摘要:
A magnetic resonance imaging apparatus creates images by exciting magnetic resonance in selected nuclei disposed within an image region. Through the image region a main magnetic field (B0) is applied and transverse gradients are produced. At selected times a high power RF pulse is applied to the imaging region causing the selected nuclei to resonate. These magnetic resonance signals are detected by a receive coil (D1, D2) and converted into an image representation viewable on a display (24). Images are obtained by repeating the transmit and receive portions until enough image data is received to produce an image. The receive coil (D1, D2) includes first decoupler circuits (28) arranged about the coil. During the transmit portion of the cycle, the decoupler circuits sense the high power RF pulse and decouple the coil. High speed switching diodes or PIN diodes are excited by the transmit RF pulse to switch inductors (40) into the coil to decouple the receive coil. During a receive portion of a cycle in which the coil is not used, a DC bias is selectively applied to the coil forcing the diodes on, actively decoupling the coil. The DC bias also biases a diode switch (50, 50′) to short the input of a preamplifier element (48, 48′) providing protection.
摘要:
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.
摘要:
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.
摘要:
A magnetic resonance apparatus includes a multi-mode receiver assembly which facilitates operation in both a quadrature combination mode and phased array mode. The multi-mode receiver assembly includes a receiver coil assembly (30) comprising a first RF coil assembly (32) and a second RF coil assembly (34). A signal combining circuit, which includes a switch means, performs at least one of combining and splitting magnetic resonance signals received by the first and second RF coil assemblies (30, 32). The application of a DC bias potential to the switch means switches the multi-mode receiver assembly into the quadrature combination mode in which the received magnetic resonance signals are phase shifted and combined into a quadrature signal and an anti-quadrature signal. The absence of a DC bias potential to the switch means switches the multi-mode receiver assembly into the phased array mode in which the received magnetic resonance signals are phase shifted and passed individually to corresponding receivers. The multi-mode capability of the receiver assembly allows an operator to switch from a quadrature mode, which is provides faster reconstruction, to a phased array mode, which provides better image quality, within a single examination.
摘要:
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.
摘要:
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.
摘要:
An RF device (A) under test is connected with ports or jacks (14, 16) of an S-parameter test set (B). An RF input jack (18) is connected with an RF tracking signal output (20) of a spectrum analyzer (C) to receive an RF tracking signal. An output jack (22) is connected with a receiver input (24) of the spectrum analyzer. A mode control (30) internal to the test set is controlled by a programmable control sequence generator (34) of the spectrum analyzer. The mode control controls a switch array (32), preferably PIN diodes, which interconnect the RF input jack (18), the RF output jack (22), the two jacks (14, 16) that are connected to the device under test, and a 50 Ohm termination (54) in four modes to make reflection measurements and two transmission measurements. DC bias jacks (26, 28) are connected with a DC power for injecting a DC component into the RF signals applied to the device under test.
摘要:
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.
摘要:
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.
摘要:
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.