coupled with the low profile antenna. The generally planar inductor provides selected frequency filtering of a radio frequency signal received by or transmitted by the low profile antenna.

Abstract: A low profile radio frequency coil (32, 44, 441, 442, 443) for use in a magnetic resonance imaging system includes a low profile antenna (34, 102, 202, 302) that is configured to resonate at about a magnetic resonance frequency of the magnetic resonance imaging system. A generally planar inductor (110, 112, 210, 240, 310) is electrically connected or coupled with the low profile antenna. The generally planar inductor provides selected frequency filtering of a radio frequency signal received by or transmitted by the low profile antenna.

Abstract: A split-top RF coil is provided. The split-top RF coil includes a first housing (80) having a first RF coil portion (41) disposed therein and a second housing (84) having a second RF coil portion (42) disposed therein. A plurality of slides (100) disposed on at least one of the housings and a plurality of slide tracks (101) are disposed the housing opposite the slides for receiving the slides. The first and second housings are mechanically coupled via the slides and slide tracks. The RF coil also includes a plurality of electric connector pins (110) disposed on at least one of the housings and a plurality of pin receivers (111) disposed on the housing opposite the pins for receiving the conductor pins. Electric connections between the first and second coil RF coil portions are made via the pins and receivers.

Abstract: A magnetic resonance imaging apparatus includes a main magnet (12) for generating a main magnetic field in an examination region (14), a plurality of gradient coils (22) for setting up magnetic field gradients in the main field, an RF transmit coil for transmitting RF signals into the examination region to excite magnetic resonance in a subject disposed therein, and an RF receive coil (16) for receiving RF signals from the subject. The RF receive coil includes a first loop (101) and a second loop (102), the first and second loops being disposed substantially in a similar plane (x-z). Also included is a signal combiner (120) for combining the signals received by the first and second loops in quadrature.

Abstract: A split-top RF coil is provided. The split-top RF coil includes a first housing (80) having a first RF coil portion (41) disposed therein and a second housing (84) having a second RF coil portion (42) disposed therein. A plurality of slides (100) are disposed on at least one of the housings and a plurality of slide tracks (101) are disposed the housing opposite the slides for receiving the slides. The first and second housings are mechanically coupled via the slides and slide tracks. The RF coil also includes a plurality of electric connector pins (110) disposed on at least one of the housings and a plurality of pin receivers (111) disposed on the housing opposite the pins for receiving the conductor pins. Electric connections between the first and second coil RF coil portions are made via the pins and receivers.

Abstract: A birdcage coil (16) used in conjunction with a magnetic resonance imaging apparatus includes a first conductive loop (81, 581), a second conductive loop (82, 582), and a plurality of first conductor rungs (80, 580) disposed between the first and second conductive loops. A third conductor (83, 83?, 583) is coupled to the second conductive loop at resonance frequencies, such as by second conductor rungs (84, 84?, 584). The birdcage coil also includes switches (590) for switching the birdcage coil at least among: 1) an RF transmit mode to operate as an RF transmit coil; and 2) an RF receive mode to operate as an RF receive coil.

Abstract: A magnetic resonance imaging apparatus includes a main magnet (12) for generating a main magnetic field in an examination region (14), a plurality of gradient coils (22) for setting up magnetic field gradients in the main field, an RF transmit coil for transmitting RF signals into the examination region to excite magnetic resonance in a subject disposed therein, and an RF receive coil (16) for receiving RF signals from the subject. The RF receive coil includes a first loop (101) and a second loop (102), the first and second loops being disposed substantially in a similar plane (x-z). Also included is a signal combiner (120) for combining the signals received by the first and second loops in quadrature.

Abstract: A birdcage coil (16) used in conjunction with a magnetic resonance imaging apparatus includes a first conductive loop (81, 581), a second conductive loop (82, 582), and a plurality of first conductor rungs (80, 580) disposed between the first and second conductive loops. A third conductor (83, 83?, 583) is coupled to the second conductive loop at resonance frequencies, such as by second conductor rungs (84, 84?, 584). The birdcage coil also includes switches (590) for switching the birdcage coil at least among: 1) an RF transmit mode to operate as an RF transmit coil; and 2) an RF receive mode to operate as an RF receive coil.

Abstract: A multi-channel RF cable trap (70) blocks stray RF current from flowing on shield conductors (114) of coaxial RF cables (60) of a magnetic resonance apparatus. An inductor (116) is formed by a curved semi-rigid trough (80) constructed of an insulating material coated with an electrically conducting layer. Preferably, the inductor (116) and the cable follow an “S”-shaped path to facilitate good electromagnetic coupling therebetween. The RF cables (60) are laid in the trough (80) and the shield conductors inductively couple with the inductor (116). A capacitor (82) and optional trim capacitor (83) are connected across the the trough of the inductor (116) to form a resonant LC circuit tuned to the resonance frequency. The LC circuit inductively couples with the shield conductors (114) to present a high, signal attenuating impedance at the resonance frequency. The resonant circuit is preferably contained in an RF-shielding box (84) with removable lid.

Abstract: A multi-channel RF cable trap (70) blocks stray RF current from flowing on shield conductors (114) of coaxial RF cables (60) of a magnetic resonance apparatus. An inductor (116) is formed by a curved semi-rigid trough (80) constructed of an insulating material coated with an electrically conducting layer. Preferably, the inductor (116) and the cable follow an “S”-shaped path to facilitate good electromagnetic coupling therebetween. The RF cables (60) are laid in the trough (80) and the shield conductors inductively couple with the inductor (116). A capacitor (82) and optional trim capacitor (83) are connected across the the trough of the inductor (116) to form a resonant LC circuit tuned to the resonance frequency. The LC circuit inductively couples with the shield conductors (114) to present a high, signal attenuating impedance at the resonance frequency. The resonant circuit is preferably contained in an RF-shielding box (84) with removable lid.