JP2004344182A - Magnetic resonance imaging apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To easily carry out the wiring and maintenance thereof for feeding an electric current to a gradient magnetic field coil, etc. without affecting the imaging or without deteriorating the openability in a vertical magnetic field type MRI apparatus. <P>SOLUTION: A through hole for inserting the wiring is formed on a side or at the center of a recess for setting the gradient magnetic field gradient coil on a static magnetic field generating system, and the wire for feeding electric currents and a pipe for cooling the gradient magnetic field coil are inserted and fixed into the through hole. After that, the wire and the pipe are connected with a connection terminal mounted on a side or at the center of the gradient magnetic field coil. In another case, the wire and the pipe may be inserted and fixed into the through hole with the wire and the pipe being connected to the gradient magnetic field coil. <P>COPYRIGHT: (C)2005,JPO&NCIPI

Description

[0001]
TECHNICAL FIELD OF THE INVENTION
The present invention relates to a vertical magnetic field type magnetic resonance imaging (hereinafter, referred to as “MRI”) apparatus, and more particularly to a wiring for supplying a current to a gradient magnetic field coil or a high frequency magnetic field coil, and a refrigerant for cooling the gradient magnetic field coil. The present invention relates to a pipe fixing structure for supplying.
[0002]
[Prior art]
As the MRI apparatus, there are a cylindrical type of a horizontal magnetic field type and a facing type of a vertical magnetic field type as a method of generating a static magnetic field, and the facing type of a vertical magnetic field type is excellent in openness. Means for generating a static magnetic field include those using a normal magnet, a permanent magnet, and a superconducting magnet. A superconducting magnet is used to generate a high static magnetic field strength. Furthermore, in imaging, when receiving a nuclear magnetic resonance (hereinafter referred to as “NMR”) signal induced by irradiating the subject with an electromagnetic wave through a high-frequency magnetic field coil, the subject is subjected to a gradient magnetic field by applying a gradient magnetic field. Is given to the NMR signal.
[0003]
In the above-described vertical magnetic field type MRI apparatus, a pair of static magnetic field generating sources are generally arranged to face each other in the vertical direction, and the static magnetic field direction is orthogonal to the body axis direction of the subject. Therefore, the plate-shaped gradient magnetic field coils are arranged to face each other with a uniform static magnetic field region formed between both static magnetic field generation sources. Further, in an MRI apparatus using a superconducting magnet as a vertical magnetic field type static magnetic field generating source, the gradient magnetic field coil is disposed in a recess of the superconducting coil in order to enhance openness.
[0004]
Furthermore, in addition to the gradient magnetic field coil and the high frequency magnetic field coil, power is supplied through a static magnetic field generation system to supply current to the shim coil and the high frequency magnetic field coil for adjusting the uniformity of the static magnetic field and to supply the refrigerant for cooling the inside of the gradient magnetic field coil. It is necessary to connect wiring and piping from the device and the refrigerant circulation device. Specifically, it is necessary to connect about 6 to 10 cables or pipes having an outer diameter of φ10 to 30 mm. However, if the wires or pipes are fixed on the open side, the openness of the MRI apparatus is lost.
[0005]
Known examples that solve the above problem include [Patent Document 1] and [Patent Document 2]. In [Patent Document 1], wiring is fixed through a notch provided in a pole piece. Further, in [Patent Document 2], the wiring is wired via a central hole of the static magnetic field generator.
[0006]
[Patent Document 1]
Japanese Patent Application No. 2001-240937 [Patent Document 2]
Japanese Patent Application No. 2000-243058
[Problems to be solved by the invention]
In Patent Literature 1, when a notch is provided in a pole piece, the amount of the magnetic material in the notch portion is reduced, so that the uniformity of the static magnetic field is reduced. Further, it is not easy to provide a notch on the open side of the superconducting coil container, and there is no space for notching. In Patent Literature 2, the wiring is taken out to the outside via a hole in the center of the superconducting coil, so that the wiring generates vibration due to Lorentz force. Since the vibration adversely affects the image, the wiring must be firmly fixed, but no specific fixing method is disclosed.
[0008]
Accordingly, the present invention provides a vertical magnetic field type MRI apparatus for supplying current to a gradient magnetic field coil, a high frequency magnetic field coil, a shim coil and receiving an echo signal without affecting imaging and without impairing openness. Wiring and piping for supplying coolant for cooling the gradient magnetic field coil can be easily fixed and connected to each other, and the gradient magnetic field coil, high frequency magnetic field coil, and shim coil can be easily attached and detached during maintenance. The purpose is to:
[0009]
[Means for Solving the Problems]
In order to solve the above problems, the present invention is configured as follows.
(1) A static magnetic field generating system including a pair of static magnetic field generating sources that form a uniform static magnetic field region in a space therebetween and a shim coil that adjusts the uniformity of the static magnetic field, and opposing the static magnetic field generating system. In a magnetic resonance imaging apparatus including a pair of gradient magnetic field coils opposed to each other with a uniform static magnetic field region on the surface side and a high frequency magnetic field coil for generating a high frequency magnetic field and inducing a magnetic resonance phenomenon in a subject,
The gradient magnetic field coil includes a current receiving terminal,
The static magnetic field generation system includes a recess for accommodating the gradient magnetic field coil, and a through hole penetrating the opposite surface side and the opposite surface side.
Wiring for supplying current to the gradient coil is fixed in the through hole,
The wiring includes a current supply terminal on the gradient magnetic field coil side,
Connecting the current receiving terminal and the current supplying terminal,
The gradient magnetic field coil is fixed to a recess of the static magnetic field generation system.
(2) Also, preferably, in the above (1), wiring for supplying a current to the high-frequency magnetic field coil and the shim coil, and wiring for transmitting an echo signal received by the high-frequency coil, It is fixed in the through hole.
(3) Preferably, in the above (1) or (2), the gradient magnetic field coil has at least one or more current receiving terminals on a substantially side surface thereof, and the static magnetic field generating system has At least one or more of the through holes are provided on substantially the side surface of the recess.
(4) Preferably, in the above (1) or (2), the gradient magnetic field coil has at least one or more current receiving terminals substantially at the center of the side opposite to the uniform static magnetic field side. And the static magnetic field generation system includes at least one or more of the through holes substantially at the center of the recess.
(5) Preferably, in the above (1) or (2) or (3) or (4), a cushion material is filled in a gap between the through hole and the wiring, so that the through hole is formed. Fix the wiring in the hole.
(6) Preferably, in (3), the wiring is fixed in the through-hole by filling and curing a liquid fixing agent in a gap between the through-hole and the wiring.
(7) Preferably, in (3), the wiring is fixed to a linear guide, a rail for guiding the guide is provided in the through hole, and the guide is placed along the rail. A magnetic resonance imaging apparatus wherein the wiring is fixed in the through hole by inserting and fixing.
(8) Further, preferably, in the above (1) or (2) or (3) or (4), one of the current supply terminal and the current supply / reception terminal has a depression, The other is provided with a projection inserted into the depression, and the gradient coil is connected to the wiring by inserting the projection into the depression.
(9) Preferably, in the above (3), each of the current receiving terminal and the current supplying terminal is provided with a hole for bolting each other, and the current receiving terminal and the current supplying terminal are provided with holes for bolting each other. The gradient magnetic field coil and the wiring are connected by bolting.
(10) Preferably, in (1), (2), (3), or (4), one of a pair of connectors that are in electrical contact with each other is used for receiving the current. A terminal is provided, and the other is provided by the current supply terminal, and the pair of connectors are connected to connect the gradient magnetic field coil to the wiring.
(11) Preferably, a static magnetic field generating system including a pair of static magnetic field generating sources which are arranged opposite to each other to form a uniform static magnetic field region in a space therebetween and a shim coil for adjusting the uniformity of the static magnetic field; A magnetic resonance system including a pair of gradient magnetic field coils opposed to each other across a uniform static magnetic field region on the opposite surface side of a magnetic field generation system and a high frequency magnetic field coil for generating a high frequency magnetic field and inducing a magnetic resonance phenomenon in a subject. In an imaging device,
The gradient magnetic field coil includes a refrigerant receiving terminal,
The static magnetic field generation system includes a recess for accommodating the gradient magnetic field coil, and a through hole penetrating the opposite surface side and the opposite surface side.
In the through hole, a pipe for supplying a refrigerant to the gradient magnetic field coil side is fixed,
The pipe includes a refrigerant supply terminal on the side of the gradient magnetic field coil,
Connecting the refrigerant supply terminal and the refrigerant reception terminal,
The gradient magnetic field coil is fixed to a recess of the static magnetic field generation system.
(12) Preferably, in the above (11), the gradient magnetic field coil has at least one or more refrigerant receiving terminals on a substantially side surface thereof, and the static magnetic field generating system has a structure in which the recess is substantially formed. At least one through hole is provided on a side surface.
(13) Preferably, in the above (11), the gradient magnetic field coil has at least one or more refrigerant supply terminals substantially at the center of a side opposite to the uniform static magnetic field side, and The generating system includes at least one or more of the through holes substantially at the center of the recess.
(14) Preferably, in the above (11), one of the refrigerant supply terminal and the refrigerant supply / reception terminal has a depression, and the other has a projection inserted into the depression, and The gradient coil is connected to the pipe by being inserted into the depression.
(15) Preferably, in the above (11), one of the pair of connectors for transporting the refrigerant to each other is provided with the refrigerant receiving terminal, and the other is provided with the refrigerant supplying terminal. The gradient coil and the pipe are connected by connecting a pair of connectors.
[0010]
Thereby, in the MRI apparatus, the wiring for supplying current to the gradient magnetic field coil, the high frequency magnetic field coil, the shim coil and receiving the echo signal, and supplying the coolant for cooling the gradient magnetic field coil without impairing the openness. The pipes can be easily fixed and connected to each other easily, and the gradient coil, the high-frequency magnetic field coil, and the shim coil can be easily attached and detached during maintenance.
[0011]
BEST MODE FOR CARRYING OUT THE INVENTION
Hereinafter, embodiments of the present invention will be described with reference to the accompanying drawings. In all the drawings for describing the embodiments of the present invention, components having the same functions are denoted by the same reference numerals, and their repeated description will be omitted.
[0012]
First, a basic outline of the MRI apparatus will be described with reference to FIG. The MRI apparatus obtains a tomographic image of a subject using a nuclear magnetic resonance phenomenon, and includes a static magnetic field generating system 1, a gradient magnetic field coil 2, and a high frequency magnetic field coil 3, as shown in FIG. Is done.
[0013]
The static magnetic field generating system 1 includes a pair of static magnetic field generating sources which are arranged to face each other up and down to form a uniform static magnetic field region 50, and a shim coil (not shown) for adjusting the uniformity of the static magnetic field. A superconducting magnet, a normal conducting magnet, or a permanent magnet is used as the static magnetic field generation source. In the case of a superconducting magnet, a superconducting coil in which a superconducting material is wound into a coil shape is accommodated in a cryocontainer made of stainless steel or GFRP.
[0014]
A subject (not shown) lies on a bed (not shown) and is arranged in the uniform static magnetic field region 50. The gradient magnetic field coils 2 are arranged vertically opposite to each other with the uniform static magnetic field region 50 interposed therebetween, and are fixed in a recess of the static magnetic field generation system 1 on the side of the uniform static magnetic field region 50. The high-frequency magnetic field coil 3 is disposed to face up and down with the uniform static magnetic field area 50 interposed therebetween, and is fixed to the uniform static magnetic field area 50 side (that is, the innermost side) of the gradient magnetic field coil 2.
[0015]
The gradient magnetic field coil 2 is composed of three coils to generate gradient magnetic fields in three axial directions orthogonal to each other. Each coil is connected to a gradient magnetic field power supply 31 and supplied with a drive current. The gradient magnetic field coil 2 is attached to a fixed stud (pedestal) (not shown) provided in the static magnetic field generation system 1.
[0016]
The high frequency magnetic field coil 3 is connected to a transmitter 32, and the transmitter 32 sends a high frequency current to the high frequency magnetic field coil 3 to generate a high frequency magnetic field. The high frequency magnetic field coil 3 is also connected to a receiver 33, and the receiver 33 receives the NMR signal from the subject through the high frequency magnetic field coil 3. The NMR signal obtained by the receiver 33 is sent to a data processor 34, where signal processing for obtaining a reconstructed image is performed.
[0017]
The controller 30 controls the gradient magnetic field power supply 31, the transmitter 32, and the receiver 33 to operate at appropriate timing.
[0018]
Next, a first embodiment according to the present invention will be described with reference to FIG.
In the static magnetic field generation system 1, at least one or more (two in FIG. 1 two on each side) through holes 5 are provided near the side surface of the central recess 4, that is, near the side surface of the gradient magnetic field coil. It is tied and opened. The cross-sectional shape of the hole may be any of a circle, a square, an ellipse, and the like.
[0019]
FIG. 2 shows a structure for fixing the wiring of the gradient magnetic field coil and the high frequency magnetic field coil. At the time of assembling the static magnetic field generating system, the wiring 6 is passed through the through-hole, the liquid waste 7 is arranged below the hole, and a fixing agent (eg, resin or foaming agent) 8 is poured from above and cured to fix the wiring. The liquid damper 7 may be a resin or a polymer material such as silicone rubber, and preferably has a high airtightness.
[0020]
Further, as shown in FIG. 3, the wiring 6 may be fixed to a cushion material (for example, cork, cushioning material) 9 whose outer diameter is previously processed into a hole shape, and the cushion material may be inserted into the hole. The cushion material 9 may be fixed by applying an adhesive on the outer surface of the cushion material in advance, or by pouring the adhesive after the insertion.
[0021]
Further, as shown in FIG. 4, the wiring 6 may be fixed to a linear guide 21. On the other hand, a rail 22 for guiding the guide 21 is provided in the through hole 5. As a result, the guide to which the wiring is fixed is guided along the rail 22, and the guide 21 is fixed at a predetermined position.
[0022]
FIG. 5 shows a structure for connecting the wiring 6 and a terminal from the gradient coil. FIG. 6 is a view of FIG. 5 as viewed from above. The terminal 10 is a current supply terminal attached to the end of the wiring from the static magnetic field generation system side, and the terminal 11 is a current supply terminal coming out of the gradient magnetic field coil. Since it can be accessed from above as shown in FIG. 6, visibility is good, and fastening with the bolt 12 is easy. Further, since the wiring can be separated from the wiring simply by removing the bolt, the mounting and dismounting of the gradient magnetic field coil become easy.
[0023]
Further, the terminals may not be fastened by bolts as shown in FIG. 5 but may be simply brought into electrical contact using a connector. As an example, FIG. 7 shows an example of a current supply terminal 13 and a current reception terminal 14 using a connector (for example, a “fork plug” manufactured by Multi Contact).
[0024]
The above is the first embodiment, but as a second embodiment based on FIG. 1, wiring 6 is attached to the gradient magnetic field coil 2 in advance, and when the gradient magnetic field coil 2 is A method of fixing the through holes 6 to the through holes 5 will be described.
The wiring 6 drawn from the gradient magnetic field coil 2 passes through the through hole 5 at the time of attachment. As a method, a rod-shaped material serving as a guide 21 is temporarily fixed to a cable, and the guide 21 is passed through a rail 22 provided in a through hole. Next, the liquid waste is arranged below the through hole 5, and the fixing agent 8 is poured from above and cured.
[0025]
Alternatively, it is also possible to pass through the through-hole only with the guide without using the rail, dispose the liquid dam below the through-hole 5, and pour the fixing agent 8 from above to harden. Alternatively, the wire 6 may be temporarily fixed to the end of the guide, and the guide may be removed after guiding the through hole.
[0026]
Next, a third embodiment according to the present invention will be described with reference to FIG.
In the static magnetic field generation system 1 of FIG. 8, at least one (one in FIG. 8) through-hole 5 is formed in the center of the central recess 4 by connecting the opposite surface side to the opposite surface side. The configuration other than the connection terminals is the same as that of FIG. 1 of the first embodiment.
[0027]
FIG. 9 shows a structure for connecting the wiring 6 and a terminal from the gradient coil 2. The terminal 15 is a current supply terminal attached to the tip of the wiring from the static magnetic field generation system side, and has a depression. Here, the shape of the depression is circular, but need not be circular in particular, and may be polygonal. The terminal 16 is a current receiving terminal coming out of the gradient magnetic field coil 2, and has a projection inserted into a circular recess of the terminal 15. Then, the gradient coil 2 is connected to the wiring 6 by inserting the current receiving terminal 16 into the current supplying terminal 15. By doing so, wiring can be connected at the center of the static magnetic field generation system 1 and removal becomes easy. As a specific example of such a connector, "B10N socket" and "S10N plug" manufactured by Multi Contact Co., Ltd. can be used. Further, a lock type connector (for example, “B10AR-N socket” and “S10AR-N plug” manufactured by Multiconnector) or a connector as shown in FIG. 7 that can be connected in the vertical direction may be used. .
[0028]
The above is the third embodiment. As a fourth embodiment based on FIG. 8, the wiring 6 is attached to the gradient magnetic field coil 2 in advance in the third embodiment, and the gradient magnetic field coil 2 is attached to the static magnetic field generation system 1. A method of fixing the wiring 6 to the through hole 5 when attaching the wiring 6 will be described.
The wiring 6 drawn from the gradient magnetic field coil 2 passes through the through hole 5 at the time of attachment. As shown in FIG. 10, as a method, a cushion material 17 having an outer diameter previously processed into a hole shape is fixed to the wiring 6, and the cushion material 17 is inserted into the hole. The cushion member 17 is fixed to an adhesive previously applied to the outer surface of the cushion member.
[0029]
In the above, the wiring to the gradient magnetic field coil has been described. However, the wiring to the high frequency magnetic field coil and the shim coil can be similarly connected to each other. At this time, a plurality of through holes may be provided, and the individual holes may be passed through the through holes individually or in groups. Alternatively, all necessary wirings can be bundled and fixed to the through hole in a state of being united.
[0030]
Next, fixing of a pipe for supplying a coolant for cooling the gradient coil will be described.
FIG. 11 shows a structure in which the piping and the terminals from the gradient coil are connected at the side of the gradient coil. The terminal 100 is a refrigerant supply terminal attached to the tip of the pipe from the static magnetic field generation system side, and the terminal 101 is a refrigerant supply terminal coming out of the gradient magnetic field coil.
The pipe and the terminal are provided with a hollow through hole. The shape may be a square or a circle. The distal end protrusion of the coolant supply terminal 100 is inserted into a recess provided in the coolant supply terminal 101. By using a lock-type connector 102 as shown in FIG. 12 for these terminals, attachment and detachment becomes possible.
[0031]
Alternatively, as shown in FIG. 13, when the refrigerant supply terminal 100 is omitted and a rubber tube 105 is used for external piping, the piping is fixed by tightening the fixing band 103 with the screw 104. Is also good. As an example of such a terminal, "Quick Release Coupling" manufactured by Stäubli can be used.
[0032]
Alternatively, when a non-magnetic metal material (brass, stainless steel, or the like) is used for the refrigerant supply terminal 100 and the refrigerant reception terminal 101, they may be fixed by brazing. Alternatively, as shown in FIG. 14, a swage lock type connector for fixing the pipe and the terminal by rotating the nut 106 may be used.
[0033]
With the configuration described above, the gradient magnetic field coil can be cooled by circulating the refrigerant (liquid or gas) in the tube and cooling the refrigerant outside the gradient magnetic field coil. Furthermore, when a conductive material is used for the pipe and the terminal, a current from a power supply can be connected to the pipe to supply a current to the gradient magnetic field coil.
The above is the structure in the case where the connection is made at the side of the gradient magnetic field coil. However, the structure can be applied to the center as shown in FIG.
[0034]
【The invention's effect】
According to the present invention, in an MRI apparatus, a gradient magnetic field coil, a high-frequency magnetic field coil, a wiring for performing current supply to a shim coil and reception of an echo signal, and a refrigerant for cooling the gradient magnetic field coil without impairing openness. The supply pipes can be easily fixed and connected to each other, and the gradient coil, the high-frequency magnetic field coil, and the shim coil can be easily attached and detached during maintenance.
[Brief description of the drawings]
FIG. 1 is a diagram showing a magnetic resonance imaging apparatus according to a first embodiment.
FIG. 2 is a diagram showing a wiring fixing structure (fixing agent method) according to the first embodiment.
FIG. 3 is a view showing a wiring fixing structure (cushion method) according to the first embodiment;
FIG. 4 is a view showing a wiring fixing structure (guide-rail system) according to the first embodiment;
FIG. 5 is a diagram showing a terminal connection method according to the first embodiment.
FIG. 6 is a diagram showing the upper surface of FIG. 5 of the first embodiment.
FIG. 7 is a diagram showing a terminal connection method according to the first embodiment.
FIG. 8 is a diagram illustrating a magnetic resonance imaging apparatus according to a third embodiment.
FIG. 9 is a diagram illustrating a terminal connection method according to a third embodiment.
FIG. 10 is a diagram showing a terminal connection method according to a fourth embodiment.
FIG. 11 is a diagram showing a method of connecting terminals of piping on substantially the side surface of the recess.
FIG. 12 is a diagram showing a method of connecting pipes using a lock-type connector.
FIG. 13 is a diagram showing a method of connecting pipes using a rubber tube.
FIG. 14 is a diagram showing a method of connecting pipes using a swagelok type connector.
FIG. 15 is a diagram showing a method of connecting terminals of piping substantially at the center of the recess.
[Explanation of symbols]
1 static magnetic field generation system, 2 gradient magnetic field coil, 3 high frequency magnetic field coil, 4 central recess, 5 through hole, 6 wiring, 7 liquid dam, 8 fixing agent, 9 cushion material, 10 current supply terminal, 11 current receiving terminal, 12 volt, 13 current supply terminal, 14 current reception terminal, 15 current supply terminal, 16 current reception terminal, 17 cushion material, 21 guide, 22 rail, 30 controller, 31 gradient power supply, 32 transmitter, 33 receiver, 34 data processor, 50 uniform static magnetic field area, 100 piping terminal, 101 piping terminal, 102 locking connector, 103 fixing band, 104 screw, 105 rubber tube, 106 nut

Claims (15)

A static magnetic field generating system including a pair of static magnetic field generating sources for forming a uniform static magnetic field region in a space between the static magnetic fields and a shim coil for adjusting the uniformity of the static magnetic field; In a magnetic resonance imaging apparatus including a pair of gradient magnetic field coils opposed to each other with a uniform static magnetic field region interposed therebetween, and a high frequency magnetic field coil for generating a high frequency magnetic field to induce a nuclear magnetic resonance phenomenon in a subject,
The gradient magnetic field coil includes a current receiving terminal,
The static magnetic field generation system includes a recess for accommodating the gradient magnetic field coil, and a through-hole penetrating the opposite surface side and the opposite surface side.
Wiring for supplying current to the gradient coil is fixed in the through hole,
The wiring includes a current supply terminal on the gradient magnetic field coil side,
Connecting the current receiving terminal and the current supplying terminal,
A magnetic resonance imaging apparatus, wherein the gradient magnetic field coil is fixed to a recess of the static magnetic field generation system. 2. The device according to claim 1, wherein a wire for supplying a current to the high-frequency magnetic field coil and the shim coil, and a wire for transmitting an echo signal received by the high-frequency coil are fixed in the through hole. A magnetic resonance imaging apparatus. 3. The gradient magnetic field coil according to claim 1, wherein the gradient magnetic field coil has at least one or more current receiving terminals on a substantially side surface thereof, and the static magnetic field generating system has at least one or more current receiving terminals on a substantially side surface of the recess. A magnetic resonance imaging apparatus comprising the through hole. The gradient magnetic field coil according to claim 1 or 2, wherein the gradient magnetic field coil includes at least one or more current receiving terminals substantially at a center of a side opposite to a side of the uniform static magnetic field, and the static magnetic field generating system includes: A magnetic resonance imaging apparatus comprising at least one or more through-holes substantially at the center of a recess. 5. The wiring according to claim 1, wherein the wiring is fixed in the through hole by filling a cushion material in a gap between the through hole and the wiring. Magnetic resonance imaging device. 4. The magnetic resonance imaging apparatus according to claim 3, wherein the wiring is fixed in the through-hole by filling and curing a liquid fixing agent in a gap between the through-hole and the wiring. 4. The method according to claim 3, wherein the wiring is fixed to a linear guide, a rail for guiding the guide is installed in the through hole, and the guide is inserted and fixed along the rail. A magnetic resonance imaging apparatus characterized in that the wiring is fixed in the through hole. Claim 1 or Claim 2, Claim 3 or Claim 4, wherein one of the current supply terminal and the current supply / reception terminal has a depression, and the other has a projection inserted into the depression. The magnetic resonance imaging apparatus, wherein the gradient magnetic field coil and the wiring are connected by inserting the projection into the depression. 4. The gradient magnetic field according to claim 3, wherein each of the current receiving terminal and the current supplying terminal is provided with a hole for bolting each other, and bolted through the bolt fastening hole. A magnetic resonance imaging apparatus, wherein a coil and the wiring are connected. In Claim 1, Claim 2, Claim 3, or Claim 4, one of the pair of connectors that are in electrical contact with each other is provided with the current receiving terminal, and the other is provided with the current supplying terminal. A magnetic resonance imaging apparatus comprising: connecting the pair of connectors to connect the gradient magnetic field coil and the wiring. A static magnetic field generating system including a pair of static magnetic field generating sources for forming a uniform static magnetic field region in a space between the static magnetic fields and a shim coil for adjusting the uniformity of the static magnetic field; In a magnetic resonance imaging apparatus including a pair of gradient magnetic field coils opposed to each other with a uniform static magnetic field region interposed therebetween and a high frequency magnetic field coil for generating a high frequency magnetic field and inducing a magnetic resonance phenomenon in a subject,
The gradient magnetic field coil includes a refrigerant receiving terminal,
The static magnetic field generation system includes a recess for accommodating the gradient magnetic field coil, and a through-hole penetrating the opposite surface side and the opposite surface side.
In the through hole, a pipe for supplying a refrigerant to the gradient magnetic field coil is fixed,
The pipe includes a refrigerant supply terminal on the side of the gradient magnetic field coil,
Connecting the refrigerant supply terminal and the refrigerant reception terminal,
A magnetic resonance imaging apparatus, wherein the gradient magnetic field coil is fixed to a recess of the static magnetic field generation system. 12. The gradient magnetic field coil according to claim 11, wherein the gradient magnetic field coil has at least one or more refrigerant receiving terminals on substantially a side surface thereof, and the static magnetic field generation system has at least one or more of the through holes on substantially a side surface of the recess. A magnetic resonance imaging apparatus comprising: 12. The gradient magnetic field coil according to claim 11, wherein the gradient magnetic field coil has at least one or more refrigerant supply terminals substantially at the center of a side surface opposite to the uniform static magnetic field side surface, and the static magnetic field generation system is substantially at the center of the recess. A magnetic resonance imaging apparatus comprising at least one through hole. The method according to claim 11, wherein one of the refrigerant supply terminal and the refrigerant supply / demand terminal has a depression, and the other has a projection inserted into the depression, and the projection is inserted into the depression, A magnetic resonance imaging apparatus, wherein a gradient magnetic field coil and the pipe are connected. In Claim 11, one of the pair of connectors for transporting the refrigerant to each other is provided by the refrigerant receiving terminal, and the other is provided by the refrigerant supply terminal, and the pair of connectors is connected to each other. A magnetic resonance imaging apparatus, wherein the gradient magnetic field coil and the pipe are connected.

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