摘要:
A multimode radio frequency coil (50.sub.1) receives resonance signals from a region of interest while allowing arbitrary placement of the coil. A peripheral electrical conductor (62) is divided into four symmetric segments by capacitors (76), (78), (80), (82). A pair of crossing conductors (64, 66) are connected between 90.degree. offset diagonally opposite portions of the peripheral loop (62). The crossing conductors include capacitors (68, 70) when not connected and include capacitors (68, 70, 86, 88) when connected at their midpoints. With this configuration, the coil supports orthogonal modes (72, 74) within the plane of the coil and, additionally, a third orthogonal mode (84) perpendicular to the plane of the coil. To image an extended region, a plurality of coils are overlapped to minimize mutual inductance relative to a first mode. An adjustable capacitor (90) across one of the coils adjusts mutual inductance relative to the second mode. A pair of half wavelength conductors (94, 96) are connected diagonally across the coils and are interconnected by an adjustable capacitor (98) for adjusting the third mode.
摘要:
An endocavity RF coil assembly for an MRI apparatus includes a reusable probe (30). The reusable probe has a hollow outer cover (60) having a closed distal end and (62) an open proximate end (64). The distal end (62) is formed to fit into a cavity of a subject being examined. An active RF coil element (72) is rigidly formed about an internal sleeve (70) which is located within the distal end (62) of the outer cover (60). A tuning and matching circuit is disposed within the outer cover (60) on the proximate end (64) side of the active RF coil element (72). The tuning and matching circuit is arranged on a printed circuit board (74) and attached to the active RF coil element (72). An over-molded form (90) is connected to the proximate end (64) of the outer cover (60). The over-molded form (90) is arranged such that it seals the proximate end (64) of the outer cover (60) closed.
摘要:
A vertical B.sub.0 temporally constant magnetic field is defined between a pair of pole faces (12, 14) that are interconnected by a C-shaped ferrous magnetic flux path (16). A quadrature radio frequency coil array (50) is disposed in a plane orthogonal to the B.sub.0 field. The coil array includes a plurality of coils (50.sub.1, 50.sub.2, . . . ) that are disposed in a partially overlapping relationship. Each of the coils has a peripheral loop (60), preferably defined by four linear legs (60.sub.1, 60.sub.2, 60.sub.3, 60.sub.4) of equal length which define a square. A pair of crossing elements (62.sub.1, 62.sub.2) are connected with mid-points of opposite sides of the square, the opposite mid-points are 180.degree. out-of-phase with each other at the magnetic resonance frequency and 90.degree. out-of-phase with neighboring mid-points of the square. The crossing elements cross but are not connected, in a symmetric relationship. Each of the crossing elements has a radio frequency pick-up (64.sub.1, 64.sub.2) associated therewith. The two radio frequency pick-ups receive 90.degree. offset, quadrature radio frequency signals from resonating nuclei within the B.sub.0 field.
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:
A resonance exciting coil (C) disposed in an image region in which a main magnetic field and transverse gradients have been produced. A flexible receiving coil (D) includes a flexible plastic sheet (40) on which an electrically continuous flexible foil strip (36) is adhered to receive signals from the resonating nuclei. The coil also includes components (24), mounted on the flexible plastic sheet (40), which may amplify the received signals before they are transmitted along a cable (22). A first soft material layer (44) is mounted on the flexible plastic sheet (40) for providing comfort to the patient. A flexible mechanical structure (50) on which two flexible receiving coils (F, G) adjusts an overlap between the coils (F, G) as the coils are flexed to adjust interaction properties of the coils (FIGS. 4 A, 4B). Pivotal rods (56) of a fixed length which connect two flexible coils (F, G) cause the spacing of the coils to vary in accordance to a flex applied to the coils to adjust the relative interactive properties with flexing (FIGS. 5 A, 5B). Flexible coils (D) in modular components provide identification points on each modular component which connect to similar identification points on other flexible coil modular components (FIGS. 9 A-9C).
摘要:
A method and apparatus for ferrous object and/or magnetic field detection are provided. Embodiments can improve magnetic resonance imaging (MRI) safety and increase the safety of MRI facilities. Embodiments can detect a given magnetic field strength around a MRI machine and alert users to the field's presence. In an embodiment, the magnetic field warning system can rely on a single badge that warns its user. In another embodiment, the badge can utilize an RFID system. The RFID system can turn the badge on when it enters the MRI room and off when it leaves the MRI room. In another embodiment, a badge with a rechargeable battery and charger can be utilized with or without an RFID tag. The subject badges or other detection devices can be worn by a person, located on or near a ferrous object, embedded in clothing, or located in other positions convenient to a user.
摘要:
A thin dielectric sheet (36) has a first or loop coil (30) defined on one surface thereof and a second or Helmholtz coil (32) defined on an obverse surface thereof. The dielectric sheet and associated coils may be laid flat (FIG. 3) or bent to match a selected curved surface of the subject (FIGS. 6-8). The first and second coils are arranged symmetrically about an axis or plane of symmetry (34). The first coil has an associated magnetic field along a y-axis and the second coil has an associated magnetic field along the x-axis. Circuits (40 and (42) tune the first and second magnetic resonance coils to a preselected magnetic resonance frequency. Magnetic resonance signals of the selected frequency received by one of the coils are phase shifted 90.degree. by a phase shifting circuit (50) and combined with the unphase shifted signals from the other coil by a combining circuit (52). The combined signals are amplified (54) and conveyed to electronic image processing circuitry (E) of a magnetic resonance scanner.
摘要:
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.
摘要:
Magnetic resonance is excited in selected portions of a subject disposed within a temporally uniform magnetic field of a magnetic resonance imaging system. A quadrature coil assembly (30) receives radio frequency magnetic resonance signals from the subject. Commonly, the quadrature coil fails to receive signals in true quadrature over the entire examination region. Resonance signals from a first coil (32) and a second, orthogonal coil (34) are received (40, 42), digitized (44, 46), and Fourier transformed (50, 52) into complex images. Each complex image includes an array or grid of vector data values having a magnitude and a direction or phase angle. If the quadrature coil was truly quadrature over the entire region of interest, the data values of both complex images would be a unit vectors. The vector of one image would be offset by 90.degree. from the vectors of the other. A phase correction board (54) sets the phase angle of the corresponding data values of the first and second complex images to a common vector direction or phase angle. A magnitude correction board (56) adjusts the magnitude of each corresponding data value of the first and second complex images. The phase angle and magnitude corrected complex data images are summed (58) and the real or magnitude image is stored in an image memory (62).
摘要:
A whole body RF antenna (22) surrounds an examination region (14). A localized coil array (40) having a plurality of coils (42a, 43b, . . . ) is mounted in the examination region. A switch array (48) selectively connects a selected one of the coils with an output (46). In a pilot or alignment scan, an imaging sequence is conducted using the whole body antenna (22) to generate an image of a portion of the surface coil array and the patient in the examination region. The coil array includes a marker (82) that is readily identifiable in the resultant image displayed on a video monitor (36). The location of slices for more detailed imaging are selected by positioning a cursor (64) on the video display. The position or coordinate system of the selected slices is aligned with the position or coordinate system of the coil array by positioning the cursor over the image of the marker and noting its position. Properties or parameters of each coil of the array are stored in a look up table (74). The parameters of each selected slice and imaging sequence are compared (72) with the properties in the look up table in order to determine an optimal one or more of the coils (42) for use in each imaging sequence. An imaging sequence along each of the slices is conducted utilizing the corresponding selected coils.