JP2005253820A - Magnetic resonance imaging apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a magnetic resonance imaging apparatus that preferably controls an eddy current generating in a coil storage container even in the case that flat active sealed type gradient magnetic field coils are arranged in a recessed arrangement space between the top and the bottom faces of the coil storage container. <P>SOLUTION: The magnetic resonance imaging apparatus comprises a static magnetic field generating means (4) arranged face to face with an imaging space in between, having a pair of static magnetic field generators with recessed arrangement spaces on the sides facing to each other, and generating a static magnetic field to each other; main coils (13c) arranged in the recessed arrangement spaces and generating a magnetic field in the imaging space; and magnetic field generating coils having sealed coils (13d), arranged between the main coils and the static magnetic field generator, and used to cancel a magnetic filed generated by the main coils in the other side of the imaging space. The magnetic field generating coil comprises first coils (23) in the recessed arrangement space, which control a magnetic field generated by the main coils and the sealed coils on a side face in parallel with the static magnetic field direction in the recessed arrangement space. <P>COPYRIGHT: (C)2005,JPO&NCIPI

Description

  The present invention relates to a magnetic resonance imaging apparatus (hereinafter referred to as an MRI apparatus), and more particularly to a technique for suitably suppressing an eddy current generated by driving a gradient magnetic field coil.

  The MRI system uses the nuclear magnetic resonance phenomenon that occurs in the nucleus of the atoms that make up the subject when the subject placed in a uniform static magnetic field is irradiated with electromagnetic waves. Hereinafter, an NMR signal is detected, and an image is reconstructed using the NMR signal, thereby obtaining a magnetic resonance image (hereinafter referred to as an NMR image) representing the physical properties of the subject. In order to give this imaging position information, a gradient magnetic field is applied in a superimposed manner on the static magnetic field.

  A conventional MRI apparatus includes a static magnetic field generation source for generating a static magnetic field in a measurement space for aligning the spin directions of the hydrogen nuclei (protons) of the subject in the examination room in which the apparatus is installed, and the subject. In order to provide position information, a three-channel gradient coil that performs position encoding in the X, Y, and Z directions, a transmission high-frequency coil that emits electromagnetic waves having a proton resonance frequency, and NMR from protons A receiving high-frequency coil for receiving signals and a shim coil for correcting a generated static magnetic field and gradient magnetic field are further provided. However, as a method for generating a static magnetic field, a method using a superconducting coil, a method using a normal conducting coil, a method using a permanent magnet, and the like are known.

In recent years, in a vertical magnetic field type MRI apparatus in which the direction of the static magnetic field is orthogonal to the body axis direction of the subject, a concave arrangement space is provided on the upper and lower opposing surfaces of the coil container arranged opposite to each other, and a flat plate is inclined in the space A configuration in which a magnetic field coil is accommodated has been proposed, and this configuration is desirable in order to reduce the required magnetomotive force (see, for example, Patent Document 1).
Japanese Patent No. 3469436

  On the other hand, when an eddy current accompanying the driving of the gradient magnetic field coil is generated on the surface of the magnet container for generating a static magnetic field, the gradient magnetic field waveform is distorted from the original shape (for example, a rectangular wave), and the image quality deteriorates. To prevent this, a gradient magnetic field shield coil is provided in each of the X, Y, and Z axis directions on the outside of the X, Y, and Z gradient magnetic field main coil, and the magnetic field generated by the main coil is magnetized. There are some which are made to cancel on the container surface. This is called an active shield type gradient magnetic field coil.

Patent Document 2 discloses a technique that suitably cancels out a magnetic field generated in an end region on the surface of a magnet container in a flat-type active shield type gradient magnetic field coil for a vertical magnetic field type MRI apparatus.
JP 2002-112977 A

  In the prior art described in Patent Document 2, a flat main coil with a gradient magnetic field and a flat magnetic field with a gradient magnetic field arranged on the back surface of the main coil with respect to the imaging space and having a current direction substantially opposite to the main coil. In the active shield type gradient magnetic field coil having a shield coil, a third coil array surface is provided between the main coil array surface of the gradient magnetic field and the shield coil array surface of the gradient magnetic field, and the third coil array surface is provided in the same direction as the shield coil. By passing an electric current, the magnetic field generated in the end region on the surface of the magnet container is preferably canceled out, and the eddy current is suppressed.

The present inventor has found the following problems as a result of studying the above prior art.
That is, in the prior art described in Patent Document 2, as shown in FIG. 1 of Patent Document 2, there is no concave arrangement space on the upper and lower opposed surfaces of the coil storage container arranged opposite to each other, and a flat vertical In the magnetic field type MRI apparatus, the suppression of eddy current was optimized.

  However, when the flat-type active shield type gradient magnetic field coil described in Patent Document 2 is arranged in the concave arrangement space of the MRI apparatus described in Patent Document 1, the magnetic flux density between the third coil and the main coil is large. Therefore, when the leakage magnetic field thereby reaches the inner side surface of the concave arrangement space (a surface parallel to the Z-axis that is not the concave bottom portion), an eddy current is generated and the image quality deteriorates.

  It is an object of the present invention to suitably apply eddy currents generated in a coil container even when a flat-type active shield type gradient magnetic field coil is disposed in a concave arrangement space formed on the upper and lower surfaces of the coil container. An object of the present invention is to provide a suppressed magnetic resonance imaging apparatus.

  According to the first feature of the present invention, it has a pair of static magnetic field generation sources that are arranged to face each other with a shooting space in between, and each provided with a concave arrangement space on the facing surface side, in the facing direction. Static magnetic field generating means for generating a static magnetic field, a main coil disposed in the concave arrangement space and generating a magnetic field in the imaging space, and the main coil disposed between the main coil and the static magnetic field generation source In the magnetic resonance imaging apparatus including a magnetic field generating coil having a shield coil for canceling a magnetic field generated on the opposite side to the imaging space, the magnetic field generating coil includes the main coil and the shield coil in the concave shape. A magnetic resonance imaging apparatus comprising a first coil for suppressing a magnetic field generated on a side surface parallel to the static magnetic field direction of the arrangement space in the concave arrangement space It is provided.

  According to the second feature of the present invention, the second coil for correcting the change in the magnetic field generated in the imaging space by the first coil is within the concave arrangement space with respect to the central axis direction of the static magnetic field direction. Thus, a magnetic resonance imaging apparatus having the first feature of the present invention is provided, which is provided inside the first coil in the radial direction.

  According to the third aspect of the present invention, the position of the static magnetic field direction in which the first and second coils are disposed is the same as the position of the plane in which the main coil is disposed. A magnetic resonance imaging apparatus having the second feature is provided.

  According to the fourth feature of the present invention, the position in the static magnetic field direction where the first and second coils are arranged is the position of the plane where the main coil is arranged, and the position of the plane where the shield coil is arranged. There is provided a magnetic resonance imaging apparatus having the second feature of the present invention characterized in that the position is in a third static magnetic field direction different from any of the above.

  According to the fifth feature of the present invention, the position in the static magnetic field direction where the first and second coils are arranged is the position of the plane where the main coil is arranged, and the position of the plane where the shield coil is arranged. There is provided a magnetic resonance imaging apparatus having a second feature characterized by being between.

  According to the present invention, even when a flat active shield type gradient magnetic field coil is arranged in a concave arrangement space formed on the upper and lower surfaces of the coil container, eddy currents generated in the coil container are preferably used. A suppressed magnetic resonance imaging apparatus can be provided.

  Hereinafter, the system configuration of a general MRI apparatus will be described in detail with reference to FIG. The MRI apparatus is roughly classified into a central processing unit (hereinafter abbreviated as CPU) 1, a sequencer 2, a transmission system 3, a static magnetic field generating magnet 4, a receiving system 5, a gradient magnetic field generating system 21, and a signal. It consists of a processing system 6.

  The CPU 1 controls the sequencer 2, the transmission system 3, the reception system 5, and the signal processing system 6 according to a predetermined program. The sequencer 2 operates based on a control command from the CPU 1, and sends various commands necessary for collecting image data of the tomographic plane of the subject 7 to the transmission system 3, the gradient magnetic field generation system 21, and the reception system 5. ing.

  The transmission system 3 includes a high-frequency oscillator 8, a modulator 9, and an irradiation coil 11. The reference high-frequency pulse from the high-frequency oscillator 8 is amplitude-modulated by the modulator 9 according to a command from the sequencer 2, and the amplitude-modulated high-frequency signal is transmitted. By amplifying the pulse through the high frequency amplifier 10 and supplying it to the irradiation coil 11, a predetermined pulsed electromagnetic wave is irradiated to the subject.

  The static magnetic field generating magnet 4 is for generating a uniform static magnetic field in a predetermined direction around the subject 7. In the static magnetic field generating magnet 4, an irradiation coil 11, a gradient magnetic field coil 13, and a receiving coil 14 are arranged. The gradient magnetic field coil 13 is included in the gradient magnetic field generation system 21 and receives a current supplied from the gradient magnetic field power supply 12 and generates a gradient magnetic field under the control of the sequencer 2.

  The receiving system 5 detects a high-frequency signal (NMR signal) emitted by nuclear magnetic resonance of the nucleus of the biological tissue of the subject, and includes a receiving coil 14, an amplifier 15, a quadrature detector 16, and an A / D converter. The high frequency signal (NMR signal) of the response of the subject due to the electromagnetic wave irradiated from the irradiation coil 14 is detected by the receiving coil 14 disposed in the vicinity of the subject, and the amplifier 15 and orthogonal The signal is input to the A / D converter 17 via the phase detector 16, converted into a digital quantity, and the signal is sent to the CPU 1.

  The signal processing system 6 includes an external storage device such as a magnetic disk 20 and an optical disk 19 and a display 18 such as a CRT. When data from the reception system 5 is input to the CPU 1, the CPU 1 performs signal processing and image re-processing. Processing such as configuration is executed, and the resulting image of a desired tomographic plane of the subject 7 is displayed on the display 18 and stored in the magnetic disk 20 of the external storage device or the like.

  In the vertical magnetic field type MRI apparatus described in Patent Document 1 having the above system configuration, an arrangement example in which a flat active shield type gradient magnetic field coil is arranged in the concave arrangement space on the upper and lower opposing surfaces of the coil container is disclosed in It is disclosed in Examples 2 to 4 of 9-262223. Among these, the configuration shown in the second embodiment is the most simple and inexpensive configuration of the shield coil. However, in the main coil and the shield coil arranged in the second embodiment, in order to prevent eddy current from being generated on the inner side surface of the concave arrangement space, it is necessary to add the additional current described below. .

  FIG. 2 is a part of a cross section of a static magnetic field generation source and a gradient magnetic field coil of the vertical magnetic field type MRI apparatus according to Embodiment 1 of the present invention. However, Fig. 2 is an example of a Z-axis gradient magnetic field coil in which the coil shape is axisymmetric with respect to the Z-axis (the direction of the static magnetic field). When the cross section of Fig. 2 is viewed from the direction of the static magnetic field, Coils are lined up. The coil pattern of the gradient magnetic field coil is known in US Pat. 4a is a side surface of the concave arrangement space, 4b is a bottom surface of the concave arrangement space, 13a is a shield coil surface of the gradient magnetic field coil, 13b is a main coil surface of the gradient magnetic field coil, and a symbol with a dot added at the center of the circle indicated by 21 Is a coil in which current flows from the back side of the paper to the front side, a symbol with an X mark added to the circle indicated by 22 is a coil in which current flows from the front side to the back side of the paper surface, and one or more coils indicated by 23 have additional current 1 The one or more coils indicated by 24 are coils for causing the additional current 2 to flow. Reference numeral 13c denotes a conventional shield coil pattern, and reference numeral 13d denotes a conventional main coil pattern, which are shown in FIG. 9 of Patent Document 2, respectively.

  According to this embodiment, in addition to the conventional main coil and shield coil, the additional current 1 is first applied to the main coil surface. Thus, the magnetic field generated on the inner side surface of the concave arrangement space can be canceled by the main coil and the shield coil. On the other hand, since the gradient magnetic field in the imaging space changes due to the application of the additional current 1, in order to correct this, the additional current 2 is applied radially inward from the first coil with respect to the central axis in the static magnetic field direction. ing. As a result, the additional current 1 and the additional current 2 can be combined to cancel the magnetic field generated on the inner side surface of the concave arrangement space, reduce the eddy current generated there, and change the gradient magnetic field generated in the imaging space. Can not be.

  FIG. 3 is a diagram of the main coil surface of the gradient magnetic field coil as viewed from the direction in which the static magnetic field is generated in the vertical magnetic field MRI apparatus according to the second embodiment of the present invention. However, although Example 1 is an example of a Z-axis gradient magnetic field coil whose shape of the coil is axisymmetric with respect to the Z-axis (the direction of the static magnetic field), Example 2 relates to the X-axis gradient magnetic field coil. This is an example, and only the upper right quadrant of the main coil surface surrounded by the X and Y axes is shown, and the others are omitted. 23a is a coil for flowing additional current 1, and 24a is a coil for flowing additional current 2. Reference numeral 13d denotes a conventional main coil pattern, which is shown in FIG. The horizontal axis is the X axis, and the vertical axis is the Y axis.

  According to this embodiment, in addition to the conventional main coil and shield coil, the additional current 1 is first applied to the main coil surface. Thereby, the magnetic field generated on the inner side surface of the concave arrangement space by the main coil and the shield coil can be canceled. On the other hand, since the gradient magnetic field is distorted in the imaging space by the application of the additional current 1, the additional current 2 is applied radially inward from the first coil with respect to the central axis in the static magnetic field direction in order to correct this. Further, the additional currents 1 and 2 are connected at the end 25a, and a loop is drawn together. As a result, the additional current 1 and the additional current 2 can be combined to cancel the magnetic field generated on the inner side surface of the concave arrangement space, reduce the eddy current generated there, and change the gradient magnetic field generated in the imaging space. Can not be.

  As in the first and second embodiments, by adding the additional currents 1 and 2, it is possible to reduce the magnetic field generated on the inner side surface of the concave arrangement space. The current density at the end of the coil surface increases, and the heat generated thereby increases. Therefore, it is desirable that the amount of the additional currents 1 and 2 be as small as possible. For this purpose, the additional current 1 is as close to the inner side surface of the concave arrangement space as possible, and the additional current 2 and the main coil are the inner side surfaces of the concave arrangement space. It should be placed away from

  FIG. 4 is a part of a cross section of a static magnetic field generation source and a gradient magnetic field coil of a vertical magnetic field MRI apparatus according to Embodiment 3 of the present invention. However, in Example 3, in order to alleviate heat generation due to the high current density in the outermost part of the main coil surface in Examples 1 and 2, the coil that passes additional currents 1 and 2 is connected to the main coil surface. And a third layer different from the shield coil surface. Further, the third embodiment is an example of a Z-axis direction gradient magnetic field coil in which the same coil shape as that of the first embodiment is axisymmetric with respect to the Z-axis (the direction of the static magnetic field). When viewed from the direction, the coils are arranged concentrically.

  4a is a side surface of the concave arrangement space, 4b is a bottom surface of the concave arrangement space, 13a is a shield coil surface of the gradient magnetic field coil, 13b is a main coil surface of the gradient magnetic field coil, and a symbol with a dot added at the center of the circle indicated by 21 Is the coil through which current flows from the back side of the paper, the symbol with a cross added to the circle indicated by 22 is the coil that flows from the front side of the paper to the back side, and the two rows of coils shown by 23b carry additional current 1 The two rows of coils indicated by 24b are coils for passing the additional current 2. Reference numeral 13c denotes a conventional shield coil pattern, and reference numeral 13d denotes a conventional main coil pattern, which are shown in FIG. 9 of Patent Document 2, respectively.

  In the present embodiment, similarly to the first and second embodiments, by combining the additional current 1 and the additional current 2, the magnetic field generated on the inner side surface of the concave arrangement space can be canceled, and the eddy current generated there can be reduced. In addition, it is possible to prevent the gradient magnetic field generated in the imaging space from changing. Further, in the present embodiment, the coil through which the additional currents 1 and 2 flow is provided in a third layer different from both the main coil surface and the shield coil surface, preferably between the main coil surface and the shield coil surface. A coil with a large area can be used as a coil for flowing the additional currents 1 and 2, and it is possible to mitigate heat generation due to high current density.

  FIG. 5 is a diagram of the gradient magnetic field coil as viewed from the direction of the static magnetic field in the vertical magnetic field MRI apparatus according to Embodiment 4 of the present invention. However, FIG. 5 shows only a part of the coil pattern to make the drawing easier to see, and Example 4 is an example of the X-axis direction gradient magnetic field coil. Reference numeral 13c denotes a conventional main coil pattern, and reference numeral 13d denotes a conventional shield coil pattern, which are shown in FIG. 9 of Patent Document 2, respectively. 23c is a coil for flowing additional current 1, and 24c is a coil for flowing additional current 2. In Example 4, the coil 23c for flowing the additional current 1 and the coil 24c for flowing the additional current 2 are arranged in the third layer between the surface of the main coil pattern and the surface of the shield coil pattern, and The additional currents 1 and 2 are connected at the end 25c, and a loop is drawn together.

  In the present embodiment, as in the first to third embodiments, by combining the additional current 1 and the additional current 2, the magnetic field generated on the inner side surface of the concave arrangement space can be canceled, and the eddy current generated there can be reduced. In addition, it is possible to prevent the gradient magnetic field generated in the imaging space from changing. Further, in the present embodiment, the coil through which the additional currents 1 and 2 flow is provided in a third layer different from both the main coil surface and the shield coil surface, preferably between the main coil surface and the shield coil surface. A coil with a large area can be used as a coil for flowing the additional currents 1 and 2, and it is possible to mitigate heat generation due to high current density.

  In the above Examples 1 to 4, the gradient magnetic field coil having a structure that suppresses the leakage magnetic field has been described, but even if the coil pattern is created with the above structure, it is not manufactured with mechanical accuracy as designed, As a result, sufficient magnetic field accuracy cannot be obtained. Embodiment 5 of the gradient coil that solves this will be described with reference to FIGS.

  In Example 5 shown in FIGS. 6 and 7, the coils are stacked with prepregs interposed therebetween, and alignment members are stacked in the thickness direction. Here, the prepreg means a mixture of a resin, an additive, and a fibrous or filamentary reinforcing material, and FIG. 6 is used to pass the additional current 1 and the additional current 2 as in Examples 1 and 2. 7 is arranged on the same surface as the main coil surface, as shown in FIG. 7 in the third and fourth embodiments, the coils for passing the additional current 1 and the additional current 2 are arranged between the main coil surface and the shield coil surface. The case where it is provided in a third layer different from both is shown.

  Stack the x, y, and z main coils and x, y, and z shield coils, or the x, y, and z main coils and the x, y, and z shield coils together in the thickness direction. When pressure is applied and heated to cure the prepreg, the thickness of the prepreg can be made constant and the coils can be configured rigidly. When heated from 120 ° C to 150 ° C at a pressure of about 4MPa, the thickness of the prepreg during curing can be managed with an accuracy of about several micrometers per layer, and the original adhesive strength of epoxy adhesives can be stabilized. Can be obtained.

  Any material can be used as the prepreg, but an insulating film such as polyethylene terephthalate is coated with an epoxy resin in a semi-cured state, a glass cloth is impregnated with an epoxy resin, and combinations thereof. Is effective for improving the insulation between the coils.

  A more detailed cross-sectional view is simply shown in FIG. According to FIG. 7, a lateral alignment member that uses a stacked structure as a skewer is used. This makes it possible to suppress lateral displacement. The structure shown in FIG. 7 allows alignment in each direction, so the gradient magnetic field coil can be structured by adding additional structural members or molding the gap with a resin such as epoxy resin or a solidified material such as cement. Can be completed. However, if molding is performed after putting an aggregate cheaper than the resin, the amount of expensive resin used can be reduced, and the resin can be manufactured at a low cost.

In addition, by separating the structural member and the alignment member functionally, the structural member does not require dimensional accuracy, so it is possible to easily use an inexpensive existing member without processing it. Therefore, it is possible to select a soft material from the viewpoint of workability.

  The present invention is not limited to the above-described embodiments, and various modifications can be made without departing from the spirit of the present invention. For example, in Examples 1 and 3, an example of a Z-axis gradient magnetic field coil is shown, and in Examples 2 and 4, an example of an X-axis gradient magnetic field coil is shown. However, the present invention can be applied to a Y-axis gradient magnetic field coil. Of course. Further, the present invention can be applied not only to gradient magnetic field coils but also to shim coils for correcting generated static magnetic fields and gradient magnetic fields. For example, since the shim coil may be configured to include a main and a shield coil as in the gradient magnetic field coil, the configurations as in the first to fourth embodiments are applicable. In addition, in a vertical magnetic field type MRI apparatus, a shim coil may be formed by stacking several layers of flat plates, and therefore the configuration as in the fifth embodiment can be applied to a shim coil. Further, in Example 5, the prepreg was used for fixing the gradient magnetic field coil, but using the prepreg for fixing the gradient magnetic field coil or shim coil has a concave arrangement space on the upper and lower surfaces of the coil container. Of course, it can be applied not only to the vertical magnetic field type MRI apparatus but also to the vertical magnetic field type MRI apparatus in which the upper and lower surfaces of the coil container are flat. A prepreg can be applied even when there is no coil to flow through, and an example is shown in FIG.

General MRI system configuration. FIG. 2 is a part of a cross section of a static magnetic field generation source and a gradient magnetic field coil of the vertical magnetic field type MRI apparatus according to Embodiment 1 of the present invention. The figure which looked at the main coil surface of the gradient magnetic field coil from the direction which a static magnetic field generate | occur | produces of the perpendicular magnetic field type | mold MRI apparatus which concerns on Example 2 of this invention. A part of cross section of a static magnetic field generation source and a gradient magnetic field coil of a vertical magnetic field type MRI apparatus according to Embodiment 3 of the present invention. The figure which looked at the gradient magnetic field coil from the direction which a static magnetic field generate | occur | produces of the perpendicular magnetic field type | system | group MRI apparatus which concerns on Example 4 of this invention. FIG. 6 is a diagram showing a state where a gradient magnetic field coil according to Example 5 of the present invention is assembled using a prepreg, and a coil for passing b additional current 1 and additional current 2 is arranged on the same plane as the main coil surface. The figure corresponding to a case. FIG. 6 is a diagram showing a state where a gradient magnetic field coil according to Example 5 of the present invention is assembled using a prepreg, and a coil for flowing b additional current 1 and additional current 2 is formed on a third layer that is not a main coil surface shield coil surface. The figure corresponding to the case where it has arrange | positioned. FIG. 7 is a more detailed cross-sectional view of a gradient coil according to Example 5 of the present invention. The figure which shows the example which applied the prepreg when there is no coil which sends additional current at all.

Explanation of symbols

4 Magnet for generating static magnetic field 4a Side surface of concave arrangement space 4b Bottom surface of concave arrangement space 13a Shield coil surface of gradient magnetic field coil 13b Main coil surface of gradient magnetic field coil 13c Conventional shield coil pattern 13d Conventional main coil pattern 21 Back side of paper A coil through which current flows from the front to the front 22 A coil through which current flows from the front to the back of the paper 23 A coil for flowing the additional current 1 24 A coil for flowing the additional current 2

Claims (4)

  A pair of static magnetic field generation sources disposed opposite to each other with a photographing space interposed therebetween, each provided with a concave arrangement space on the opposite surface side, and a static magnetic field generation means for generating a static magnetic field in the facing direction; A main coil that is disposed in the concave arrangement space and generates a magnetic field in the imaging space, and a magnetic field that is disposed between the main coil and the static magnetic field generation source and is generated on the opposite side of the imaging space. In the magnetic resonance imaging apparatus comprising a magnetic field generating coil having a shield coil for canceling the magnetic field, the magnetic field generating coil is a side surface in which the main coil and the shield coil are parallel to the static magnetic field direction of the concave arrangement space. A magnetic resonance imaging apparatus comprising a first coil for suppressing a magnetic field generated in the concave arrangement space.   A second coil for correcting a change in the magnetic field generated in the imaging space by the first coil is provided inside the first coil in the radial direction with respect to the central axis in the static magnetic field direction in the concave arrangement space. The magnetic resonance imaging apparatus according to claim 1.   3. The magnetic resonance imaging apparatus according to claim 2, wherein a position in a static magnetic field direction in which the first and second coils are arranged is the same as a position in a plane in which the main coil is arranged.   3. The position in the static magnetic field direction where the first and second coils are arranged is between a position of a plane where the main coil is arranged and a position of a plane where the shield coil is arranged. The magnetic resonance imaging apparatus described in 1.

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