Magnetic resonance apparatus

Abstract: A magnetic resonance apparatus includes a magnet (10) which generates a uniform, static magnetic field through a central bore (12) along its longitudinal or z-axis. A gradient coil assembly, (44) creates gradients across the static magnetic field along orthogonal x, y, and z-axes. A radio frequency coil assembly (50, 80) transmits radio frequency signals into a subject and receives magnetic resonance signals from the subject. The radio frequency coil assembly includes a first biplanar coil assembly (50) for generating RF signals in an x-direction and a second biplanar coil coil assembly (80) for generating RF signals in a y-direction. The two biplanar coil assemblies each include a plurality of conductors (52, 82) along a first plane and a second plurality of conductors (54, 84) along a parallel second plane. The conductors extend parallel to the z-direction. Capacitors (56, 58, 94) are connected in series with each of the conductors in order to control the current flow such that the current flow in each plane is uniform across the plane. The ends of the electrical conductors are connected together (66, 88) such that the current flows are equal and opposite in the two planes. A radio frequency transmitter (136) transmits RF signals to the quadrature biplanar coil assembly. A digital receiver (140) receives and demodulates radio frequency signals from the radio frequency coil assembly. The demodulated signals are reconstructed (144) into an image representation for display on a video monitor (146).

Description: This invention relates to magnetic resonance apparatus. It finds particular application in conjunction with medical magnetic resonance imaging apparatus and will - be described with particular reference thereto. It is to be appreciated, however, that the invention will also find application in conjunction with other types of magnetic resonance imaging apparatus, magnetic resonance spectroscopy apparatus, and the like, In magnetic resonance imaging, a strong uniform static magnetic field B 0 is generated, often by a superconducting magnet. This static magnetic field B 0 polarizes the nuclear spin system of an object to be imaged. Superconducting magnets are commonly wound on a cylindrical body former mounted in an annular helium vessel surrounded by an annular vacuum vessel for thermal isolation. The superconducting magnet generates the static magnetic field, B 0 along its own longitudinal axis and the common longitudinal axis of the cylindrical bore of the vacuum vessel, commonly denoted as the "z-axis". To generate a magnetic resonance signal, the polarized spin system is first excited by a radio frequency magnetic field perpendicular to the z-axis. This RF field, denoted B 1 , is produced by an RF coil located inside the bore of the magnet and closely conforming thereto to maximise the space available to receive a patient. The RF magnetic field, which is changing in time in a sinusoidal waveform, is turned on and off to create short RF pulses to excite magnetization in the polarized object in the bore. More specifically, the RF pulses tip the magnetization out of alignment with the z-axis and causes its macroscopic magnetic moment vector to precess around the z-axis. The precessing magnetic moment, in turn, generates a radio frequency magnetic resonance signal that is received by the RF coil in a reception mode. To encode a sample spatially, magnetic field gradient pulses are applied after the RF excitation. The gradient magnetic fields are also applied in pulses to generate magnetic fields pointing in the z-axis, but changing in magnitude linearly in x, y, or z-directions. These gradient pulses are commonly denoted as G x , G y , and G z pulses, respectively. The gradient magnetic fields are generated by gradient magnetic field coils which are also located inside the magnet bore. Commonly, the gradient field coils are mounted on a cylindrical former between the RF coil and the bore. The RF and gradient field coils have a sufficient inner diameter to receive the entire body of a patient within their circular bore. These cylindrical whole body RF and gradient coils are routinely used to examine the patient's chest cavity and to examine individual organs therein, such as the heart. Examining individual organs or small regions of the chest cavity places the RF coils a significant distance from the region of interest. The most common whole body RF coils are saddle coils and birdcage coils. Both saddle and birdcage coils include electrical conductors which are mounted on a cylindrical dielectric former. Prior patents, such as EP-A-0 257 782, have also suggested mounting the RF coils on an elliptical former to follow the contour of a patient's body more accurately. Typical saddle and birdcage coils are described in "Radio Frequency Coils" by Hayes, Edelstein, and Schenck, NMR in Medicine: The Instrumentation and Clinical Applications, pages 142-165, (1985). Typical saddle coils includes four conductors extending in the z-direction, adjacent pairs of which are connected at their ends by connectors extending along the cylindrical former. In a birdcage coil, a plurality of conductors, e.g. eight, are spaced equidistant along the circular former and interconnected at their ends by a generally annular conductor extending along the surface of the circular former. For quadrature detection, a second coil rotated 90° from the first is provided. In order to accommodate the entire body of a patient, conventional birdcage and saddle coils are relatively large in diameter and length, e.g. 60 cm in diameter and about the same length. One of the problems with whole body birdcage and saddle coils is that the large size causes a loss of signal to noise ratio. The signal to noise ratio is generally proportional to coil sensitivity and to the coil filling factor. The coil sensitivity is generally inversely proportional to a power of the coil radius. Thus, the larger the diameter of the coil, the poorer its sensitivity and the lower its signal to noise ratio. The filling factor is the ratio of the magnetic energy stored in the region of interest in the patient and the total energy generated by the RF coil. When viewing only a small region of the patient, such as the heart, the magnetic energy stored in the heart region is relatively small compared to the total energy generated by the RF coil. Hence, the filling factor is low and the signal to noise ratio is also low. In order to improve the signal to noise ratio, when examining individual organs, the whole body RF coil is often used only as a transmitter coil. A separate receiver coil is positioned on the surface of the patient to detect the MR signals. The dedicated receiver coils are each designed for a specific organ and are sized and shaped accordingly. This increases its sensitivity to the organ and suppresses noise from other tissue in the patient. Thus, a large inventory of coils is required to image various internal organs of the body. Moreover, the sensitivity of surface coils falls off sharply away from the plane of the coil. This drop off in sensitivity toward the deeper regions of the subject causes non-uniformity in the images. Moreover, the sensitivity may drop off sufficiently fast that the examination of some deeper organs is impractical. The present invention provides magnetic resonance apparatus which overcomes the above-referenced problems. EP-A-0359374 discloses an r.f. antenna for use in a magnetic resonance method or apparatus comprising two sub-systems each comprising a relatively large area conductor means and a return current path conductor means which together act as a transmission line tuned to the frequency of the r.f. The two sub-systems are placed on opposite sides of a body under examination with the large area conductor means in facing relationship, and when used to apply an r.f. field to the body, are excited so that the r.f. currents in the two large area conductor means at any given instant are in opposite directions. The large area conductor means of each sub-system may be planar or convexly or concavely curved, and may comprise a single sheet of conducting material or an array of conducting strips in spaced relationship. The return path conductor means of each sub-system is suitably in the form of one or two strips or wires positioned behind the associated large area conductor means with respect to the other sub-system. Alternatively each return path conductor means may be surrounded by an electrical screen and positioned wherever is convenient. EP-A-0454251 discloses a coil system particularly for a wrist for use in an NMR imaging system comprising first and second planar U-shaped rectangular parallel coils. The extended legs of the U-shapes are interconnected to form third and fourth rectangular U-shaped planar coils oriented normal to the plane of the first and second coils to form a rectangular polyhedron coil configuration. A support arrangement for the coils receives a wrist to be imaged and assists in aligning the wrist relative to a body coil of the NMR system. Impedance matching and tuning circuits selectively apply and receive signals from the coils in quadrature. According to the invention there is provided a magnetic resonance apparatus comprising: an array of annular superconducting magnets for generating a substantially uniform, static magnetic field through a central bore thereof; a whole body gradient magnetic field coil assembly mounted around the central bore on a cylindrical dielectric former for selectively generating gradient magnetic fields in the bore; a whole body radio frequency coil mounted around said central bore adjacent the whole body gradient magnetic field coil assembly for generating radio frequency signals in and receiving radio frequency signals from an examination region within the bore; a further radio frequency coil assembly comprising a biplanar coil assembly insertable within and withdrawable from the bore and including a first planar coil section disposed along a first plane and a second planar coil section disposed along a second plane, the first and second planes being parallel to each other and being located on opposite sides of said examination region, and means for connecting the first and second coil sections such that current flows along the first planar coil section in a first direction parallel to a longitudinal axis of the bore and along the second planar coil section in a second direction opposite to the first direction parallel to the longitudinal axis of the bore; a radio frequency transmitter which is selectively connectable with the whole body radio frequency coil and the further radio frequency coil assembly; and a radio frequency receiver which is selectively connectable with the whole body radio frequency coil and the further radio frequency coil assembly for receiving and demodulating radio frequency magnetic resonance signals therefrom; characterised in that said first planar coil section of said insertable and withdrawable RF coil assembly includes a first plurality of electrical conductors of at least three parallel conductors; said second planar coil section of said insertable and withdrawable RF coil assembly includes a second plurality of electrical conductors of at least three parallel conductors; said insertable RF coil assembly further includes current adjusting means for adjusting the relative current flows through the first and second plurality of conductors such that the first plurality of conductors have a uniform first current flow therethrough and such that the second plurality of conductors have a uniform second current flow therethrough, the first and second current flows being equal to each other and in opposite directions; and said MR apparatus further includes further gradient coil assemblies which are mounted on parallel planar dielectric surfaces that extend parallel to said first and second planes and which are mounted on parallel planar dielectric surfaces on a third and a fourth plane that extend vertically to said first and second planes, said third and fourth planes being located on opposite sides of said examination region, said further gradient coil assemblies being insertable into and withdrawable from the bore together with the radio frequency coil assembly. One advantage of the present invention resides in its improved signal to noise ratio, filling factor, and RF coil efficiency. Another advantage of the present invention is that it facilitates high speed, fast scan imaging techniques. It is particularly suited for freeze frame images of the heart. Another advantage of the present invention is that the radio frequency coil assembly and the gradient coil assembly are insertable and with drawable within the bore of a conventional magnetic resonance apparatus. One magnetic resonance apparatus in accordance with the invention will now be described, by way of example, with reference to the accompanying drawings in which: Figure 1 is a vertical cross-sectional view of the apparatus; Figure 2 is a perspective view of RF and gradient coil assemblies of the apparatus with a top panel lifted to facilitate receipt of a patient into the assembly; Figure 3 is a perspective view of one RF coil assembly with a supporting dielectric material former shown in phantom for simplicity of illustration; Figure 4 is a diagrammatic illustration of another RF coil assembly which is mounted to the same dielectric former (shown in phantom) as the assembly of Figure 3 to provide quadrature detection; and Figure 5 illustrates a preferred coupling circuit for coupling the RF coil assemblies with an RF cable. With reference to Figure 1, the apparatus includes a plurality of superconducting main magnetic field coils 10 which generate a generally uniform static magnetic field along a longitudinal or z-axis of a central bore 12. The superconducting coils are mounted on a dielectric former 14 and received in an annular, helium vessel 16. The helium vessel is filled with liquid helium to maintain the superconducting magnets at their superconducting temperature. A main magnetic field shield coil assembly 18 generates a magnetic field which opposes the fields generated by the main magnets 10 in regions surrounding the superconducting magnets 10. The annular helium reservoir 16 is surrounded by a first cold shield 20 which is maintained at about 20 K. or less. A second cold shield assembly 22 is chilled to about 60 - 70 K. or less. An outer vacuum vessel 24 encases the cold shields to define a vacuum reservoir therearound. Layers of mylar insulation 26 are arranged between the vacuum vessel, the cold shields, and the helium reservoir. A circularly cylindrical, whole body gradient coil assembly 30 is mounted on a circularly cylindrical dielectric former and mounted within the bore 12. A circularly cylindrical, whole body RF coil 32 is mounted on a circularly cylindrical dielectric former and mounted within the bore 12. A circularly cylindrical dielectric cosmetic sleeve 34 shields the RF and gradient coils from view and protects them from damage. With continuing reference to Figure 1 and further reference to Figure 2, a biplanar gradient and RF coil assembly 40 is slidably received within the bore 12 as defined by the cosmetic sleeve 34. The planar RF and gradient coil assembly 40 includes a pair of dielectric guides 42 which conform to and are slidably received within the cosmetic sleeve 34. A biplanar gradient coil portion 44 includes a pair of y-gradient coils 46a, 46b mounted on planar dielectric formers which extend parallel to each other in an (x,y) plane (horizontal in FIGURE 1). A pair of x-gradient coils 48a, 48b are mounted in parallel (y,z) planes on dielectric formers that extend vertically (in FIGURE 1). The z-gradient coils extend annularly around the dielectric formers of the x and y-gradient coils, generally in (x,y) planes. Optionally, the z-gradient can be generated by the z-gradient coils of the circularly cylindrical gradient coil assembly 30 . Suitable x, y, and z-gradient coils are described in U.S. Patent No. 5,036,282. With continuing reference to FIGURES 1 and 2 and further reference to FIGURE 3, a first biplanar RF coil assembly 50 is provided inside the gradient coil assembly for generating and receiving RF fields in the y-direction. The first RF coil assembly includes a first conductor means 52, including a first plurality of conductors 52 1 , 52 2 , 52 3 , ..., 52 n , causes a substantially uniform first current flow extending in the z-direction along an upper (x,z) planar surface. A second conductor means 54, including a second plurality of conductors 54 1 , 54 2 , 54 3 , ..., 54 n , causes a substantially uniform second current flow extending along a second lower (x,z) plane parallel to the first upper plane. In the preferred embodiment, n equals 4. A first current adjusting means 56, including capacitors 56 1 , 56 2 , 56 3 , ..., 56 n , each mounted intermediately along a corresponding one of the first plurality of conductors, adjusts the current flow such that the current flow through each conductor at the selected radio frequency is equal. A second current adjusting means 58, including capacitors 58 1 , 58 2 , 58 3 , ..., 58 n each mounted intermediately along a corresponding one of the second plurality of conductors, adjusts the current flow such that the current flow through each conductor at the selected radio frequency is equal. The top z-direction conductors are connected together by a pair of edge connectors 60a, 60b. The bottom conductors are likewise connected together by a pair of edge connectors 62a, 62b. Top and bottom portion connectors 64a, 64b, 64c, 64d interconnect the top and bottom edge connectors 60, 62. Capacitors 66a, 66b, 66c, 66d divide the connector strips 64a, 64b, 64c, 64d, respectively. The connectors 64 and capacitors 66 are selected such that the current flows through the first conductor means 52 is equal in magnitude and opposite in direction to the current through the second conductor means 54. A coupling circuit 68 interconnects the RF coil assembly 50 with an RF cable 70. In the preferred embodiment, the conductors 52, 54, 60, 62, and 64 are constructed of copper foil mounted on sheets of dielectric material 72. With continuing reference to FIGURES 1 and 2 and further reference to FIGURE 4, a second RF coil 80 is provided for generating and receiving RF fields in the x-direction. The second RF coil 80 includes a first conductor means or set 82 of parallel electrical conductors extending parallel to each other and in the z-direction in a first (y,z) plane and a second conductor means or set 84 of conductors extending parallel to each other and in a z-direction in a second displayed (y,z) plane. First edge conductors 86a, 86b connect the ends of the first conductor set 82 and second edge conductors 88a, 88b connect the ends of the second conductor set 84. Conductors 90a, 90b, 90c, 90d interconnect the edge conductors 86a, 86b, and 88a, 88b. Capacitors 92 are mounted in the first conductors 82; capacitors 94 are connected in the second conductors 84; and capacitors 96a-96d are connected in conductors 90. The capacitors taken together are means that adjust the current flow through the third and fourth conductor sets such that at the selected RF frequency there is equal current flow through conductors 82 and equal current flow through conductors 84. The capacitors 96 are current adjusting means which are selected to insure that the current flow through conductors 82 and 84 is equal to each other, but in an opposite direction. The second RF coil assembly 80 is preferably constructed of copper foil mounted on opposite faces of the dielectric material 72 from the first RF coil assembly 50. With reference to FIGURE 1, if necessary, an RF shield coil 100 may be placed between the RF coils 50, 80 and the gradient coils 44. The RF shield coil 100 inhibits the RF current pulses applied to the RF coil assemblies from inducing gradient currents in the gradient coils. As illustrated in FIGURE 2, the top portion of the coil assembly 40 is preferably detachable. That is, appropriate connectors are provided in connectors 64, 86, and 88 of the RF coils to enable the top portion to be electrically coupled and decoupled. Similar electrical connectors are provided in the gradient coil assemblies and the shield coil assembly. In this manner, an upper portion 102 of the coil assembly 40 is physically removable and electrically detachable from a lower portion 104 of the coil assembly. This enables the patient to be positioned inside the coil assembly more easily. With reference to FIGURE 5, the coupling circuit 68 connects the cable 70 with the RF coil assemblies while matching the impedance of the coil assembly to 50 Ω when looking into the cable 70. The coupling circuit 68 also acts as a balun to couple the unbalanced cable to the balanced coil for better resonance stability. A pair of capacitors 112, 114 are connected across one of the capacitors 66 or 96. A pair of matched inductors 116, 118 are connected between the capacitors 112, 114. Three capacitors 120, 122, 124 are connected between each end of the coils and a ground sheath on the cable 70. The center or feed of the cable 70 is connected at the intersection of one of capacitors 112, 114 with the corresponding one of inductors 116, 118. With reference again to FIGURE 1, in operation, a gradient coil control means 130 controls an array of current amplifiers 132 to supply appropriate current pulses to one of gradient coils assemblies 44 and 30. More specifically, a switching means 134 selectively disconnects the current amplifiers 132 from the whole body gradient coils 30 when the insertable coil assembly 40 is inserted into the bore. A radio frequency transmitter 136 generates radio frequency signals which are conveyed by a switching means 138 to one of (1) the whole body radio frequency coils 32 and (2) the biplanar radio frequency coils 50, 80. The switching means 138 also connects a selected one of the radio frequency coils with a receiver 140. The receiver 140, preferably a digital receiver, demodulates the magnetic resonance signals emanating from the examination region and produces a series of digital views therefrom. An image reconstruction means 142 performs a two-dimensional inverse Fourier transform or other conventional image reconstruction technique to reconstruct the plurality of views into an image representation which is stored in an image memory 144. The image memory 144 is connected with a video monitor 146 which selectively displays man-readable images of the image representations in the memory 144.

Claims: A magnetic resonance apparatus comprising: an array of annular superconducting magnets (10) for generating a substantially uniform, static magnetic field through a central bore (12) thereof; a whole body gradient magnetic field coil assembly (30) mounted around the central bore (12) on a cylindrical dielectric former for selectively generating gradient magnetic fields in the bore (12); a whole body radio frequency coil (32) mounted around said central bore (12) adjacent the whole body gradient magnetic field coil assembly (30) for generating radio frequency signals in and receiving radio frequency signals from an examination region within the bore (12); a further radio frequency coil assembly (50, 80) comprising a biplanar coil assembly (50 or 80) insertable within and withdrawable from the bore (12) and including a first planar coil section (52 or 82) disposed along a first plane and a second planar coil section (54 or 84) disposed along a second plane, the first and second planes being parallel to each other and being located on opposite sides of said examination region, and means for connecting the first and second coil sections such that current flows along the first planar coil section (52 or 82) in a first direction parallel to a longitudinal axis of the bore and along the second planar coil section (54 or 84) in a second direction opposite to the first direction parallel to the longitudinal axis of the bore (12); a radio frequency transmitter (136) which is selectively connectable with the whole body radio frequency coil (32) and the further radio frequency coil assembly (50, 80); and a radio frequency receiver (140) which is selectively connectable with the whole body radio frequency coil (32) and the further radio frequency coil assembly (50, 80) for receiving and demodulating radio frequency magnetic resonance signals therefrom; characterised in that said first planar coil section of said insertable and withdrawable RF coil assembly includes a first plurality of electrical conductors (52) of at least three parallel conductors; said second planar coil section of said insertable and withdrawable RF coil assembly includes a second plurality of electrical conductors (54) of at least three parallel conductors; said insertable RF coil assembly further includes current adjusting means (56, 58) for adjusting the relative current flows through the first and second plurality of conductors (52, 54) such that the first plurality of conductors (52) have a uniform first current flow therethrough and such that the second plurality of conductors (54) have a uniform second current flow therethrough, the first and second current flows being equal to each other and in opposite directions; and said MR apparatus further includes further gradient coil assemblies (46, 48) which are mounted on parallel planar dielectric surfaces that extend parallel to said first and second planes and which are mounted on parallel planar dielectric surfaces on a third and a fourth plane that extend vertically to said first and second planes, said third and fourth planes being located on opposite sides of said examination region, said further gradient coil assemblies (46, 48) being insertable into and withdrawable from the bore (12) together with the radio frequency coil assembly (50, 80). An apparatus according to Claim 1, wherein said current adjusting means (56, 58) includes a plurality of capacitors (56, 58). An apparatus according to Claim 1 or 2, wherein the radio frequency coil assembly (50, 80) is a quadrature coil assembly and further includes: a third plurality of conductors (82) extending along the third plane; and a fourth plurality of conductors (84) extending along the fourth plane. An apparatus according to Claim 3 further including further current adjusting means (92, 94) for adjusting the relative current flows through the third and fourth plurality of conductors (82, 84) such that the third plurality of conductors (82) have a substantially uniform third current flow therethrough and the fourth plurality of conductors (84) have a substantially uniform fourth current flow therethrough, the third and fourth current flows being equal to each other and in opposite directions. An apparatus according to Claim 3 or 4, wherein the magnets (10) include annular magnets which generate the magnetic field such that an examination region is defined in said central bore (12) thereof with the magnetic field extending through the longitudinal axis of the central bore (12) and wherein the first, second, third, and fourth plurality of conductors (52, 54, 82, 84) extend parallel to the longitudinal axis of the central bore (12). An apparatus according to any one of Claims 3 to 5 further including a rectangularly cylindrical dielectric former on which the first, second, third, and fourth pluralities of conductors (52, 54, 82, 84) are mounted.

Inventors: MASTANDREA NICHOLAS J, PATRICK JOHN L, XUEMING ZOU, MASTANDREA, NICHOLAS J., PATRICK, JOHN L., XUEMING, ZOU
Applicants: MARCONI MEDICAL SYS INC, MARCONI MEDICAL SYSTEMS, INC.
Application year: 1993
Main classification: G01R33
IPC codes: G01R33