JP6334444B2 - Magnetic resonance imaging system - Google Patents

Description

  The present invention relates to a magnetic resonance imaging technique using a coil for transmitting and receiving electromagnetic waves.

  Magnetic Resonance Imaging (MRI) is a technique for visualizing organs and tissues in the body in detail using an electromagnetic wave of a static magnetic field and a radio frequency (RF). An MRI apparatus places a subject in a uniform static magnetic field generated by a magnet, irradiates the subject with an RF magnetic field, excites nuclear spins in the subject, and generates nuclear magnetic resonance signals that generate nuclear spins. Receive and construct an image of the subject. The irradiation of the RF magnetic field and the reception of the nuclear magnetic resonance signal are performed by an RF coil, and various shapes of transmission RF coils, reception RF coils, or transmission / reception RF coils suitable for the MRI apparatus are used.

  In a typical MRI apparatus, a tunnel type superconducting magnet is used, and a high magnetic field MRI apparatus of 1.5 Tesla or 3 Tesla is mainstream. On the other hand, an open MRI apparatus has a pair of permanent magnets or superconducting magnets and realizes high openness. The open MRI apparatus has an advantage that it can be applied to an infant, a claustrophobic subject, or an obese subject, which is difficult to apply with a tunnel type MRI apparatus.

  In the open MRI apparatus, an RF coil having a shape called a planar birdcage coil is used. A planar birdcage coil is disclosed in Patent Document 1 and the like. Patent Document 2 discloses a tunnel type MRI apparatus.

International Publication Number WO2008 / 108048 JP 2003-175015 A

  In the MRI apparatus, when the static magnetic field strength is increased, the signal-to-noise ratio is improved and the image quality of the MRI tends to be improved. On the other hand, safety management regarding RF electromagnetic wave irradiation is required more strictly. The International Electrotechnical Commission (IEC) defines safety standards for specific absorption rate (SAR), which is the amount of absorbed power per unit mass, by guidelines. Since the SAR is proportional to the square of the electric field strength, it is necessary to prevent the subject from being exposed to a strong electric field in order to satisfy the safety standard of the SAR. For example, Patent Document 2 discloses a tunnel-type RF coil in which electric field exposure is reduced in a high-magnetic-field tunnel-type MRI apparatus.

  On the other hand, with respect to the RF coil used in the open MRI apparatus, no disclosure has been made regarding a technique for reducing electric field exposure. This is because, in a conventional open MRI apparatus having a static magnetic field strength of 1 Tesla or less, the electric field exposure of the subject accompanying the RF electromagnetic wave irradiation is small, so the safety management of the SAR was not serious. Recently, however, an open MRI apparatus having a static magnetic field strength of 1 Tesla or higher has been developed, and it is considered that a technique for reducing electric field exposure is also required in the open MRI apparatus.

  Accordingly, an object of the present invention is to provide an MRI apparatus or the like that can reduce exposure of an electric field to a subject in order to solve the above-described problems.

  In order to achieve the above object, in the present invention, a static magnetic field generation system that generates a static magnetic field in a first direction, an RF transmission system that includes an RF transmission coil that generates an RF magnetic field, and a gradient that is superimposed on the static magnetic field A gradient magnetic field system for generating a magnetic field; and an RF reception system including an RF reception coil for detecting a nuclear magnetic resonance signal, wherein the RF transmission coil includes a first ring conductor having a first diameter, A second ring conductor having a second diameter smaller than the diameter, and a plurality of rung conductors connecting the first ring conductor and the second ring conductor, wherein the first ring conductor is more than the plurality of rung conductors. An MRI apparatus configured to be separated from an imaging space in a direction parallel to a first direction is provided.

  In order to achieve the above object, in the present invention, a static magnetic field generation system that generates a static magnetic field in the first direction, an RF transmission system that includes an RF transmission coil that generates an RF magnetic field, and a static magnetic field are superimposed. A gradient magnetic field system that generates a gradient magnetic field, and an RF reception system including an RF reception coil that detects a nuclear magnetic resonance signal, wherein the RF transmission coil includes a first ring conductor having a first diameter, A second ring conductor having a second diameter smaller than the first diameter, and a plurality of rung conductors connecting the first ring conductor and the second ring conductor, wherein the first ring conductor is a plurality of rungs. An MRI apparatus configured to be separated from an imaging space in a direction parallel to a first direction from the center of gravity of each conductor.

  According to the present invention, it is possible to realize an MRI apparatus capable of reducing the electric field strength in a planar birdcage coil.

It is an external view which shows an example of an open MRI apparatus. It is a schematic diagram which shows an example of a planar birdcage coil. It is a figure for demonstrating distribution of the electric field strength in the plane birdcage coil vicinity. It is a figure for demonstrating the distribution of the circumferential direction of the electric field strength in the vicinity of the ring conductor of the outer side of a planar birdcage coil. It is a block diagram which shows one structure of the MRI apparatus based on each Example. It is a figure which shows the structural example of the planar birdcage coil based on Example 1. FIG. It is a figure which shows the effect of the planar birdcage coil based on Example 1. FIG. It is a figure which shows the structural example and effect of a planar birdcage coil based on Example 2. FIG. It is a figure which shows the structural example and effect of a planar birdcage coil based on Example 3. FIG. It is a figure which shows the structural example of the planar birdcage coil based on Example 4. FIG. It is a figure which shows the structural example of the planar birdcage coil based on Example 5. FIG. It is a figure which shows the structural example of the planar birdcage coil based on Example 6. FIG. It is a figure which shows the structural example and effect of a planar birdcage coil based on Example 7. FIG. It is a figure which shows the structural example of the planar birdcage coil based on Example 8. FIG.

  Hereinafter, various embodiments of the present invention will be described. Prior to that, an example of the configuration of an open MRI apparatus and a planar birdcage coil will be described. FIG. 1 shows an external view of the open MRI apparatus. The apparatus shown in the figure is an MRI apparatus provided with a vertical static magnetic field generation system. A subject 1 laid on a table 2 is inserted into an imaging space in a bore of the static magnetic field generation system and imaged.

  FIG. 2 shows a schematic diagram of a typical planar birdcage coil. Hereinafter, in this specification, the center of the imaging space surrounded by a pair of opposed planar birdcage coils is defined as the coordinate origin, and the static magnetic field direction is defined as the z direction. 2A is a perspective view, FIG. 2B is a plan view seen from the direction of the static magnetic field (z direction), and FIG. 2C is a cross-sectional view taken along the xz plane.

  As shown in FIG. 2A, the pair of planar birdcage coils 60 are disposed so as to surround the imaging space so that the coil surfaces are orthogonal to the static magnetic field. As shown in FIG. 2B, each planar birdcage coil 60 includes a plurality of rung conductors in which an outer ring conductor 61 and an inner ring conductor 62 arranged concentrically are arranged in the radial direction. A structure connected by 63 is formed. Further, a plurality of capacitors 64 are connected in series to the outer ring conductor 61 and the inner ring conductor 62. As shown in FIGS. 2B and 2C, a diode 65 having a switching function is connected to the rung conductor 63 in series. The coupling between the RF transmission coil and the RF reception coil during transmission / reception of the RF magnetic field is suppressed by turning on / off the diode 65.

  In other words, the basic planar birdcage coil is composed of an outer ring conductor, an inner ring conductor, a rung conductor that radiates both, a capacitor connected in series to the ring conductor, and a rung conductor in series. It is a diode to be connected. Patent Document 1 discloses a planar birdcage coil in which a ring conductor having an intermediate size is arranged in addition to an outer ring conductor and an inner ring conductor to improve the uniformity of the RF magnetic field. .

  Next, problems to be solved by the present invention in the above-described planar birdcage coil will be described.

  FIG. 3 shows an example of an electric field intensity distribution in the vicinity of an RF coil used in an open MRI apparatus, that is, a pair of planar birdcage coils. FIG. 3A shows a cross-sectional view of the planar birdcage coil 60 in the xz plane. FIG. 3B is a graph plotting the electric field strength in a direction (z-axis direction) parallel to the static magnetic field 66 from the planar birdcage coil 60 and a few cm away from the origin. The horizontal axis of the graph of FIG. 3B represents the position in the x-axis direction, and the radius of the outer ring conductor 61 is a. According to this distribution, the electric field strength tends to be extremely high in the vicinity of x = ± a, that is, in the vicinity of the outer ring conductor 61. As described above, since the SAR is proportional to the square of the electric field strength, there is a concern that the SAR is locally increased when a part of the subject is disposed in the vicinity of the outer ring conductor 61.

  FIG. 4 shows an example of the distribution in the circumferential direction of the electric field strength in the vicinity of the outer ring conductor 61. 4A is a plan view of the planar birdcage coil 60 as in FIG. 2B. FIG. 4B is a schematic view in which the ring conductor 61 and the capacitor 64 outside the planar birdcage coil 60 are displayed in a one-dimensional manner. FIG. 4C shows the electric field intensity distribution 68 at a position parallel to the static magnetic field 66 (in the z-axis direction) and a few centimeters away from the origin, with the horizontal axis as the angle θ. Indicates. According to FIG. 4C, the electric field intensity distribution 68 in the vicinity of the outer ring conductor 61 tends to be extremely high in the vicinity of the capacitor 64. That is, in the planar birdcage coil 60, the electric field tends to be locally high in the vicinity of the outer ring conductor 61, particularly in the vicinity of the capacitor 64.

  Therefore, in the open MRI apparatus, when a part of the subject 1 is disposed in the vicinity of the outer ring conductor 61, particularly in the vicinity of the capacitor 64, there is a concern that the SAR is locally increased. Various embodiments of the RF coil for an open MRI apparatus and the MRI apparatus that can solve the problem to be solved by the present invention, that is, can reduce the exposure of the electric field to the subject, will be described.

  First, a configuration example of an open MRI apparatus common to the embodiments will be described with reference to FIG. The appearance of this open MRI apparatus is as shown in FIG. FIG. 5 is a block diagram showing an example of the overall configuration of the MRI apparatus. This MRI apparatus obtains a tomographic image of a subject using each magnetic resonance (Nuclear Magnetic Resonance: NMR) phenomenon. As shown in FIG. 5, the MRI apparatus includes a static magnetic field generation system 10 and a gradient magnetic field coil. 21 and a gradient magnetic field power source 22, a gradient magnetic field generation system, an RF oscillator 31, a modulator 32, a transmission system consisting of an RF amplifier RF transmission coil, an RF reception coil 41, a signal amplifier 42, a phase detector 43, and an A / D. A receiving system including a converter 44, a signal processing system 50, a sequencer 3, and a central processing unit (CPU) 4 are provided.

  If the static magnetic field generation system 10 is a vertical magnetic field method shown in FIG. 1, the body is substantially a body if it is a horizontal magnetic field method in a direction substantially perpendicular to the body axis in the space around the subject 1. A uniform static magnetic field is generated in the axial direction, and a permanent magnet type, normal conducting type or superconducting type static magnetic field generating source is arranged around the subject 1.

  The gradient magnetic field generation system includes a gradient magnetic field coil 21 that generates gradient magnetic fields in the three-axis directions of X, Y, and Z, which are coordinate systems (stationary coordinate systems) of the MRI apparatus, and a gradient magnetic field power source that drives each gradient magnetic field coil. 22, and the gradient magnetic field power supply 22 of each coil is driven in accordance with a command from the sequencer 3 to apply gradient magnetic fields Gx, Gy, and Gz in the three axial directions of X, Y, and Z. At the time of imaging, a slice direction gradient magnetic field (Gs) is applied in a direction orthogonal to the slice plane (imaging cross section) to set a slice plane for the subject 1, and the remainder that is substantially orthogonal to the slice plane and orthogonal to each other The phase encode direction gradient magnetic field (Gp) and the frequency encode direction gradient magnetic field (Gf) are applied in the two directions, and position information in each direction is encoded in the echo signal.

  The sequencer 3 is a control means that repeatedly applies an RF magnetic field and a gradient magnetic field in a predetermined pulse sequence. The sequencer 3 operates under the control of the CPU 4 and sends various commands necessary for collecting tomographic image data of the subject 1 to the transmission system. Send to magnetic field generation system and reception system.

  The transmission system irradiates the subject 1 with an RF magnetic field in order to cause nuclear magnetic resonance to the nuclear spins of the atoms constituting the living tissue of the subject 1, and the sequencer 3 receives the RF signal output from the RF oscillator 31. The amplitude is modulated by the modulator 32 at a timing in accordance with a command from the signal, and the amplitude-modulated RF signal is amplified by the RF amplifier 33 and then supplied to the RF transmission coil 34 disposed in the vicinity of the subject 1. A magnetic field is applied to the subject 1.

  The receiving system detects an echo signal (NMR signal) emitted by nuclear magnetic resonance of nuclear spins of atoms constituting the biological tissue of the subject 1. In the reception system, the NMR signal of the response of the subject 1 induced by the RF magnetic field irradiated from the RF transmission coil 34 of the transmission system is detected by the RF reception coil 41 arranged close to the subject 1, and the signal After being amplified by the amplifier 42, it is divided into two orthogonal signals by the phase detector 43 at a timing according to a command from the sequencer 3, and each signal is converted into a digital signal by the A / D converter 44, and the signal processing system 50 Sent to.

  The signal processing system 50 performs various data processing and display and storage of processing results. The signal processing system 50 includes an external storage device such as a magnetic disk 51 and an optical disk 52, a display 53 including a CRT, and an operation unit 54. When data from the receiving system is input to the CPU 4, the CPU 4 executes processing such as signal processing and image reconstruction, displays the tomographic image of the subject 1 as a result on the display 53, and also stores the data in the external storage device. Recording on the magnetic disk 51 or the like.

  The operation unit 54 is used to input various control information of the MRI apparatus and control information of processing performed in the signal processing system 50, and includes, for example, a mouse and a keyboard. The operation unit 50 is disposed in the vicinity of the display 53, and the operator controls various processes of the MRI apparatus interactively through the operation unit 54 while looking at the display 53.

  In FIG. 5, the RF transmission coil 34 and the gradient magnetic field coil 21 of the transmission system face the subject 1 in the static magnetic field space of the static magnetic field generation system 10 into which the subject 1 is inserted if the vertical magnetic field method is used. And if it is a horizontal magnetic field system, it will install so that the subject 1 may be surrounded. Further, the RF receiving coil 41 of the receiving system is installed so as to face or surround the subject 1.

  At present, the radionuclide to be imaged by the MRI apparatus is a hydrogen nucleus (proton) which is a main constituent material of the subject as widely used clinically. Information on the spatial distribution of the proton density and the spatial distribution of the relaxation time of the excited state is imaged, thereby imaging the form or function of the human head, abdomen, limbs, etc. two-dimensionally or three-dimensionally.

  Example 1 is a static magnetic field generation system that generates a static magnetic field in a first direction, an RF transmission system that includes an RF transmission coil that generates an RF magnetic field, and a gradient magnetic field system that generates a gradient magnetic field superimposed on the static magnetic field. An RF receiving system including an RF receiving coil for detecting a nuclear magnetic resonance signal, wherein the RF transmitting coil has a first ring conductor having a first diameter and a second diameter smaller than the first diameter. A second ring conductor having a plurality of rung conductors connecting the first ring conductor and the second ring conductor, wherein the first ring conductor is parallel to the first direction from the plurality of rung conductors. 1 is an embodiment of a magnetic resonance imaging apparatus having a configuration separated from an imaging space, and a planar birdcage coil which is an RF transmission coil thereof. In the case of the vertical magnetic field method shown in FIG. 1, the first direction, which is the direction of the static magnetic field, is the vertical direction.

  FIG. 6 is a diagram illustrating a configuration example of the planar birdcage coil according to the first embodiment. 6A is a plan view of the planar birdcage coil 70 of this embodiment, and FIG. 6B is a cross-sectional view in the xz plane. Here, the space between the pair of planar birdcage coils is the imaging space, the center of this imaging space is defined as the origin, and the direction of the static magnetic field is defined as the z-axis direction. In the conventional planar birdcage coil shown in FIG. 2, the outer ring conductor 61, the inner ring conductor 62, the rung conductor 63, the capacitor 64, and the diode 65 are arranged on the same plane, whereas FIG. In the planar birdcage coil of this embodiment shown in FIG. 1, the outer ring conductor 71 as the first ring conductor is separated from the rung conductor 73 from the plane parallel to the coil plane through the xy plane, that is, the center of the imaging space. ing. In other words, the first ring conductor is separated from the imaging space in a direction parallel to the first direction, which is the direction of the static magnetic field, from the plurality of rung conductors. For example, when the imaging space of the MRI apparatus is 45 to 50 cm, it is desirable that the distance is about 1 to 5 cm.

  Further, the outer ring conductor 71 and the rung conductor 63 are connected by a diode 65. That is, the outer ring conductor, which is the first ring conductor, is connected to each of the plurality of rung conductors via diodes. Here, of the two terminals of each diode 75, the first terminal is the outer ring conductor. It is desirable that the second terminal is connected to the end of the rung conductor 73 and connected to the ring conductor 71. That is, it is desirable that the diode 75 be disposed at a level difference between the ring conductor 71 and the rung conductor 73 outside the planar birdcage coil. By disposing the diode 75 at the level difference, the heat generating diode 75 can be separated from the imaging space, that is, the subject, and safety can be improved.

  FIG. 7 is a diagram showing a configuration example and effects of the planar birdcage coil in the present embodiment. FIG. 7A is a cross-sectional view in the xz plane of the planar birdcage coil 70 of the present embodiment, similar to FIG. 6B. The dotted line plot in FIG. 7B shows the electric field strength distribution 67 of the conventional planar birdcage coil 60 shown in FIG. The solid line plot in FIG. 7 (b) is the same position as in FIG. 3 (b), that is, the direction parallel to the static magnetic field 76 (z-axis direction) from the rung conductor 73 of the planar birdcage coil 70 and the number on the origin side. An electric field intensity distribution 77 at a position separated by cm is shown. The horizontal axis of the graph of FIG. 7B represents the position in the x-axis direction, and the radius of the outer ring conductor 71 is a. According to this distribution, the electric field strength distribution 77 of the planar birdcage coil 70 of this embodiment is x = ± a, that is, in the vicinity of the outer ring conductor, compared to the electric field strength distribution 67 of the conventional planar birdcage coil 60. Remarkably low. Therefore, according to the planar birdcage coil 70 of the present embodiment, it is possible to provide an MRI apparatus and an RF transmission coil for the MRI apparatus that are less exposed to electric field than before and that are superior in terms of safety.

  In the second embodiment, in addition to the configuration of the first embodiment, the MRI has a configuration in which the inner ring conductor, which is the second ring conductor, is separated from the imaging space in a direction parallel to the first direction from the plurality of rung conductors. 1 is an example of a device and its RF transmit coil.

  FIG. 8 is a diagram illustrating a configuration example and effects of the planar birdcage coil according to the second embodiment. FIG. 8A shows a cross-sectional view of the planar birdcage coil 80 of the present embodiment in the xz plane. Here, in the planar birdcage coil 70 shown in FIG. 7A of the first embodiment, only the outer ring conductor 71 that is the first ring conductor is more in the xy plane, that is, in the imaging space than the rung conductor 73. In the planar birdcage coil 80 shown in FIG. 8A of the present embodiment, the outer ring conductor 81 and the second ring conductor are separated from the plane passing through the center and parallel to the coil surface. The inner ring conductor 82 is further away from the plane parallel to the coil surface through the center of the imaging space than the rung conductor 83. Further, the outer ring conductor 81 and the rung conductor 83 are connected by a diode 85. Although FIG. 8 shows an example in which the outer ring conductor 81 and the rung conductor 83 are connected by the diode 85, the inner ring conductor 82 and the rung conductor 83 may be connected by the diode 85.

  Here, of the two terminals of each diode 85, the first terminal is connected to the outer ring conductor 81 or the inner ring conductor 82, and the second terminal is connected to the end of the rung conductor 83. desirable. That is, it is desirable that the diode 85 be disposed at a level difference between the outer ring conductor 81 or the inner ring conductor 82 and the rung conductor 83 of the planar birdcage coil. By disposing the diode 85 at the position of the step, the heat generating diode 85 can be separated from the imaging space, that is, the subject, and safety can be improved.

  The dotted line plot in FIG. 8B shows the electric field strength distribution 67 of the conventional planar birdcage coil 60 shown in FIG. The solid line plot in FIG. 8B is the same position as in FIG. 3B, that is, a direction parallel to the static magnetic field 86 (z-axis direction) from the rung conductor 83 of the planar birdcage coil 80 and a few centimeters away from the origin. The electric field strength distribution 87 at the different positions is shown. 8B represents the position in the x-axis direction, and the radius of the outer ring conductor 81 is a.

  According to this distribution, the electric field strength distribution 87 of the planar birdcage coil 80 of this embodiment is only x = ± a, that is, in the vicinity of the outer ring conductor, as compared with the electric field strength distribution 67 of the conventional planar birdcage coil 60. In addition, x = 0, that is, extremely low in the vicinity of the inner ring conductor. Therefore, according to the planar birdcage coil 80 of the present embodiment, it is possible to provide an MRI apparatus and an RF transmitter coil for the MRI apparatus that are less exposed to electric field than those of the prior art and that are superior in safety.

  In the third embodiment, the first ring conductor includes a plurality of first capacitors connected in series, and the plurality of first capacitors are imaging space in a direction parallel to the first direction from the first ring conductor. 1 is an embodiment of an MRI apparatus having a configuration separated from the RF transmitter coil and its RF transmitting coil. Further, the second ring conductor includes a plurality of second capacitors connected in series, and the plurality of second capacitors are separated from the imaging space in a direction parallel to the first direction from the second ring conductor. 1 is an example of an MRI apparatus having the above configuration and its RF transmission coil.

  FIG. 9 is a diagram illustrating a configuration example and effects of the planar birdcage coil according to the third embodiment. FIG. 9A is a plan view of the planar birdcage coil 90. FIG. 9B is a schematic diagram in which the outer ring conductor 91 and the capacitor 64 which are the first ring conductors of the planar birdcage coil 90 are displayed in a one-dimensional manner. Here, in the conventional planar birdcage coil 60 shown in FIG. 4B, the capacitor 64 and the outer ring conductor 61 are arranged on the same plane, whereas in FIG. In the planar birdcage coil of this embodiment shown, the capacitor 94 is farther away from the outer ring conductor 91 than the plane parallel to the coil plane through the xy plane, that is, the center of the imaging space.

  The dotted line plot in FIG. 9C shows the electric field strength distribution 68 in the vicinity of the ring conductor 61 outside the conventional planar birdcage coil 60 shown in FIG. The solid line plot in (c) of FIG. 9 is the same position as in (c) of FIG. 4, that is, a number parallel to the static magnetic field 96 (z-axis direction) from the respective positions in (b) of FIG. An electric field intensity distribution 98 at a position separated by cm is shown. According to FIG. 9 (c), the electric field strength distribution 98 of the planar birdcage coil 90 of this embodiment is significantly lower in the vicinity of the capacitor than the electric field strength distribution 68 of the conventional planar birdcage coil 60. Therefore, according to the planar birdcage coil 90 of the present embodiment, it is possible to provide an MRI apparatus and an RF transmission coil for the MRI apparatus that are less exposed to electric field than the conventional one and are excellent in safety.

  In the present embodiment, the capacitor 74 connected in series to the outer ring conductor 91 is shown as being separated from the xy plane relative to the outer ring conductor 91. Similarly, in the second ring conductor, A planar birdcage coil in which a capacitor 74 connected in series to an inner ring conductor 92 is separated from the xy plane relative to the inner ring conductor 92 is also an example of this embodiment, and the same effects as described above can be obtained. .

  The effect of each embodiment can be enhanced by combining this embodiment with the first embodiment or the second embodiment. That is, the outer ring conductor 91 and / or the inner ring conductor 92 is relatively far from the xy plane than the rung conductor 93, and the capacitor 74 connected in series to the outer ring conductor 91 is connected to the outer ring conductor 91. And a planar birdcage coil that is farther away from the xy plane than 91 and / or in which the capacitor 74 connected in series to the inner ring conductor 92 is further away from the xy plane than the inner ring conductor 92. It is an example of a present Example.

  In the fourth embodiment, the RF transmission coil further includes a third ring conductor having a diameter intermediate between the diameter of the first ring conductor and the diameter of the second ring conductor and connected to the plurality of rung conductors. , An MRI apparatus having a configuration in which the first ring conductor, the second ring conductor, and the third ring conductor are separated from the imaging space in a direction parallel to the first direction from the plurality of rung conductors, and an RF thereof It is an Example of a transmission coil.

  FIG. 10 is a diagram illustrating a configuration example and effect of the planar birdcage coil according to the fourth embodiment. 10A is a plan view of the planar birdcage coil 100 of the present embodiment, and FIG. 10B is a cross-sectional view in the xz plane. The planar birdcage coil of the embodiment shown in FIG. 10 is a third ring conductor in addition to the outer ring conductor 101 that is the first ring conductor and the inner ring conductor 102 that is the second ring conductor. An intermediate ring conductor 103 is provided. As described above, the intermediate ring conductor 103 has an effect of improving the uniformity of the RF magnetic field. In the planar birdcage coil 100 of the present embodiment, the outer ring conductor 101, the inner ring conductor 102, and the intermediate ring conductor 103 pass through the center of the imaging space and are parallel to the coil surface, rather than the rung conductors 104a and 104b. Away from. Furthermore, the rung conductor 104 a is connected to the outer ring conductor 101 or the intermediate ring conductor 103 by a diode 106. Further, the rung conductor 104b may be connected to the inner ring conductor 102 or the intermediate ring conductor 103 by a diode 106 as necessary.

  Here, of the two terminals of each diode 106, the first terminal is connected to the outer ring conductor 101, the inner ring conductor 102, or the intermediate ring conductor 103, and the second terminal is connected to the rung conductor 104a or 104b. It is desirable to be connected. That is, the diode 106 is disposed at a level difference between the outer ring conductor 101 or the inner ring conductor 102 or the intermediate ring conductor 103 of the planar birdcage coil 100 and the rung conductor 104a or 104b. Is desirable. By disposing the diode 106 at the position of the step, the diode 106 that generates heat can be separated from the imaging space, that is, the subject, and safety can be improved.

  The dotted line plot in FIG. 10 (c) shows the electric field strength distribution 108 of a conventional planar birdcage coil having an intermediate ring conductor. The solid line plot in FIG. 10 (c) is a direction parallel to the static magnetic field 107 (z-axis direction) and a few cm away from the origin side from the rung conductors 104a and 104b of the planar birdcage coil 100 of this embodiment. An electric field strength distribution 109 is shown. The horizontal axis of the graph of FIG. 10C represents the position in the x-axis direction, and the radius of the outer ring conductor 101 is a, and the radius of the intermediate ring conductor 103 is b. According to this distribution, the electric field strength distribution 109 of the planar birdcage coil 100 of the present embodiment having the intermediate ring conductor 103 is compared with the electric field strength distribution 108 of the conventional planar birdcage coil having the intermediate ring conductor. x = ± a, ie, near the outer ring conductor, x = ± b, ie, near the middle ring conductor, and x = 0, ie, near the inner ring conductor. Therefore, according to the planar birdcage coil 100 of the present embodiment, it is possible to provide an MRI apparatus and an RF transmission coil for the MRI apparatus that are less exposed to electric field than the conventional one and are excellent in safety.

  In the fifth embodiment, two RF transmission coils are arranged in the vertical direction that is the direction of the static magnetic field, and in at least one of the two RF transmission coils, the first ring conductor is in the imaging direction in the vertical direction from the plurality of rung conductors. 1 is an embodiment of an MRI apparatus having a configuration separated from the RF transmitter coil and its RF transmission coil. In other words, two RF receiving coils opposed to detect a nuclear magnetic resonance signal are provided, and the two RF transmitting coils have a first ring conductor having a first diameter and a second diameter smaller than the first diameter. And a plurality of rung conductors connecting the first ring conductor and the second ring conductor, and at least one of the two RF transmission coils includes a plurality of first ring conductors. It is an Example of the structure which has left | separated from the imaging space to the perpendicular direction from the rung conductor.

  FIG. 11 is a diagram illustrating an example of a planar birdcage coil in the present embodiment. In this example, an RF transmission coil is configured by combining the planar birdcage coil 70 shown in the first embodiment and the conventional planar birdcage 60. If the z direction in FIG. 11 is defined as upward in the vertical direction, the table on which the subject is mounted in the imaging space is disposed between the origin and the planar birdcage coil 60. When the table itself has a thickness of about several centimeters, there may be a case where exposure to an electric field derived from the planar birdcage coil 60 does not cause a problem. In this case, only by applying the configuration of the first embodiment only to the upper planar birdcage coil 70, exposure to an electric field can be reduced as compared with the prior art, and an MRI apparatus excellent in safety and an RF transmission coil for an MRI apparatus can be provided. . In the present embodiment, an example in which the conventional planar birdcage coil and the birdcage coil 70 of the first embodiment are combined is shown. However, each planar birdcage coil described in the second embodiment, the third embodiment, or the fourth embodiment and the conventional one. A combination of planar birdcage coils is also included in the configuration of this embodiment.

  In Example 6, the RF transmission coil is disposed on a support formed of a non-metallic material, the support has a bowl-shaped part, a plane part, and a step part, and the first ring conductor is bowl-shaped. An MRI apparatus having a configuration in which a rung conductor is formed in a flat part, a first ring conductor is connected to each of the plurality of rung conductors via a diode, and a diode is arranged in the stepped part, and It is the Example of the RF transmission coil.

  FIG. 12 is a diagram illustrating a configuration example of a planar birdcage coil according to the sixth embodiment. FIG. 12A is a perspective view of the support 110 of the planar birdcage coil 70 of the present embodiment. The support 110 has a hook-shaped portion 111, a flat surface portion 112, a stepped portion 113, and a vent 114, and is made of a non-metallic material such as fiber reinforced plastic (FRP). It is desirable that the surfaces of the bowl-shaped portion 111 and the plane portion 112 are arranged so as to be perpendicular to the direction of the static magnetic field 76, respectively. The planar birdcage coil 70 is formed of a thin metal body such as a copper foil and has flexibility, so that it is preferably formed on the support body 110. Further, by arranging the diode 75 in the stepped portion 113, the locally generating diode 75 can be separated from the imaging space, that is, the subject, and safety can be improved. Furthermore, there is an effect that assembly work such as soldering is simplified.

  If the rung conductor 73 becomes longer, in order to further enhance the air-cooling effect of the RF coil, the support body 110 is formed with a vent 114 in the flat surface portion 112, and a plurality of flanges 111, the flat surface portion 112, and the stepped portion 113 are formed. Form slit holes and punch holes.

  In this embodiment, the birdcage coil 70 according to the first embodiment is mounted on the support 110. However, the same applies to the planar birdcage coil described in the second, third, or fourth embodiment. It is assumed that the coil is held on a support formed according to the coil shape. Therefore, according to the planar birdcage coil of the present embodiment, the MRI apparatus and the MRI apparatus, which are less exposed to electric field than the prior art, are excellent in safety, are less likely to be deformed, generate less heat, and are easy to assemble. An RF transmitter coil can be provided.

  Example 7 includes a static magnetic field generation system that generates a static magnetic field in a first direction, an RF transmission system that includes an RF transmission coil that generates an RF magnetic field, and a gradient magnetic field system that generates a gradient magnetic field superimposed on the static magnetic field. An RF receiving system including an RF receiving coil for detecting a nuclear magnetic resonance signal, wherein the RF transmitting coil has a first ring conductor having a first diameter and a second diameter smaller than the first diameter. A second ring conductor, and a plurality of rung conductors connecting the first ring conductor and the second ring conductor, wherein the first ring conductor has a first direction from the center of gravity of each of the plurality of rung conductors. It is an Example of the MRI apparatus which has the structure which is separated from the imaging space in the parallel direction, and its RF transmission coil.

  FIG. 13 is a diagram illustrating a configuration example and effects of a planar birdcage coil according to the seventh embodiment. FIG. 13A is a plan view of the planar birdcage coil 120 of the seventh embodiment, and FIG. 13B is a cross-sectional view in the xz plane. Here, the space between the pair of planar birdcage coils is the imaging space, the center of this imaging space is defined as the origin, and the direction of the static magnetic field is defined as the z-axis direction. In the planar birdcage coil of this embodiment shown in FIG. 13, the outer ring conductor 121 is from the plane parallel to the coil plane through the xy plane, that is, the center of the imaging space, rather than the center of gravity of each of the plurality of rung conductors 123. is seperated. Further, the outer ring conductor 121 and the rung conductor 123 are connected by a diode 125. Here, of the two terminals of each diode 125, the first terminal is preferably connected to the outer ring conductor 121, and the second terminal is preferably connected to the end of the rung conductor 123. The other end of the rung conductor 123 is connected to the inner ring conductor 122. When the rung conductor 123 has a uniform diameter, the center of gravity of each of the rung conductors 123 is located at a substantially middle point between both ends thereof. With this arrangement, the heat generating diode 125 can be separated from the imaging space, that is, the subject, and safety can be improved.

  The dotted line plot in FIG. 13C shows the electric field strength distribution 67 of the conventional planar birdcage coil 60 shown in FIG. The solid line plot in FIG. 13C is the same position as in FIG. 3B, that is, the direction parallel to the static magnetic field 126 from the point closest to the origin of the rung conductor 73 of the planar birdcage coil 70 (z-axis direction). ) And an electric field intensity distribution 127 at a position several cm away from the origin. The horizontal axis of the graph in FIG. 13C represents the position in the x-axis direction, and the radius of the outer ring conductor 121 is a. According to this distribution, the electric field strength distribution 127 of the planar birdcage coil 120 of this embodiment is x = ± a, that is, in the vicinity of the outer ring conductor, compared to the electric field strength distribution 67 of the conventional planar birdcage coil 60. Remarkably low. Therefore, according to the planar birdcage coil 120 of the present embodiment, it is possible to provide an MRI apparatus and an RF transmission coil for the MRI apparatus that are less exposed to an electric field than before and that are superior in safety.

  In the present embodiment, the outer ring conductor 121 is separated from the centroid of the rung conductor 123 from the plane parallel to the coil surface through the xy plane, that is, the center of the imaging space. Similarly, 122 is bent in a V shape near the center of gravity of the plane birdcage coil that is away from the plane parallel to the coil plane through the xy plane, that is, the center of the imaging space, rather than the center of gravity of the rung conductor 123. A planar birdcage coil having a configuration having a rung conductor 123 is also included in the configuration of this embodiment.

  Example 8 is a static magnetic field generation system that generates a static magnetic field in a first direction, an RF transmission system that includes an RF transmission coil that generates an RF magnetic field, and a gradient magnetic field system that generates a gradient magnetic field superimposed on the static magnetic field. An RF receiving system including an RF receiving coil for detecting a nuclear magnetic resonance signal, wherein the RF transmitting coil includes a ring conductor and a plurality of rung conductors that radially connect the ring conductor, It is the Example of the magnetic resonance imaging apparatus of the structure separated from the imaging space in the direction parallel to a 1st direction from several rung conductors, and the planar birdcage coil which is the RF transmission coil.

  FIG. 14 is a diagram illustrating a configuration example of a planar birdcage coil according to the eighth embodiment. 14A is a plan view of the planar birdcage coil 130 of this embodiment, and FIG. 14B is a cross-sectional view in the xz plane. A planar birdcage coil 130 serving as an RF transmission coil according to the present embodiment includes a ring conductor 131, a plurality of rung conductors 133, a plurality of capacitors 134, and a plurality of diodes 135. Here, the space between the pair of planar birdcage coils is the imaging space, the center of this imaging space is defined as the origin, and the direction of the static magnetic field is defined as the z-axis direction. In the planar birdcage coil of this embodiment shown in FIG. 14, the ring conductor 131 is separated from the rung conductor 133 from the plane parallel to the coil plane through the xy plane, that is, the center of the imaging space. In other words, the first ring conductor is separated from the imaging space in a direction parallel to the first direction, which is the direction of the static magnetic field, from the plurality of rung conductors. Therefore, according to the planar birdcage coil 130 of the present embodiment, as in the case of the first embodiment, the MRI apparatus and the RF transmitter coil for the MRI apparatus, which are less in terms of electric field exposure than conventional and excellent in safety, are provided. it can.

  Further, the ring conductor 131 and the rung conductor 133 are connected by a diode 135. That is, the ring conductor is connected to each of the plurality of rung conductors via a diode. Here, of the two terminals of each diode 135, the first terminal is connected to the ring conductor 131, and the second terminal Is preferably connected to the end of the rung conductor 133. That is, it is desirable that the diode 135 be disposed at a level difference between the ring conductor 131 and the rung conductor 133 outside the planar birdcage coil. By disposing the diode 135 at the position of the step, the diode 135 that generates heat can be separated from the imaging space, that is, the subject, and safety can be improved.

  As described above, in the present invention, in view of the characteristic situation of a planar birdcage coil, exposure to an electric field associated with irradiation of an RF electromagnetic wave to a subject is reduced, and bioabsorption of electromagnetic energy, that is, SAR is reduced as compared with the conventional case. An RF transmission coil comprising a planar birdcage coil and an open MRI apparatus using the same can be provided.

  In addition, this invention is not limited to an above-described Example, Various modifications are included. For example, the above-described embodiments have been described in detail for better understanding of the present invention, and are not necessarily limited to those having all the configurations described. Further, a part of the configuration of one embodiment can be replaced with the configuration of another embodiment, and the configuration of another embodiment can be added to the configuration of one embodiment. For example, the configurations of Example 3, Example 5, Example 6, and Example 7 can be added to the configuration of Example 8. Further, it is possible to add, delete, and replace other configurations for a part of the configuration of each embodiment.

  In the description detailed above with reference to the drawings, not only the invention described in the claims but also many inventions are disclosed. Some of these are listed below.

<List 1>
An RF transmission coil for an open MRI apparatus that generates an RF magnetic field in a static magnetic field,
A first ring conductor of a first diameter;
A second ring conductor having a second diameter smaller than the first diameter;
A plurality of rung conductors connecting the first ring conductor and the second ring conductor;
The RF transmission coil, wherein the first ring conductor is further away from the imaging space in a direction parallel to the direction of the static magnetic field than the plurality of rung conductors.

<List 2>
An RF transmission coil according to List 1,
The RF transmission coil, wherein the second ring conductor is further away from the imaging space in a direction parallel to the direction of the static magnetic field than the plurality of rung conductors.

<List 3>
An RF transmission coil according to List 1,
The RF transmission coil, wherein the first ring conductor is connected to each of the plurality of rung conductors via a diode.

<List 4>
An RF transmission coil according to List 1,
The first ring conductor includes a plurality of first capacitors connected in series, and the plurality of first capacitors from the imaging space in a direction parallel to the direction of the static magnetic field from the first ring conductor. An RF transmitter coil characterized by being separated.

<List 5>
An RF transmission coil according to List 1,
The second ring conductor includes a plurality of second capacitors connected in series, and the plurality of second capacitors from the imaging space in a direction parallel to the direction of the static magnetic field from the second ring conductor. An RF transmitter coil characterized by being separated.

<List 6>
An RF transmission coil according to List 1,
A first ring conductor having a first diameter, a second ring conductor having a second diameter smaller than the first diameter, and a third intermediate between the first diameter and the second diameter A third ring conductor having a diameter, and a plurality of rung conductors connecting the first ring conductor, the second ring conductor, and the third ring conductor, and the first ring conductor and the first ring conductor Two ring conductors and the third ring conductor are separated from the imaging space in a direction parallel to the first direction from the plurality of rung conductors,
An RF transmission coil characterized by that.

<List 7>
An RF transmission coil according to List 1,
The RF transmission coil is disposed on a support formed of a non-metallic material, the support has a hook-shaped portion, a flat surface portion, and a step portion, and the first ring conductor is formed on the hook-shaped portion. The rung conductor is formed on the planar portion, the first ring conductor is connected to each of the plurality of rung conductors via a diode, and the diode is disposed on the stepped portion. A featured RF transmitter coil.

<List 8>
An RF transmission coil according to List 7,
An RF transmission coil comprising a vent hole in the flat portion.

<List 9>
Two opposed RF transmitter coils for open MRI apparatus that are installed in a static magnetic field generated in the vertical direction and generate an RF magnetic field,
The two RF transmitting coils include a first ring conductor having a first diameter, a second ring conductor having a second diameter smaller than the first diameter, the first ring conductor, and the second ring conductor. A plurality of rung conductors for connecting the ring conductors, and in at least one of the two RF transmission coils, the first ring conductor is further away from the imaging space in the vertical direction than the plurality of rung conductors. An RF transmission coil characterized by that.

<List 10>
An RF transmission coil for an open MRI apparatus installed in a static magnetic field in a first direction,
A first ring conductor having a first diameter, a second ring conductor having a second diameter smaller than the first diameter, and a plurality of parts connecting the first ring conductor and the second ring conductor. An RF transmission coil comprising a rung conductor, wherein the first ring conductor is separated from the imaging space in a direction parallel to the first direction from the center of gravity of the rung conductor.

<List 11>
A static magnetic field generation system for generating a static magnetic field in a first direction;
An RF transmission system including an RF transmission coil for generating an RF magnetic field;
A gradient magnetic field system for generating a gradient magnetic field superimposed on the static magnetic field;
An RF receiving system including an RF receiving coil for detecting a nuclear magnetic resonance signal,
The RF transmitter coil is
A ring conductor, and a plurality of rung conductors that radially connect the ring conductor;
The magnetic resonance imaging apparatus, wherein the ring conductor is separated from the imaging space in a direction parallel to the first direction from the plurality of rung conductors.

<List 12>
A magnetic resonance imaging apparatus according to List 11, comprising:
The magnetic resonance imaging apparatus, wherein the first direction is a vertical direction.

<List 13>
A magnetic resonance imaging apparatus according to List 11, comprising:
The magnetic resonance imaging apparatus, wherein the ring conductor is connected to each of the plurality of rung conductors via a diode.

<List 14>
A magnetic resonance imaging apparatus according to List 11, comprising:
The ring conductor includes a plurality of capacitors connected in series, and the plurality of first capacitors are separated from the imaging space in a direction parallel to the first direction from the ring conductor. Magnetic resonance imaging device.

<List 15>
A magnetic resonance imaging apparatus according to List 11, comprising:
The first direction is a vertical direction;
Two RF transmitter coils are arranged in the vertical direction,
The magnetic resonance imaging apparatus according to claim 1, wherein in at least one of the two RF transmission coils, the ring conductor is separated from the imaging space in a vertical direction with respect to the plurality of rung conductors.

<List 16>
A magnetic resonance imaging apparatus according to List 11, comprising:
The RF transmitter coil is disposed on a support formed of a non-metallic material, the support has a hook-shaped portion, a flat surface portion, and a step portion, and the ring conductor is disposed in the hook-shaped portion. The rung conductor is formed in the flat portion, the ring conductor is connected to each of the plurality of rung conductors via a diode, and the diode is disposed in the stepped portion. Resonance imaging device.

<List 17>
A static magnetic field generation system for generating a static magnetic field in a first direction;
An RF transmission system including an RF transmission coil for generating an RF magnetic field;
A gradient magnetic field system for generating a gradient magnetic field superimposed on the static magnetic field;
An RF receiving system including an RF receiving coil for detecting a nuclear magnetic resonance signal,
The RF transmitter coil is
A ring conductor, and a plurality of rung conductors that radially connect the ring conductor;
The magnetic resonance imaging apparatus, wherein the ring conductor is separated from the imaging space in a direction parallel to the first direction from the center of gravity of each of the plurality of rung conductors.

1 Subject 2 Table 3 Sequencer 4 Central Processing Unit (CPU)
DESCRIPTION OF SYMBOLS 10 Static magnetic field generation system 21 Gradient magnetic field coil 22 Gradient magnetic field power supply 31 RF oscillator 32 Modulator 33 RF amplifier 34 RF transmission coil 41 RF reception coil 42 Signal amplifier 43 Phase detector 44 A / D converter 50 Signal processing system 51 Magnetic disk 52 Optical disk 53 Display 54 Operation unit 60, 70, 80, 90, 100, 120, 130 Planar birdcage coil 61, 71, 81, 91, 101, 121, 131 Outer ring conductors 62, 72, 82, 92, 102 122 Inner ring conductors 63, 73, 83, 93, 104a, 104b, 123, 133 Lang conductors 64, 74, 84, 94, 105, 124, 134 Capacitors 65, 75, 85, 95, 107, 125, 135 Diode 66, 76, 86, 96, 106, 126, 136 Fields 67, 68, 108, Electric field intensity distribution 77, 87, 98, 109, 127 in the vicinity of the conventional planar birdcage coil 103 Electric field intensity distribution in the vicinity of the planar birdcage coil of Example 103 Intermediate ring conductor 110 Support body 111 鍔Part 112 Plane part 113 Step part 114 Vent

Claims (9)

A static magnetic field generation system for generating a static magnetic field in a first direction;
An RF transmission system including an RF transmission coil for generating an RF magnetic field;
A gradient magnetic field system for generating a gradient magnetic field superimposed on the static magnetic field;
An RF receiving system including an RF receiving coil for detecting a nuclear magnetic resonance signal,
The RF transmitter coil is
A first ring conductor of a first diameter;
A second ring conductor having a second diameter smaller than the first diameter;
A plurality of rung conductors connecting the first ring conductor and the second ring conductor;
The first ring conductor is separated from the imaging space in a direction parallel to the first direction from the plurality of rung conductors ;
The first ring conductor includes a plurality of first capacitors connected in series, and the plurality of first capacitors are separated from the imaging space in a direction parallel to the first direction from the first ring conductor. Away
A magnetic resonance imaging apparatus. The magnetic resonance imaging apparatus according to claim 1,
The first direction is a vertical direction;
A magnetic resonance imaging apparatus. The magnetic resonance imaging apparatus according to claim 1,
The second ring conductor is separated from the imaging space in a direction parallel to the first direction from the plurality of rung conductors;
A magnetic resonance imaging apparatus. The magnetic resonance imaging apparatus according to claim 1,
The first ring conductor is connected to each of the plurality of rung conductors via a diode;
A magnetic resonance imaging apparatus. A static magnetic field generation system for generating a static magnetic field in a first direction;
An RF transmission system including an RF transmission coil for generating an RF magnetic field;
A gradient magnetic field system for generating a gradient magnetic field superimposed on the static magnetic field;
An RF receiving system including an RF receiving coil for detecting a nuclear magnetic resonance signal,
The RF transmitter coil is
A first ring conductor of a first diameter;
A second ring conductor having a second diameter smaller than the first diameter;
A plurality of rung conductors connecting the first ring conductor and the second ring conductor;
The first ring conductor is separated from the imaging space in a direction parallel to the first direction from the plurality of rung conductors;
The second ring conductor includes a plurality of second capacitors connected in series, and the plurality of the second capacitors from the imaging space in a direction parallel to the first direction from the second ring conductor. Away
A magnetic resonance imaging apparatus. The magnetic resonance imaging apparatus according to claim 5 ,
The first direction is a vertical direction;
A magnetic resonance imaging apparatus. The magnetic resonance imaging apparatus according to claim 5 ,
The second ring conductor is separated from the imaging space in a direction parallel to the first direction from the plurality of rung conductors ;
A magnetic resonance imaging apparatus. A static magnetic field generation system for generating a static magnetic field in a first direction;
An RF transmission system including an RF transmission coil for generating an RF magnetic field;
A gradient magnetic field system for generating a gradient magnetic field superimposed on the static magnetic field;
An RF receiving system including an RF receiving coil for detecting a nuclear magnetic resonance signal,
The RF transmitter coil is
A first ring conductor of a first diameter;
A second ring conductor having a second diameter smaller than the first diameter;
A plurality of rung conductors connecting the first ring conductor and the second ring conductor;
The first ring conductor is separated from the imaging space in a direction parallel to the first direction from the plurality of rung conductors;
The first direction is a vertical direction;
Two RF transmitter coils are arranged in the vertical direction,
In at least one of the two RF transmission coils, the first ring conductor is separated from the imaging space in a vertical direction from the plurality of rung conductors,
A magnetic resonance imaging apparatus. A static magnetic field generation system for generating a static magnetic field in a first direction;
An RF transmission system including an RF transmission coil for generating an RF magnetic field;
A gradient magnetic field system for generating a gradient magnetic field superimposed on the static magnetic field;
An RF receiving system including an RF receiving coil for detecting a nuclear magnetic resonance signal,
The RF transmitter coil is
A first ring conductor of a first diameter;
A second ring conductor having a second diameter smaller than the first diameter;
A plurality of rung conductors connecting the first ring conductor and the second ring conductor;
The first ring conductor is separated from the imaging space in a direction parallel to the first direction from the plurality of rung conductors;
The RF transmission coil is disposed on a support formed of a non-metallic material, the support has a hook-shaped portion, a flat surface portion, and a step portion, and the first ring conductor is the hook-shaped portion. Placed in
The rung conductor is formed in the flat portion, the first ring conductor is connected to each of the plurality of rung conductors via a diode, and the diode is disposed in the stepped portion.
A magnetic resonance imaging apparatus.

Images