JP3578295B2 - Open magnetic resonance imaging system - Google Patents

Description

[0001]
TECHNICAL FIELD OF THE INVENTION
The present invention relates to a magnetic resonance imaging apparatus (hereinafter, referred to as an MRI apparatus) using a cylindrical or cylindrical open superconducting magnet, and particularly to an MRI apparatus in which wiring is performed so as not to impair the feeling of opening.
[0002]
[Prior art]
An MRI apparatus using a superconducting magnet generally has a cylindrical structure and is not an open type. For this reason, the point to be considered in wiring of the MRI apparatus is mainly to eliminate noise. Open-type MRI apparatuses have been put into practical use with relatively low static magnetic field strength using permanent magnets or normal conducting magnets, but all have large fluctuations in characteristics depending on the environmental temperature of the installation place. In the case of the permanent magnet, a space for the heat insulating cover of 50 to 100 mm is provided. Therefore, the wiring to the MRI apparatus is sufficiently processed inside the space for the heat insulating cover. On the other hand, the superconducting magnet does not require the space for the heat insulating cover, so that a new space and processing for wiring are required.
[0003]
[Problems to be solved by the invention]
In an open-type MRI apparatus using a superconducting magnet, a problem is how to secure the degree of opening of the apparatus, which is a feature of the apparatus. In an open-type MRI apparatus, two superconducting magnets are arranged facing each other around a measurement area, and both superconducting magnets are supported by columns. Therefore, in order to secure the degree of opening of the MRI apparatus, it is effective to reduce the diameter of the superconducting magnet as much as possible, minimize the number of the columns, and reduce the diameter of the columns. However, even if these are realized as a superconducting magnet, the degree of opening secured above may be reduced unless sufficient consideration is given to wiring to devices attached to the superconducting magnet. In addition, the facing distance between the magnets must be increased depending on the manner in which the wiring cables are routed based on the power handled by the MRI apparatus.
Therefore, an object of the present invention is to solve these problems and to provide an MRI apparatus provided with wiring that does not impair the degree of opening.
[0004]
[Means for Solving the Problems]
The object of the present invention is achieved by the following solution.
The open type MRI apparatus according to the present invention comprises an upper superconducting magnet and a lower superconducting magnet which are vertically opposed to each other with a measurement area as a center, a gradient magnetic field coil installed on the opposing surfaces of the two magnets, and an irradiation high frequency. A coil, a table on which a subject is placed and inserted into the measurement area, a high-frequency receiving coil for receiving a magnetic resonance signal from the subject, and an operation display unit for operating these coils A power supply device for disposing an MRI apparatus main body in a shield room provided with a radio wave shield or a radio wave and an electromagnetic shield, and supplying power to the MRI apparatus main body and equipment constituting the MRI apparatus main body installed outside the shield room In an open-type MRI apparatus in which wiring is connected between a console for operating and controlling the main body of the MRI apparatus via a filter provided on an outer wall of the shield room, The wiring is divided into an upper superconducting magnet side wiring and a lower superconducting magnet side wiring, the upper superconducting magnet side wiring is introduced from a filter provided on the ceiling side of the shield room, and the lower superconducting magnet side wiring is connected to the shield room. The MRI apparatus is introduced through a filter provided on a lower side surface of the MRI apparatus, and is connected to equipment constituting the MRI apparatus main body (claim 1).
In this configuration, the wiring between the MRI apparatus main body arranged in the shield room and the power supply device etc. arranged outside the shield room is divided into two parts based on the upper superconducting magnet and the lower superconducting magnet constituting the MRI apparatus main body. Since the measurement is performed separately, there is no wiring around the measurement area, and even in an MRI apparatus using a superconducting magnet with high magnetic field strength, a feeling of openness equivalent to that of an MRI apparatus using a permanent magnet can be obtained. Can be.
[0005]
The open type MRI apparatus of the present invention includes an upper superconducting magnet and a lower superconducting magnet arranged to face each other in the vertical direction with the measurement area as a center, a support supporting the upper superconducting magnet, and a facing surface of the two magnets. An installed gradient magnetic field coil and an irradiation high-frequency coil, a table on which the subject is placed and inserted into the measurement area, a reception high-frequency coil for receiving a magnetic resonance signal from the subject, An operation display unit for operating the MRI apparatus main body is disposed in a shield room provided with a radio wave shield or a radio wave and an electromagnetic shield, and electric power is supplied to equipment constituting the MRI apparatus main body, which is installed outside the shield room. Wiring is provided between a power supply device to be supplied and a console for operating and controlling the MRI apparatus main body and the MRI apparatus main body via a filter provided on an outer wall of the shield room. In the continuous open-type MRI apparatus, all wirings are collectively introduced from a filter provided on a lower side surface of the shield room, and divided into an upper superconducting magnet side wiring and a lower superconducting magnet side wiring in the shield room, The upper superconducting magnet side wiring is connected from the lower superconducting magnet side to the upper superconducting magnet side along the outer periphery of the column (claim 2).
In this configuration, after the wiring of the MRI apparatus main body arranged in the shield room and the power supply device arranged outside the shield room are collectively introduced into the shield room, the upper superconducting magnet side wiring is separated. The wiring is performed along the columns, so that the wiring is performed without impairing the open feeling of the MRI apparatus.
[0006]
In the open-type MRI apparatus of the present invention, wiring at the upper superconducting magnet portion and the lower superconducting magnet portion and / or the wiring at the support portion is further provided with an electrostatic shield composed of a duct and a duct cover. 3).
In this configuration, by applying an electrostatic shield composed of a duct and a duct cover to the wiring at the superconducting magnet and the column, the penetration of noise into the measurement signal is reduced and the appearance is improved.
[0007]
In the open-type MRI apparatus of the present invention, a wiring in the upper superconducting magnet portion and the lower superconducting magnet portion of the gradient magnetic field coil, and / or a bus bar-shaped conductor made of a highly conductive metal material may be used. (Claim 4).
In this configuration, the wiring to the gradient magnetic field coil is made of a busbar-shaped conductor to reduce the intrusion of noise into the measurement signal when a large power of a pulse waveform is supplied.
[0008]
BEST MODE FOR CARRYING OUT THE INVENTION
Hereinafter, embodiments of the present invention will be described with reference to the accompanying drawings.
FIG. 1 shows an example of the configuration of an open type MRI apparatus using the superconducting magnet of the present invention. FIG. 1A is a view of the superconducting magnet 2 and the table 3 of the MRI apparatus main body 1 of the present invention as viewed from above. The MRI apparatus main body 1 is arranged in the shield room 4 in such an arrangement. A compressor 6 connected to a refrigerator 5 for cooling the superconducting magnet 2 is installed outside the shield room 4. FIG. 1B shows an example of a state where the superconducting magnet 2 and the table 3 are installed in a shield room 4 provided with an electrostatic or electrostatic and electromagnetic shield. In FIG. 1B, the superconducting magnet 2 is composed of a magnet (upper) 2A and a magnet (lower) 2B. An examinee is placed on the table 3, and a high-frequency receiving coil (hereinafter, referred to as an RF coil) 8 is attached to the table 3 and sent to a measurement area 7 inside the superconducting magnet. On the opposing surfaces of the magnet (upper) 2A and the magnet (lower) 2B, gradient magnetic field coils (hereinafter, referred to as GC) (upper), (lower) 9A, 9B and irradiation high-frequency coils (upper), (lower) ( Hereinafter, RF (upper) and (lower) are attached. 10A and 10B are attached, and a series of measurements are performed as an MRI apparatus.
[0009]
As is clear from FIG. 1 (B), the subject is set in the measurement area 7 between the magnet (upper) 2A and the magnet (lower) 2B by operating the operation display unit 11. Is desirably configured not to exist. However, at least two support columns 12 for supporting the magnet (upper) 2A are required, and it is important to make this as thin as possible. In addition, the inside of the column 12 is usually configured to pass a cryogen or a cooling structure for cooling the superconducting magnet 2 and a wire.
[0010]
For the device in FIG. 1B, there are various units shown in FIG. 1C, and a wiring (including a flexible hose) 13 is provided between these units and the device. . In FIG. 1C, the power supply unit 14 has a role of distributing and supplying AC power to each device, and receives a tributary voltage V _AC1 (including a ground potential) collectively from the outside as a whole, This was converted and distribution into an AC voltage V _AC2 ~V _AC6 required via an isolation transformer, Furthermore, the console 15 is connected via an instruction signal C _1, having the sequence operation function when the normal time abnormality. The RF unit 16 is a power supply for irradiating a subject with a high frequency (hereinafter, referred to as RF). The RF unit 16 mainly includes an amplifier (several kW to several tens of kW), a power supply to the amplifier, a control circuit, and a state management circuit. is configured, the console 15 is connected with a command signal C _2. The GC unit 17 is a power supply for the GC, and further has a function of designating a measurement point of the subject. The GC unit 17 is composed of an amplifier (several tens of kW), a power supply to the amplifier, a control circuit, and a state management circuit. the console 15 is connected via an instruction signal C _3.
[0011]
The console 15 includes a function of capturing a received signal from the RF coil 8 (the received signal may be transmitted through the RF unit 16). The console 15 controls the overall operation, and includes a computer, including an operation, an image processing, and a display function. It consists of the input / output display device. Signal _C RF from RF unit 16, the signal _{C GC} from GC unit 17, the signal _{C O} from console 15, and since all such tables lighting voltage _{V AC5} is intended properties to be incorporated into the shield room 4, The shield room 4 is guided into the shield room 4 via either the filter (upper) 19A or the filter (lower) 19B provided at the lower part of the ceiling 18 and the side surface. The flexible hose 20 from the compressor 6 to the refrigerator 5 of the superconducting magnet 2 and the valve motor cable 21 are also connected to the refrigerator 5 via either the filter (upper) 19A or the filter (lower) 19B.
[0012]
FIG. 2 shows an example of wiring processing to an MRI apparatus using a superconducting magnet in a shield room in the above configuration example. In FIG. 2, the wiring taken into the shield room 4 via the filter (upper) 19A provided on the ceiling 18 of the shield room 4 is connected to the magnet (upper) 2A side, The wiring taken into the shield room 4 via the provided filter (bottom) 19B is connected to the magnet (bottom) 2B and the table 3, and is divided into two groups. It is appropriate to make a connection corresponding to that outside of the device. In the example of FIG. 2, the refrigerator 5 attached to the magnet (upper) 2A, the helium level meter 22, the GC (upper) 9A, the RF (upper) 10A, the operation display unit 11, and the wiring to the shield room lighting 23 are filtered. The wiring to the RF (bottom) 10B, the GC (bottom) 9B, the RF coil 8, the table 3, and the outlet 24 in the shield room is introduced into the shield room 4 via the filter (bottom) 19B via the (top) 19A. Have been. Each of the filters (upper) and (lower) 19A, 19B is composed of a filter element 25 provided for each wiring.
[0013]
Next, a specific example of how the wiring divided into two groups as described above is connected to the MRI apparatus main body 1 in the shield room 4 will be described with reference to FIG. The problem in FIG. 3 is that the GCs (upper), (lower) 9A, 9B, RF (upper), (lower) 10A, 10B attached to the facing surfaces of the magnets (upper), (lower) 2A, 2B Cable processing. RF (top), (lower) 10A, 10B is the high frequency of several tens MH _Z as determined by the magnetic field strength of the static magnetic field is generally used a coaxial cable, with a special cable processing commensurate with opposing portion curved Is possible, but the GC (upper) and (lower) 9A and 9B wirings require, for example, three pairs of twisted pair wires (50 mm outside diameter) in the X, Y, and Z directions, and are large outside diameter wiring. Therefore, this is the biggest problem in this wiring. In order to solve these problems, in the present invention, a duct 26 shown in FIGS. 3A and 3B is provided. The ducts 26 are provided independently for RF (upper), (lower), GC (upper), (lower), operation display, etc., and these ducts 26 are finally covered with the magnet cover 27. It will be invisible from the outside. 3A and 3B, ducts (upper), (lower) 26A, 26B are provided on the outer peripheral side surfaces of the magnets (upper), (lower) 2A, 2B, and are located on the magnet (upper) 2A side. RF (top) duct 28A, GC _X (top) duct 29AX, GC _Y (top) duct 29AY, GC _Z (top) duct 29AZ, the operation display unit duct 30, and the preliminary duct 31 is 3 points provided divided into position, the magnet (bottom) RF (bottom) duct 28B on the side of 2B, GC _X (bottom) duct 29BX, GC _Y (bottom) duct 29BY, GC _Z (bottom) duct 29BZ and a spare duct 31 are separately provided at two positions. Further, wiring is connected to the duct on the side of the magnet (lower) 2 </ b> B from a pit 32 provided below the floor surface 32.
[0014]
Further, in the present invention, a bus bar type structure is adopted for the wires of GC _X 9X, GC _Y 9Y, and GC _Z 9Z provided in the duct 26. Details of the structure will be described with reference to FIGS. 4A and 4B, the duct 26 for the wiring of GC _X 9X, GC _Y 9Y, and GC _Z 9Z is an electrostatic shield box matching the shape of the magnet. Are stored in a bus bar structure of a copper plate (or aluminum plate).
[0015]
4A and 4B, after the GC lead cable 33 introduced through the filter (upper) 19A of the ceiling 18 of the shield room 4 is fixed to the magnet (upper) 2A by the cable clamp 34 once. , Through a GC cable through hole 35 and to a bus bar 36 fixed in the duct 26. The busbars 36 are arranged in two stages in the duct 26, and are insulated by insulating spacers 37 between the stages and fixed by busbar set screws 38. The other end of the bus bar 36 is connected to the GC lead cable 33 of the GC (upper) 9A. The connection between the bus bar 36 and the GC lead cable 33 is fixed by a wiring screw 40. The duct 26 is fixed to the magnet (upper) 2A with a duct set screw 41. After fixing the bus bar 36 to the duct 26, the duct cover 42 is covered and fixed with the cover set screw 43. FIG. 4C is an enlarged view of the end of the bus bar 36. The upper bus bar 36A of the two bus bars 36 is provided with a notch, and the lower bus bar 36B can be fixed with screws from above. After a space is provided and the bus bars 36A and 36B are fixed with screws, the bus bars 36A and 36B are covered with a wiring cover 44. Both ends of the bus bar 36 have the same structure.
[0016]
In the wiring to the GC 9, not only the connection of the wiring cable 39 from the filter 19 attached to the shield room 4 but also the connection of the GC lead cable 33 are performed with the electrostatic shield after the connection work is completed. The noise associated with the supply of pulsed power to the At the same time, the terminal on the side of the GC lead cable 33 is structured so that the terminal processing is thinner than the combined thickness of the wiring to the GC 9 and the wiring to the RF 10.
[0017]
FIG. 5 is a view of the wiring of the MRI apparatus main body as viewed from above the magnet [top] 2A and from below the magnet (bottom) 2B. FIG. 5A is a view of the magnet (upper) 2A as viewed from above. The magnet (upper) 2A has a portion near the center of the refrigerator 5, the valve motor 45, the flexible hose 20 to the helium level meter 22, and a cable. 21, 39 is, RF (top) 10A in the peripheral portion, GC _X (above) 9AX, GC _Y (upper) 9AY, GC _Z (upper) 9AZ, duct 28A to the operation display unit 11, 29AX, 29AY, 29AZ, 30, a spare duct 31, a cable 39, and a bus bar 36 are arranged. Further, a GC lead cable 33 is connected to each bus bar 36 for GC. The entire wiring is covered with a magnet cover 27. FIG. 5 (B) a view seen from the lower side of the magnet (lower) 2B, RF (lower) 10B in the peripheral portion, GC _X (below) 9BX, GC _Y (bottom) 9BY, the GC _Z (below) 9BZ , Ducts 28B, 29BX, 29BY, 29BZ, a spare duct 31, a cable 39, and a bus bar 36 are arranged. Further, a GC lead cable 33 is connected to each bus bar 36 for GC. The entire wiring is covered with a magnet cover 27 as in the case of the magnet (upper) 2A.
[0018]
As described above, the entire wiring including the superconducting magnet 2 and the refrigerator 5 is divided into two parts, and the magnet (upper) 2A and the magnet (lower) 2B of the MRI apparatus main body 1 are separated from the ceiling 18 and the lower side of the shield room 4. By performing the wiring process, an open MRI apparatus that is close to ideal is configured.
[0019]
On the other hand, an example of a wiring process when wiring from the ceiling 18 of the shield room 4 is inconvenient due to the building will be described below. FIG. 6 shows an example of wiring processing to the MRI apparatus body 1 in the shield room 4 as in FIG. 2. 2 is different from the example of FIG. Since the wiring introduced from the filter (lower) 19B can be connected between the devices in the shield room 4, the number of filter elements 25 when passing through the filter (lower) 19B is reduced. In FIG. 6, the wiring of the RF (upper) 10A and RF (lower) 10B, the wiring of the GC (upper) 9A and GC (lower) 9B, the wiring of the lighting 23 in the shield room and the outlet 24 in the shield room are distributed in the shield room 4. I have.
[0020]
FIG. 7 shows the arrangement and structure of the wiring ducts in the wiring processing example of FIG. All wiring is led from the floor pit 32 toward the top of the magnet 2. All wiring to the magnet (upper) 2A passes through the support 12. In FIG. 7, an integral duct 46 leading from the magnet (bottom) 2B to the magnet (top) 2A is provided in addition to the RF and GC wiring duct 26 shown in FIG. 3, and the ceiling of the magnet (top) 2A It is a passage for wiring to the refrigerator 5, the operation display unit 11, the helium level meter 22, and the like installed on the side close to 18. In addition, the integral duct 46 has a structure to be attached to the outer peripheral side of the RF and GC ducts 26, and is configured to fit within the thickness of the column 12. In the example of FIG. 7, two integrated ducts 46 are provided along two columns 12.
[0021]
Next, regarding the wiring of the RF10 and the GC9, the wiring of the RF10 is performed in the same manner as in FIG. 3, whereas the wiring of the GC9 is performed by a bus bar method. 8A and 8B show examples of the wiring of the GC 9. A GC lead cable 33 is guided from the floor pit 32 to the duct (lower) 26B of the magnet (lower) 2B as a wiring for the GC (lower) 9B and the GC (upper) 9A, and inside the duct (lower) 26B of the magnet (lower) 2B. The bus bar 36 for the GC (bottom) 9B and the GC (top) 9A is wired, the bus bar 36 for the GC (bottom) 9B is connected to the GC (bottom) 9B, and the bus bar 36 for the GC (top) 9A is a support. 12, is passed through a duct (upper) 26A of the magnet (upper) 2A, and is connected to a GC (upper) 9A at an end of the duct (upper) 26A of the magnet (up) 2A. Width struts of the duct 26 and two pairs of GC (e.g. GC _X (upper) 9AX and GC _Y (upper) 9AY) dimensioned to fit within the width of the struts 12 in a state of attaching the duct, in the case of FIG. 4 Similarly, the duct 26 is used as an electrostatic shield box, and wiring is performed with a bus bar 36 using a copper plate (or an aluminum plate).
[0022]
FIG. 9 is a diagram showing the wiring state in the MRI apparatus main body as viewed from below the magnet (lower) 2B. In this case, since the support 12 is also provided with a cover to cover the RF and GC ducts 26, the degree of opening of the MRI apparatus is hindered more than in the case of FIG. In addition, the open feeling of the MRI apparatus is not greatly impaired. In any case, by performing the wiring of GC _X , GC _Y , GC _Z 9X, 9Y, 9Z by the bus bar method, a reasonable wiring suitable for the structure of the magnet can be realized. Can be satisfied.
[0023]
When compared with conventional MRI devices using permanent magnets or normal conducting magnets, in these devices, the columns are made of iron, and the dimensions are large. Wiring space is easy to take. On the other hand, in the facing MRI apparatus using the superconducting magnet, not only the wiring space is hardly taken up, but also the static magnetic field strength is generally high. The power supplied to the RF becomes larger, the wiring cable becomes thicker and the noise becomes larger. Therefore, in order to eliminate the noise, the use of the electrostatic shield box or the bus bar having the duct structure as in the present invention is very effective. In addition, the thickness of the support in the MRI apparatus to which the present invention is applied can be suppressed to the same level as that using a conventional permanent magnet or the like. As a compact can be.
[0024]
【The invention's effect】
As described above, according to the present invention, in the open MRI apparatus in which the superconducting magnets are vertically opposed by the improvement of the wiring method, there is no object other than the columns around the measurement area, so that the subject has Great open feeling can be obtained. Further, the most since the large noise source to become potential wirings GC was completely subjected to shield arrangement, a substantially zero noise from entering the measurement. Further, since the wiring related to the GC is structurally standardized, it is not influenced by the operator, the influence on the characteristics of the wiring work is minimal, and a uniform MRI apparatus can be obtained.
[Brief description of the drawings]
FIG. 1 is a configuration example of an open type MRI apparatus main body using a superconducting magnet.
FIG. 2 is an example of wiring processing to an MRI apparatus body using a superconducting magnet in a shield room.
FIG. 3 is an example of wiring processing of a gradient magnetic field coil and a high-frequency coil for irradiation.
FIG. 4 shows a first configuration example of a gradient coil duct and a bus bar.
FIG. 5 is a first specific example of wiring to an MRI apparatus main body according to the present invention.
FIG. 6 is an example of a wiring process when the wiring to the MRI apparatus main body is divided into two and introduced from one place.
FIG. 7 is a structural example in the case where wiring dust is provided on a support.
FIG. 8 is a second configuration example of the gradient coil duct and the busbar.
FIG. 9 shows a second specific example of wiring to the MRI apparatus main body according to the present invention.
[Explanation of symbols]
1 MRI apparatus main body 2 Superconducting magnet 2A Magnet (top)
2B magnet (bottom)
3 Table 4 Shield room 5 Refrigerator 6 Compressor 7 Measurement area 8 High frequency coil for reception (RF coil)
9 Gradient field coil 9X GC _X
9Y GC _Y
9Z GC _Z
9A GC (above)
9AX GC _X (above)
9AY GC _Y (above)
9AZ GC _Z (above)
9B GC (bottom)
9BX GC _X (bottom)
9BY GC _Y (bottom)
9BZ GC _Z (bottom)
10 RF coil for irradiation 10A RF (top)
10B RF (bottom)
Reference Signs List 11 Operation display unit 12 Support 13 Wiring 14 Power supply unit 15 Operation console 16 RF unit 17 GC unit 18 Ceiling 19 Filter 19A Filter (top)
19B filter (bottom)
Reference Signs List 20 Flexible hose 21 Valve motor cable 22 Helium level meter 23 Lighting in shield room 24 Outlet in shield room 25 Filter element 26 Duct 26A Duct (top)
26B duct (bottom)
27 Duct magnet cover 28A RF (top) duct 28B RF duct duct 29 GC for (bottom) 29AX GC _X (top) duct 29AY GC _Y (upper) 29AZ GC _Z (top) duct 29BX GC _X (under ) duct 29BY GC _Y (bottom) duct 29BZ GC _Z (bottom) duct 30 operation display unit duct 31 spare duct 32 pits 33 GC lead cable 36 bus bar 39 cable 42 duct cover 44 wire cover 45 valve motor 46 integrally Shaped duct.

Claims (4)

An upper superconducting magnet and a lower superconducting magnet arranged vertically facing each other with the measurement area as a center, a gradient magnetic field coil and an irradiation high-frequency coil installed on opposing surfaces of the two magnets, and a subject are placed. And a table inserted into the measurement area, a receiving high-frequency coil for receiving a magnetic resonance signal from the subject, and a magnetic resonance imaging apparatus main body including an operation display unit for operating the same. The magnetic resonance imaging apparatus main body, which is disposed in a shield room provided with a radio wave and an electromagnetic shield, and a power supply device which is provided outside the shield room and supplies power to a device constituting the magnetic resonance imaging apparatus main body, and the magnetic device. Wiring connection is made between a console for operating and controlling the resonance imaging apparatus main body via a filter provided on the outer wall of the shield room. In the discharge type magnetic resonance imaging apparatus, the wiring is divided into an upper superconducting magnet side wiring and a lower superconducting magnet side wiring, and the upper superconducting magnet side wiring is introduced from a filter provided on a ceiling side of the shield room. An open-type magnetic resonance imaging apparatus, wherein a lower superconducting magnet-side wiring is introduced from a filter provided on a lower side surface of the shield room, and is connected to equipment constituting the magnetic resonance imaging apparatus main body. An upper superconducting magnet and a lower superconducting magnet arranged vertically facing each other with a measurement area as a center, a column supporting the upper superconducting magnet, a gradient coil installed on a facing surface of the two magnets, and an irradiation coil. A high-frequency coil, a table on which the subject is placed and inserted into the measurement area, a receiving high-frequency coil for receiving a magnetic resonance signal from the subject, and an operation display unit for operating the same A magnetic resonance imaging apparatus main body to be disposed in a shield room provided with a radio wave shield or a radio wave and an electromagnetic shield, and a power supply apparatus installed outside the shield room and supplying power to a device constituting the magnetic resonance imaging apparatus main body; An outer wall of the shield room between the console for operating and controlling the magnetic resonance imaging apparatus main body and the magnetic resonance imaging apparatus main body. In an open-type magnetic resonance imaging apparatus in which wiring is connected via a filter provided, all wirings are collectively introduced from a filter provided on a lower side surface of the shield room, and an upper superconducting magnet side wiring and a lower superconductivity are introduced in the shield room. Open magnetic resonance, wherein the upper superconducting magnet side wiring is connected to the upper superconducting magnet side from the lower superconducting magnet side along the outer periphery of the column. Imaging device. 3. The open magnetic resonance imaging apparatus according to claim 1, wherein an electrostatic shield comprising a duct and a duct cover is applied to the wiring at the upper superconducting magnet part and the lower superconducting magnet part and / or the support part part. An open-type magnetic resonance imaging apparatus characterized in that: 4. The open-type magnetic resonance imaging apparatus according to claim 1, wherein a bus bar made of a highly conductive metal material is used for wiring in the upper superconducting magnet portion and the lower superconducting magnet portion of the gradient magnetic field coil and / or the column portion. An open-type magnetic resonance imaging apparatus characterized in that the conductor has a form.

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