JP2002143119A - Magnetic field forming device and magnetic resonance video system - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an MRI system capable of improving the SNR characteristics of a magnetic resonance signal. SOLUTION: The system has gradient coil parts 261a and 261b for forming a gradient magnetic field in a space 350 in which a patient 99 is positioned, an RF magnetic field forming coil part 262a for forming an RF magnetic field in the space 350, an RF reception coil part 262b for receiving electromagnetic waves generated from the patient 99, a magnetic shield 264b interposed between the part 261b and the part 262b, a navigation coil part 263 and a supply line 265 consisting of an FPC formed on the side of the part 261b of the part 264b.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

The present invention relates to a magnetic field forming apparatus and a magnetic resonance imaging (MRI: Ma
More particularly, the present invention relates to a magnetic field forming apparatus and a magnetic resonance imaging system having a supply line for supplying a current or a voltage to a device located on an RF (Radio Frequency) coil side with respect to an electromagnetic wave shielding unit.

[0002]

2. Description of the Related Art There is a magnetic resonance imaging system for imaging a test site of a subject using magnetic resonance. FIG. 9 is a diagram schematically showing a cross-sectional structure around a space where a test site in a bore is located in a magnet system used in a conventional magnetic resonance imaging system. As shown in FIG. 9, the magnet system 101 includes a pair of static magnetic fields that form a static magnetic field in a space around a space 150 in a bore in which a portion to be examined (a part to be imaged) of the subject 99 is located. Magnetic field forming magnet units 160a and 160b, a pair of gradient coil units 161a and 161b for forming a gradient magnetic field in the space,
In addition to forming a high-frequency magnetic field for exciting the spins of the test site, NMR (Nuclear
A pair of RF coil units 162a and 162b for receiving a magnetic resonance signal are provided.

An electromagnetic wave shield 164a is interposed between the gradient coil section 161a and the RF coil section 162a, and the gradient coil section 161b and the RF coil section 162a are interposed.
b, an electromagnetic wave shield part 164b is interposed. Also, near the center of the RF coil units 162a, 162b, for example, a static magnetic field fluctuation detection / correction coil unit 163a, 163 for detecting and correcting a static magnetic field fluctuation due to an external factor.
63b are provided respectively. A current or voltage is supplied to the static magnetic field fluctuation detection / correction coil units 163a and 163b from the static magnetic field fluctuation detection / correction coil driving unit 174 via supply cables 170a and 170b having a diameter of about 3 mm. Conventionally, supply cables 170a,
170b are electromagnetic wave shielding parts 164a, 164a, respectively.
4b, on the side of the RF coil units 162a and 162b,
It is arranged at a position distant from the electromagnetic wave shields 164a and 164b.

[0004]

However, in the above-described conventional magnetic resonance imaging system, the supply cables 170a and 170b having a diameter of about 3 mm are arranged at positions away from the electromagnetic wave shields 164a and 164b. There is a problem that the width of the space 150 in the bore in the vertical direction in FIG. In the conventional magnetic resonance imaging system described above, the supply cables 170a, 17
0b is disposed on the side of the RF coil sections 162a and 162b with respect to the electromagnetic wave shield sections 164a and 164b, respectively, so that the RF coil section 162 is generated by noise generated from the supply cables 170a and 170b.
a, 162b of the NMR signal received by the SNR (Signal No.
se Ratio) There is a problem that the characteristics are lowered.

An object of the present invention is to provide a magnetic field forming apparatus and a magnetic resonance imaging system which can secure a wide space in a bore where a site to be examined of a subject is located. And Further, the present invention
An object of the present invention is to provide a magnetic field forming apparatus and a magnetic resonance imaging system that can improve the SNR characteristic of an MR signal.

[0006]

In order to solve the above-mentioned problems of the prior art and to achieve the above object, a magnetic field forming apparatus according to a first aspect of the present invention captures an image of a subject using magnetic resonance. A magnetic field forming apparatus that forms a static magnetic field and an RF magnetic field in a space in which the subject is arranged, and receives a NMR signal generated from the subject, and a gradient coil unit that forms a gradient magnetic field in the space. An RF coil portion, an electromagnetic wave shield portion interposed between the gradient coil portion and the RF coil portion, a device disposed on the opposite side of the electromagnetic wave shield portion from the gradient coil portion, and the electromagnetic wave shield. And a supply line for supplying voltage or current to the device.

The operation of the magnetic field forming apparatus according to the first invention is as follows. A static magnetic field, a gradient magnetic field, and an RF magnetic field are formed in the space where the subject is located. Then, the NMR signal generated from the subject is received by, for example, an RF coil unit. In addition, a current or a voltage is supplied from a supply line to a device disposed on the side opposite to the gradient coil unit with respect to the electromagnetic wave shield unit. In the present invention, since the supply line is formed on the electromagnetic wave shield, the space where the subject is arranged can be made larger than in the related art.

Further, in the magnetic forming apparatus according to the first invention, preferably, the supply line is disposed on the side of the gradient coil section with respect to the electromagnetic wave shield section. Thereby, the noise generated from the supply line is shielded by the electromagnetic wave shield part, and the NMR by the RF coil part.
The influence on signal reception is suppressed.

Further, in the magnetic forming apparatus according to the first aspect of the present invention, the supply line is connected to the electromagnetic wave shield with the R line.
It may be arranged on the side of the F coil unit. Further, in the magnetic forming apparatus according to the first invention, for example, the RF coil unit includes an RF coil that forms an RF magnetic field in the space or an RF coil that receives an NMR signal generated from the subject.

In the magnetic forming apparatus according to the first aspect of the present invention, the electromagnetic wave shield preferably has a hole for passing the supply line at a position facing the device. Further, in the magnetic forming apparatus of the first invention, preferably, the supply line is formed using a flexible printed circuit board. By using a thin, flexible printed circuit board as the supply line, the space where the subject is located can be further increased.

According to a second aspect of the present invention, there is provided a magnetic resonance imaging system which forms a static magnetic field and an RF magnetic field in a space where the subject is arranged in order to image the subject using magnetic resonance. A magnetic resonance imaging apparatus for receiving an NMR signal generated from the apparatus, and a processing apparatus for generating an image of the subject using the NMR signal, wherein the magnetic resonance imaging apparatus forms a gradient magnetic field in the space. Gradient coil and R
An F coil unit, an electromagnetic wave shield unit interposed between the gradient coil unit and the RF coil unit, a device arranged on the opposite side of the electromagnetic wave shield unit from the gradient coil unit, and the electromagnetic wave shield unit And a supply line for supplying voltage or current to the device.

[0012]

DESCRIPTION OF THE PREFERRED EMBODIMENTS Hereinafter, an MRI system according to an embodiment of the present invention will be described. First Embodiment An MRI system according to the first embodiment includes an MRI apparatus,
And an operator console for controlling the MRI apparatus. FIG. 1 shows an MRI system according to this embodiment.
FIG. 2 is a schematic external view of an RI device 202. As shown in FIG. 1, the MRI apparatus 202 includes a magnet system (Magnet
System) 201 and the cradle 15 on which the subject 99 is placed
3 and a transport unit 152 for loading a cradle 153 into a bore 250 of the magnet system 201.

FIG. 2 is a configuration diagram of the MRI apparatus 202 and the operator console 114 shown in FIG. 1, and FIG. 3 is a sectional line A shown in FIG. 2 around a space where a portion to be examined is located in the bore 250 of the magnet system 201. FIG. 4 is a diagram schematically illustrating a cross-sectional structure of FIG. 4A, and FIG. 4 is a diagram illustrating a coil pattern of the RF coil unit 262b and the static magnetic field fluctuation detection / correction coil unit 263 viewed from the direction of arrow B illustrated in FIG. FIG. 5 is a view for explaining a pattern of a supply line 265b formed on the electromagnetic wave shield portion 264b viewed from the direction of arrow B shown in FIG. 3, and FIG. 6 is a view for explaining a cross-sectional structure of the supply line 265. FIG.

[MRI Apparatus 202] MRI Apparatus 202
Is a magnet system 201, R, as shown in FIG.
F drive unit 271, gradient drive unit 272, data collection unit 27
3. It has a static magnetic field fluctuation detection / correction coil drive unit 274 and a control unit 275. In the magnet system 201, as shown in FIGS. 2 and 3, one side of the space 350 in the bore 250 near the magnet center (center position for scanning) is sequentially arranged from the outside to the static magnetic field forming magnet section 260a. , Gradient coil section 261a, electromagnetic wave shield section 2
64a and an RF coil unit 262a are provided. In addition, on the side facing these with the space 350 interposed therebetween,
In order from the outside, the static magnetic field forming magnet 260b, the gradient coil 261b, the electromagnetic wave shield 264b and the R
An F coil unit 262b is provided. Here, the gradient coil sections 261a and 261b correspond to the gradient coil section of the present invention, and the RF coil sections 262a and 262b correspond to the RF coil section of the present invention.
Corresponding to the coil part, the electromagnetic wave shield parts 264a, 264
“b” corresponds to the electromagnetic wave shield part of the present invention.

The static magnetic field forming magnets 260a, 260
2b are located opposite to each other in the vertical direction in FIGS. 2 and 3 at a predetermined interval, and form a static magnetic field (vertical magnetic field) in a space 350 between them. It should be noted that a permanent magnet, a superconducting electromagnet, a normal conducting electromagnet, or the like is used for the static magnetic field forming magnet units 260a and 260b.

The gradient coil units 261a and 261b are RF
In order to provide the magnetic resonance signal received by the coil unit 262b with three-dimensional position information, the static magnetic field forming magnet unit 26
0a and 260b generate a gradient magnetic field that gives a gradient to the intensity of the static magnetic field formed. The gradient magnetic fields generated by the gradient coil units 261a and 261b are of three types: a slice gradient magnetic field, a read-out gradient magnetic field, and a phase encode gradient magnetic field. Correspondingly, each of the gradient coil sections 261a and 261b has three gradient coils.

The RF coil units 262a and 262b form a high-frequency magnetic field (RF magnetic field) for exciting spins in the body of the subject 99 in the static magnetic field space formed by the static magnetic field forming magnet units 260a and 260b. Here, forming a high-frequency magnetic field is called transmission of an RF excitation signal. The RF coil units 262a and 262b receive an electromagnetic wave generated by the excited spin as a magnetic resonance signal. At the center of the RF coil units 262a and 262b, there are provided static magnetic field fluctuation detection / correction coil units 263a and 263b, respectively.

The static magnetic field fluctuation detection / correction coil unit 263a,
H.263b forms a magnetic field in the space 350 in order to correct the variation of the static magnetic field due to an external factor. Here, the static magnetic field fluctuation detection / correction coil unit 263 corresponds to the device of the present invention.

The electromagnetic wave shield part 264a is interposed between the gradient coil part 261a and the RF coil part 262a, and suppresses the electromagnetic wave generated from the gradient coil part 261a from affecting the RF coil part 262a. The electromagnetic wave generated from 262a is generated by the gradient coil unit 261a.
To control the effect. Electromagnetic wave shield part 264b
Is interposed between the gradient coil unit 261b and the RF coil unit 262b to suppress the electromagnetic wave generated from the gradient coil unit 261b from affecting the RF coil unit 262b and to reduce the electromagnetic wave generated from the RF coil unit 262b The influence on the coil portion 261b is suppressed. The electromagnetic wave shields 264a and 264b are formed using copper foil or the like, are grounded, and shield electromagnetic waves. The electromagnetic wave shield portions 264a, 264b are, for example, walls 264a2, 264 surrounding the gradient coil portions 261a, 261b, respectively.
4b2. Electromagnetic wave shield parts 263a, 264b
Includes a static magnetic field fluctuation detection / correction coil unit 263
a, a coupling hole 2 for passing supply lines 265a, 265b for supplying current or voltage to the static magnetic field fluctuation detection / correction coil units 263a, 263b at a position opposed to the coupling holes 2a, 263b;
64a1 and 264b1 are formed.

The supply lines 265a and 265b electrically connect the static magnetic field fluctuation detection / correction coil units 263a and 263b and the static magnetic field fluctuation detection / correction coil drive unit 274. FPC: Fle
xible Print Circuit). One end of each of the supply lines 265a and 265b is connected to the static magnetic field fluctuation detection / correction coil units 263a and 263b,
Connection hole 264a of electromagnetic wave shield portions 264a, 264b
1 and 264b1 to pass through the electromagnetic wave shielding portions 264a,
H.264b is formed on the surface on the side of the gradient coil units 261a and 261b, and the other end is connected to the static magnetic field fluctuation detection / correction coil drive unit 274.

The supply lines 265a and 265b are, for example, as shown in FIG.
It has a stripe shape incorporating a plurality of wires 301 such as a transmission wire, an RF reception wire, and a gradient forming wire, and has a thickness t of, for example, about 0.3 mm. Further, for example, the magnetic shield 302 is formed on both surfaces of the supply lines 265a and 265b, but the magnetic shield may not be provided, or may be formed on only one surface. here,
The supply lines 265a and 265b correspond to the supply lines of the present invention.

The RF driving section 271 includes an RF coil section 262
a, 262b to generate a RF excitation signal to excite spins in the body of the subject 99.

The gradient driving section 272 includes a gradient coil section 261
a, 261b is supplied with a drive signal to generate a gradient magnetic field. The gradient driving unit 272 includes the gradient coil units 261a and 261a.
There are three drive circuits (not shown) corresponding to the three gradient coils 1b.

The data collection unit 273 includes the RF coil unit 26
2a and 262b take in the electromagnetic waves received as magnetic resonance signals and convert them into view data.
And outputs it to the data processing unit 295 of the operator console 114.

A static magnetic field fluctuation detecting / correcting coil driving section 274
Drives the static magnetic field fluctuation detection / correction coil units 263a and 263b so as to detect and correct the static magnetic field fluctuation due to an external factor. The control unit 275 includes an RF drive unit 271, a gradient drive unit 272, a data collection unit 273, and a static magnetic field fluctuation detection /
The correction coil driving section 274 is controlled.

[Operator Console 114] As shown in FIG.
0, an operation display unit 194 and a data processing unit 195. The operation unit 190 is, for example, a keyboard or a mouse connected to a computer or the like, and outputs an operation signal corresponding to an operation of the operator to the data processing unit 195. The operation display unit 194 displays information corresponding to the operation state of the MRI apparatus 202, a processing result of the data processing unit 195, and the like according to an operation signal from the operation unit 190. In the data processing unit 195, data input from the data collection unit 273 is stored in the memory, and a data space is formed in the memory. The data space constitutes a two-dimensional Fourier space. Data processing unit 19
In step 5, the two-dimensional Fourier space data is subjected to two-dimensional inverse Fourier transform to generate (reconstruct) an image of the test site of the subject 99.

Hereinafter, an operation example of the magnetic resonance imaging system of this embodiment will be described. FIG. 7 is a flowchart for explaining the operation example. The operation shown below is
For example, the processing is performed based on the processing and control of the data processing unit 195 in response to the operation of the operation unit 190 of the operator console 114 shown in FIG. 2 by the operator.

Step ST1: First, the cradle 153
The subject 99 placed on the upper part is
Bore 2 of magnet system 201 of MRI apparatus 202
It is carried into 50.

Step ST2: The test site of the subject 99 is positioned at the magnet center in the bore 250. The space 350 shown in FIG. 3 in the bore 250 including the magnet center
, A static magnetic field is formed by the static magnetic field forming magnet units 260a and 260b.

Step ST3: Under the control of the control section 275, the RF coil section 262a by the RF drive section 271
The driving of the RF coil unit 262b and the driving of the gradient coil units 261a and 261b by the gradient driving unit 272 are performed. Thereby, the bore 2 including the magnet center
A gradient magnetic field and a high-frequency magnetic field are formed in the space where the test site is located in 50, and an electromagnetic wave that generates a spin excited at the test site of the test subject 99 is extracted as a magnetic resonance signal by the RF coil units 262a and 262b. This is collected by the data collection unit 173 and output to the data processing unit 195 of the operator console 114 as inspection result data. Further, when the static magnetic field fluctuates due to an external factor, the static magnetic field fluctuation detection / correction coil units 263a and 263b are driven by the static magnetic field fluctuation detection / correction coil driving unit 274 based on the control of the control unit 275, and the static magnetic field Is detected, and the fluctuation of the static magnetic field is corrected based on the detection result. Static magnetic field fluctuation detection / correction coil units 263a, 26
The supply of voltage or current to 3b is performed from the static magnetic field fluctuation detection / correction coil drive unit 274 via supply lines 265a and 265b shown in FIGS. 3, 5, and 6. At this time, since the supply lines 265a and 265b are disposed on the opposite sides of the electromagnetic wave shield parts 264a and 264b from the RF coil parts 262a and 262b, noise generated from the supply lines 265a and 265b is generated by RF.
The influence on the reception of the NMR signal by the coil units 262a and 262b is small.

In the data processing unit 195, the data collection unit 1
The data input from 73 is stored in the memory, and a data space is formed in the memory. The data space constitutes a two-dimensional Fourier space. The data processing unit 195 converts these two-dimensional Fourier space data into two.
The image of the test site of the subject 99 is generated (reconstructed) by performing the dimensional inverse Fourier transform.

Step ST4: When the data collection of the test site of the subject 99 is completed, the subject 99 is carried out of the bore 250 together with the cradle 153 by the transport unit 152.

As described above, according to the magnetic resonance imaging system of the present embodiment, the supply lines 265a, 265
b to the electromagnetic shielding portions 264a and 264b by RF.
Because it is arranged on the opposite side to the coil parts 262a and 262b,
The noise generated from the supply lines 265a and 265b is
The influence on the reception of the NMR signal by the RF coil units 262a and 262b can be reduced. Therefore, high quality N
An MR signal can be obtained, and a high-quality image of a test site can be displayed using the NMR signal.

According to the magnetic resonance imaging system of this embodiment, the supply lines 265a and 265b are used as FPCs.
By using, the width of the space 350 in the bore 250 where the test site is located in the vertical direction in FIG. 3 can be increased,
The space inside the bore 250 where the test site is located can be made sufficiently large.

Second Embodiment The MRI system according to the second embodiment is shown in FIGS.
In the configuration shown in FIG.
Same as the system. The MRI system of the present embodiment is characterized by a supply line that supplies a current or a voltage to the static magnetic field fluctuation detection / correction coil unit 263 in the magnet system. FIG. 8 is a diagram schematically showing a cross-sectional structure taken along a cross-sectional line AA shown in FIG. 2 around a space where a test site is located in the MRI system of the present embodiment. FIG.
In FIG. 3, components denoted by the same reference numerals as those in FIG. 3 are the same as the components denoted by the same reference numerals described in the first embodiment.

As shown in FIG. 8, in the MRI system of the present embodiment, the static magnetic field fluctuation detection / correction coil driving section 274
From static magnetic field fluctuation detection / correction coil units 263a, 263b
Supply lines 365a, 36 for supplying voltage or current to the
5b is disposed on the surface of the electromagnetic wave shield portions 264a, 264b on the side of the RF coil portions 262a, 262b.
The supply lines 365a and 365b are configured using, for example, a flexible printed circuit board. Supply line 3
For example, as shown in FIG. 6, the wires 65a and 365b have a stripe shape in which the electric wires 301 are incorporated at equal intervals in the substrate 300, and have a thickness t of about 1 mm, for example. Further, for example, a magnetic shield 302 is formed on both surfaces of the supply lines 265a and 265b.

According to the MRI system of the present embodiment, the use of the FPC as the supply lines 365a and 365b increases the vertical width of the space 450 in the bore 250 where the test site is located in FIG. And the space in the bore where the test site is located can be made sufficiently large.

The present invention is not limited to the above embodiment. In the above-described embodiment, the vertical magnetic field type MRI system has been illustrated, but the present invention is also applicable to a horizontal magnetic field type MRI system. In the embodiment described above,
As the device of the present invention, the static magnetic field fluctuation detection / correction coil unit has been exemplified. However, in the present invention, if the device is located on the side of the RF coil unit with respect to the electromagnetic wave shield unit and needs to supply current or voltage, For example, a laser for specifying a portion to be inspected or another device such as a camera and a microphone provided in the bore may be used.

[0039]

As described above, according to the magnetic field forming apparatus and the magnetic resonance imaging system of the present invention, since the supply line is formed on the electromagnetic wave shield, the inside of the bore where the portion to be inspected of the subject is located. A large space can be secured. Also,
According to the magnetic field forming apparatus and the magnetic resonance imaging system of the present invention, it is possible to reduce the influence of noise generated from the supply line on the RF coil unit. Therefore, the SNR of the NMR signal
Characteristics can be improved and a high-quality image can be provided.

[Brief description of the drawings]

FIG. 1 is an MRI according to a first embodiment of the present invention.
1 is a schematic external view of an MRI apparatus of a system.

FIG. 2 is a configuration diagram of an MRI apparatus and an operator console shown in FIG. 1;

FIG. 3 is a diagram schematically showing a cross-sectional structure taken along a line AA shown in FIG. 2 around a space where a test site is located in a bore of the magnet system.

FIG. 4 is an RF view from the direction of arrow B shown in FIG. 3;
It is a figure for explaining a coil plane pattern of a coil part and a static magnetic field fluctuation detection and correction coil part.

FIG. 5 is a view for explaining a pattern of a supply line formed on the electromagnetic wave shield section viewed from a direction of an arrow B shown in FIG. 3;

FIG. 6 is a diagram for explaining a cross-sectional structure of a supply line.

FIG. 7 is a flowchart for explaining an operation example of the magnetic resonance imaging system of the first embodiment.

FIG. 8 is a cross-sectional structure taken along a line AA shown in FIG. 2 around a space where a test site is located in a bore of a magnet system according to the MRI system of the second embodiment of the present invention. It is the figure which showed typically.

FIG. 9 is a diagram schematically showing a cross-sectional structure around a space where a test site is located in a bore of a magnet system related to a conventional MRI system.

[Explanation of symbols]

99 subject, 152 transport unit, 153 cradle,
190: operation unit, 194: operation display unit, 195: data processing unit, 201: magnet system, 202: MR
I device, 260a, 260b ... static magnetic field forming magnet section, 261a, 261b ... gradient coil section, 262a, 2
62b RF coil unit, 263 static magnetic field fluctuation detection / correction coil unit, 271 RF drive unit, 272 gradient drive unit
273: Data collection unit, 274a, 274b: Static magnetic field fluctuation detection / correction coil driving unit, 275: Control unit, 265
a, 265b, 365a, 365b ... supply line

──────────────────────────────────────────────────続 き Continued on the front page (51) Int.Cl. ⁷ Identification FI FI Theme Court ゛ (Reference) H01F 7/22 ZAAZ (72) Inventor Kenshi Sato 127 Gee Yokogawa Medical 4-7 Asahigaoka, Hino City, Tokyo System Co., Ltd. F term (reference) 4C096 AB07 AB42 CA01 CA23 CA29 CA58 CA62

Claims (10)

[Claims] 1. A magnetic field forming apparatus for forming a static magnetic field and an RF magnetic field in a space in which the subject is arranged in order to image the subject using magnetic resonance, and receiving an NMR signal generated from the subject. A gradient coil unit that forms a gradient magnetic field in the space; an RF coil unit; an electromagnetic wave shield unit interposed between the gradient coil unit and the RF coil unit; A magnetic field forming apparatus, comprising: a device disposed on a side opposite to a gradient coil unit; and a supply line disposed on the electromagnetic wave shielding unit and supplying a voltage or a current to the device. 2. The magnetic field forming apparatus according to claim 1, wherein the supply line is arranged on a side of the gradient coil unit with respect to the electromagnetic wave shield unit. 3. The magnetic field forming apparatus according to claim 1, wherein the supply line is arranged on a side of the RF coil unit with respect to the electromagnetic wave shield unit. 4. The magnetic field forming apparatus according to claim 1, wherein said supply line is formed using a flexible printed circuit board. 5. The RF coil unit according to claim 1, further comprising an RF coil for forming an RF magnetic field in the space, or an RF coil for receiving an NMR signal generated from the subject.
The magnetic field forming device according to any one of the above. 6. The magnetic field forming apparatus according to claim 1, wherein said electromagnetic wave shield has a hole for passing said supply line at a position facing said device. 7. A magnetic resonance image in which a static magnetic field and an RF magnetic field are formed in a space where the subject is arranged to image the subject using magnetic resonance, and an NMR signal generated from the subject is received. An apparatus, and a processing apparatus that generates an image of the subject using the NMR signal, wherein the magnetic resonance imaging apparatus includes: a gradient coil unit that forms a gradient magnetic field in the space; an RF coil unit; An electromagnetic wave shield part interposed between the gradient coil part and the RF coil part, a device arranged on the side opposite to the gradient coil part with respect to the electromagnetic wave shield part, and arranged on the electromagnetic wave shield part; A magnetic resonance imaging system having a supply line for supplying voltage or current to the device. 8. The magnetic resonance imaging system according to claim 7, wherein the supply line is arranged on the side of the gradient coil unit with respect to the electromagnetic wave shield unit. 9. The magnetic resonance imaging system according to claim 7, wherein the supply line is arranged on a side of the RF coil unit with respect to the electromagnetic wave shield unit. 10. The magnetic resonance imaging system according to claim 7, wherein said supply line is formed using a flexible printed circuit board.