JP2003325471A - Magnetic resonance imaging apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To eliminate works to handle cables or the like for supplying electric power to a magnetic resonance imaging apparatus movable in an MRI room and for exchanging control signals. <P>SOLUTION: The magnetic resonance imaging apparatus is divided into a gantry means and a control means. When images are taken, the gantry means is moved around a bed to load a subject, and a first and a second connector means are coupled there. When no image is taken, the gantry means is removed to a place away from the subject, and the first and a third connector means are coupled there. Various kinds of signals are exchanged between the gantry means and the control means and electric power is supplied through the first and the second connector means coupled mutually when the images are taken. Electric power is supplied to a temperature control means or the like to maintain a state of temperature or the like of a magnetic field generating means or the like on the gantry means through the first and the third connector means coupled mutually when no image is taken. <P>COPYRIGHT: (C)2004,JPO

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a magnetic resonance imaging apparatus for taking a tomographic image of a desired portion of a human body as a subject by utilizing a nuclear magnetic resonance phenomenon, and is particularly configured to be movable in an imaging room. The present invention relates to a magnetic resonance imaging apparatus.

[0002]

2. Description of the Related Art A magnetic resonance imaging apparatus uses a magnetic field generating means to apply a static magnetic field and a gradient magnetic field to a subject, and further irradiates the subject with a high frequency magnetic field pulse to cause nuclear magnetic resonance in the subject. At that time, an echo signal emitted from the subject is detected, and the detected echo signal is processed to capture the density distribution, relaxation time distribution, etc. of nuclear spins in the subject as a tomographic image. The static magnetic field for generating such a nuclear magnetic resonance phenomenon must have a spatially and temporally uniform intensity and direction. The static magnetic field generating means for generating such a static magnetic field is roughly classified into one using a permanent magnet, one using a superconducting magnet and a normal conducting magnet.

These static magnetic field generating means always generate a leak magnetic field outside when generating a static magnetic field. Since a magnetic resonance imaging apparatus is usually used in a hospital, it is important to take safety measures for a person using a pacemaker. Further, the leakage magnetic field generated from the static magnetic field generating means not only affects the pacemaker, but also when the ferromagnetic material such as iron approaches the static magnetic field generating means, the leakage magnetic field magnetizes the ferromagnetic material, A large force is attracted in the direction of the static magnetic field generating means. This attracting force increases as the size of the ferromagnetic material increases and the magnetic permeability increases. Therefore, normally, the ferromagnetic material is not brought into the examination room in which the magnetic resonance imaging apparatus is installed.

[0004]

At present, non-transcutaneous treatment (IVR: Inter Ve
National Radiography) has become commonplace, and a magnetic resonance imaging apparatus has come to be used as an image diagnostic apparatus. Therefore, the magnetic resonance imaging apparatus has come to be installed in the operating room, and the operation of keeping the subject away from the magnetic field area during the operation and moving the subject to the imaging area of the magnetic resonance imaging apparatus as necessary is performed. I was going.

FIG. 1 is a diagram showing a conventional schematic configuration in which a magnetic resonance imaging apparatus is installed in an operating room and a non-percutaneous treatment is performed there. In the figure, the magnetic resonance imaging apparatus is composed of a control apparatus / image processing apparatus 10 and a gantry 100 which are connected by a cable 10a for supplying various signals and electric power. This cable 10a has a number corresponding to the number of signal lines,
It is housed in a cable duct so as not to scatter. The control device / image processing device 10 controls the transmitting coil, the receiving coil, the gradient magnetic field coil and the like on the gantry 100 according to a predetermined program to capture a tomographic image, and also controls the movement of the gantry 100. To do.

Gantry 10 of magnetic resonance imaging apparatus
From 0, a leakage magnetic field 100a is generated around it.
In the figure, the leakage magnetic field 100a is drawn by three lines,
About 5 gauss lines are shown abstractly as the outermost lines. A patient 101, which is a subject, lies on a bed 102. The head of the patient 101 is fixed to the surgical unit fixing tool 103. The surgical field 10 is in the vicinity of the surgical unit fixing tool 103.
Called 4. This surgical field 104 is 5 of the leakage magnetic field 100a.
It is designed so that it does not enter the Gauss line. Patient 101
In addition, peripheral devices 105 to 107 such as a drip, an electrocardiograph, and a surgical microscope are provided around the bed 102. In addition, a surgical instrument table 109 having a surgical instrument 108 mounted thereon is provided near the surgical unit fixing tool 103. Surgeon 110
Are peripheral devices 105 to 107 and surgical instrument 10
8 is used to perform surgery.

However, among the surgical instruments 108, the forceps and the peripheral devices 105 to 107 used during surgery are
Since it is usually made of a magnetic material, it is affected by the leakage magnetic field 100a from the gantry 100 of the magnetic resonance imaging apparatus, and inadvertently accidentally causes the gantry 100 of the magnetic resonance imaging apparatus to mistake these surgical instruments 108 and peripheral devices 105. When ~ 107 are brought close to each other, they are attracted toward the magnetic resonance imaging apparatus 100, which causes a dangerous state. In addition, among the peripheral devices 105 to 107,
Some of them may malfunction due to the influence of the leakage magnetic field 100a.

Therefore, as shown in FIG.
When moving the patient to the head of the patient 101, the peripheral devices 105 to 105
107 is retracted to a position where it is not affected by the leakage magnetic field 100a. At this time, as shown in FIG. 2, a cable (cable duct) 10a connecting the control device / image processing device 10 and the gantry 100 needs to be routed from one end of the operating room to the other, which is troublesome. In addition, the routed cable (cable duct) 10a interferes with the evacuation operation of the peripheral devices 105 to 107, and the operator catches on the cable (cable duct) 10a, trips over, and falls. Was not preferable.

According to the present invention, there is no need to supply power to a magnetic resonance imaging apparatus that can move in a radiographing room, or to carry out a wiring work such as a cable or a cable duct for exchanging control signals. An object is to provide an imaging device.

[0010]

According to a first aspect of the present invention, there is provided a magnetic resonance imaging apparatus, wherein magnetic field generating means for applying a static magnetic field and a gradient magnetic field to a subject and nuclear magnetic resonance to a nuclear spin of atoms constituting the subject. A transmitting means for irradiating a high-frequency magnetic field pulse to wake it up, a receiving means for detecting an echo signal emitted by nuclear magnetic resonance, a magnetic field generating means, the transmitting means and the receiving means are mounted to be movable. And a gantry means having a first connector means for electrically connecting each of these means and an external control means, and the first connector provided near the bed on which the subject is mounted. Second connector means for exchanging various signals and power supply with the gantry means by being connected to the means, and provided at a location apart from the vicinity of the bed, The third connector means for supplying at least electric power to the gantry means by being connected to the first connector means, and the first connector means and the second or third connector means. The control means controls the magnetic field generating means, the transmitting means, and the receiving means, and controls the image reconstruction using the echo signals to create a tomographic image of the subject. According to the present invention, the magnetic resonance imaging apparatus is separated into the gantry means and the control means, and the gantry means is moved to the vicinity of the bed on which the subject is mounted only at the time of imaging, and the first and second connector means are coupled there. . At the time of non-imaging, the gantry means is retracted to a place away from the subject, and the first and third connector means are coupled there.
Since the gantry means is equipped with the magnetic field generating means, the transmitting means and the receiving means as the minimum necessary constituent means capable of capturing a tomographic image by nuclear magnetic resonance, the first and the first coupled to each other at the time of capturing. Various signals are exchanged and power is supplied to and from the control means via the two connector means. On the other hand, at the time of non-photographing, electric power is supplied to the temperature control means for maintaining the temperature state of the magnetic field generation means on the gantry means and the like through the first and third connector means coupled to each other. As a result, it is not necessary to route the cables that connect the control unit and the gantry unit in the photographing room, and it is possible to eliminate the obstacle caused by the presence of the cables.

A magnetic resonance imaging apparatus according to a second aspect is the magnetic resonance imaging apparatus according to the first aspect, wherein the magnetic field generating means uses a permanent magnet to generate a static magnetic field to detect the temperature of the permanent magnet, and the permanent magnet. A heater means for maintaining the temperature of the magnet is provided on the gantry means side, and a temperature control means for controlling a current supplied to the heater means based on the temperature detected by the temperature detection means is provided on the control means side. It is a thing. This is a static magnetic field generated by a permanent magnet. In this case, in order to maintain the temperature of the permanent magnet, the temperature detecting means and the heater means are provided on the gantry means side, and the temperature control means is provided on the control means side. The exchange of signals and the supply of electric power between the temperature control means, the temperature detection means, and the heater means are performed by the first,
This is done via the second and third connector means.

A magnetic resonance imaging apparatus according to a third aspect is the magnetic resonance imaging apparatus according to the first or second aspect, wherein the magnetic field generating means includes a gradient magnetic field coil for generating the gradient magnetic field and a gradient magnetic field power supply for supplying a current to the gradient magnetic field coil. The gradient magnetic field coil is provided by using the gradient magnetic field coil, the gradient magnetic field coil is provided on the gantry means side, and the gradient magnetic field power source is provided on the control means side. This is a gradient magnetic field generated by a gradient magnetic field coil and a gradient magnetic field power source,
In this case, the gradient magnetic field coil is provided in the gantry means, and the gradient magnetic field power supply is provided in the control means side. By providing the minimum necessary means on the gantry means side as described above, the structure of the gantry means can be simplified and it is not necessary to take measures against the leakage magnetic field on the power source side.

A magnetic resonance imaging apparatus according to a fourth aspect is the magnetic resonance imaging apparatus according to any one of the first, second or third aspects, wherein the transmitting means causes a high frequency magnetic field for causing nuclear magnetic resonance in atomic nuclei of atoms constituting the biological tissue of the subject. An irradiation coil for irradiating a pulse, and a high frequency transmission means for repeatedly supplying a high frequency pulse to the irradiation coil in a predetermined pulse sequence, the irradiation coil on the gantry means side,
The high frequency transmission means is provided on the control means side. In this configuration, the transmitting means is composed of an irradiation coil and a high frequency transmitting means. In this case, the irradiation coil is provided in the gantry means and the high frequency transmitting means is provided in the control means side. By providing the minimum necessary means on the gantry means side in this way, the configuration of the gantry means can be simplified and it is not necessary to take measures against the leakage magnetic field on the high frequency transmission means side.

A magnetic resonance imaging apparatus according to claim 5 is the magnetic resonance imaging apparatus according to any one of claims 1, 2, 3 or 4, wherein the gantry means includes drive means for moving and battery means for supplying electric power to the drive means. The battery means is charged while the first connector means is connected to the second or third connector means. In this, the gantry means is moved by the drive means and the battery. Since the battery is mounted on the gantry means, the drive means operates by the electric power from the battery, and the gantry means can be moved. If the gantry means is not provided with a battery, the power line cable may be routed only for supplying electric power to the driving means. A normal household power line cable is sufficient as such a power line cable, and therefore, even if the power line cable is routed around the photographing room, it has little effect.

A magnetic resonance imaging apparatus according to claim 6 is the magnetic resonance imaging apparatus according to any one of claims 1, 2, 3, 4 or 5, wherein the first connector means and the second and third connector means are guide holes and guide pins. Are combined by. This is to provide a guide hole or a guide pin in the connector means in order to more reliably connect the first connector means and the second and third connector means.

[0016]

BEST MODE FOR CARRYING OUT THE INVENTION Preferred embodiments of a magnetic resonance imaging apparatus according to the present invention will be described below with reference to the accompanying drawings. FIG. 3 is a block diagram showing the overall configuration of the magnetic resonance imaging apparatus according to the present invention. This magnetic resonance imaging apparatus, as shown in FIG.
It is composed of a control device 2 and an image processing device 3.

The gantry 1 is composed of a permanent magnet 11, an irradiation coil 12, a gradient magnetic field coil 13, a receiving coil 14, a temperature sensor 15, a heater 16, a battery 17, a drive mechanism 18, a connector 19 and the like. The permanent magnet 11 is
It generates a uniform static magnetic field around the subject in the body axis direction or in a direction orthogonal to the body axis, and is provided in a space with a certain extent around the subject (not shown). . It should be noted that the one that generates the static magnetic field is the permanent magnet 1
In addition to 1, a normal conducting type or superconducting type static magnetic field generating magnet may be used.

Inside the permanent magnet 11, an irradiation coil 12 for repeatedly irradiating a high frequency pulse for causing nuclear magnetic resonance in atomic nuclei of atoms constituting the biological tissue of the subject in a predetermined pulse sequence, A gradient magnetic field coil 13 for generating a gradient magnetic field and a receiving coil 14 for detecting an echo signal (NMR signal) emitted by nuclear magnetic resonance of atomic nuclei of a living tissue of a subject are provided. The gradient magnetic field coil 13 has a configuration capable of independently applying a slice-direction gradient magnetic field, a phase-direction gradient magnetic field, and a frequency-direction gradient magnetic field to Cartesian coordinate axis directions orthogonal to each other. By applying this gradient magnetic field, position information can be added to the echo signal.

The permanent magnet 11 for generating a static magnetic field has a high temperature dependency of the magnetic field strength, and therefore, it is necessary to control the temperature. Therefore, the temperature sensor 15 and the heater 16 are provided, the temperature of the permanent magnet 11 is measured, and the heater 16 is used to control the temperature of the permanent magnet 11 to be a constant temperature. The drive device 18 is composed of a motor, a stop means, and the like, and performs movement of the gantry 1 and positioning during photographing. Drive device 18
Is driven by electric power from the battery 17, because electric power is not supplied from the outside when moving. The battery 17 is adapted to be charged from the primary power source 24 side in the unused state. The connector 19 is the connector 2
By connecting with A, signals and electric power are exchanged between the gantry 1 and the control device 2.

The control device 2 comprises a gradient magnetic field power supply 21, a high frequency transmission / reception system 22, a temperature control device 23 and a primary power supply 24. The gradient magnetic field power supply 21 supplies a current to the gradient magnetic field coil 13. The gradient magnetic field power supply 21 is controlled by the sequencer 32 of the image processing device 3. The high frequency transmission / reception system 22 includes an interface 25 and a synthesizer 2.
6, a transmission system 27 and a reception system 28. The interface 25 inputs the control signal from the sequencer 32 of the image processing device 3 and supplies the control signal to the synthesizer 26.
The synthesizer 26 generates a high-frequency pulse based on the control signal from the sequencer 32, modulates the high-frequency pulse with a predetermined amplitude, amplifies the amplitude-modulated high-frequency pulse by a high-frequency amplifier of a transmission system 27, a filter box 29, a connector. It is supplied to the irradiation coil 12 via 2A and the connector 19 to irradiate the subject with a predetermined pulsed electromagnetic wave.
The reception system 28 has an amplifier that amplifies the echo signal received by the reception coil 14, a quadrature detector, and an A / D converter. When the receiving system 28 detects the electromagnetic wave (NMR signal) generated from the subject by the electromagnetic wave emitted from the transmitting side irradiation coil 12 by the receiving coil 14 arranged close to the subject, the echo signal is amplified. , A quadrature detector and an A / D converter are used to convert into a predetermined digital amount, and at the same time as a command from the sequencer 32, the quadrature detector is converted into two series of collected data, and the interface 25 To the sequencer 32 via. The temperature control device 23 controls the temperature of the permanent magnet 11 by adjusting the current flowing through the heater 16 based on the temperature of the permanent magnet 11 measured by the temperature sensor 15. The primary power supply 24 is
Electric power is supplied to the battery 17 and electric power is supplied to the heater 16.

The image processing device 3 comprises a high speed array processor 31, a sequencer 32, an external storage device 33, a setting switch 34, a display 35 and the like. The high-speed array processor 31 controls the control device 2 via the sequencer 32 according to a predetermined program.
The sequencer 32 operates based on a control command from the high-speed array processor 31, and outputs various commands necessary for collecting data of a tomographic image of the subject to the gradient magnetic field power supply 21 and the high frequency transmission / reception system 22. The sequencer 32 repeatedly applies a high-frequency magnetic field pulse that causes nuclear magnetic resonance to atomic nuclei of the atoms forming the biological tissue of the subject in a predetermined pulse sequence, and the high-speed array processor 3
It operates under the control of 1. The sequencer 32 also outputs various commands necessary for collecting data of a tomographic image of the subject to the gradient magnetic field power supply 21 and the high frequency transmission / reception system 22. The setting switch 34 is an operator such as a keyboard and a mouse that can set and input various states. The external storage device 33 is composed of a magnetic disk, an optical disk, or the like. The display 35 is composed of a CRT, a liquid crystal or the like, and displays a tomographic image or the like. High speed array processor 3
1 is a result of performing signal processing such as Fourier transform or correction coefficient calculation on the dedacil data from the receiving system 28 and processing such as image reconstruction and performing an appropriate calculation on a signal intensity distribution of an arbitrary cross section or a plurality of signals. The obtained distribution is imaged and displayed as a tomographic image on the display 35, and is recorded in the external storage device 33.

FIG. 4 is a diagram showing an outline of a state of an operating room equipped with the magnetic resonance imaging apparatus according to the embodiment of FIG. 3, and is a view of the room seen from above. In this figure, a first box composed of a filter box 291 and a connector 2A1
Connection part, filter box 292 and connector 2A
A second connecting portion consisting of 2 is provided on the wall inside the operating room 40. The filter box 29 which is the first connection part
1 and the connector 2A1 are provided in the upper left corner of the operating room 40 which is the retracted position of the gantry 1, the filter box 292 of the second connecting portion is near the center of the right end of the operating room 40, and the connector 2A2 is the bed 102. Are provided at the lower shooting positions. The gantry 1B shows a case where it is connected to the first connector 2A1 at the retracted position, and the gantry 1C shows a case where it is connected to the second connector 2A2 at the photographing position. The patient (not shown) who is the subject is a bed 1.
Lying above 02. When performing surgery, the gantry 1 is placed in the gantry 1B, where it receives power from the power supply 24 of the connector 2A1 to the battery.
Then, at the time of photographing, the gantry 1 moves from the position of the gantry 1B to the position of the gantry 1C and is installed near the head of the patient, that is, at a position where the operative field can be photographed. The gantry 1 may be moved manually or automatically. In the figure, the control device 2 and the image processing device 3 are arranged in separate rooms separated by a wall. The operating room 40 has an electromagnetic shield room around it.

FIG. 5 is a diagram showing an external configuration of the gantry 1 of FIG. The gantry 1 has a connector 19 at an end of the base 1A, and a battery 17, a permanent magnet 11, a magnetic field generating means such as an irradiation coil 12 and a gradient magnetic field coil 13 (not shown), and a receiving coil on the base 1A. 14, a temperature sensor 15, a heater 16 and the like are mounted. Drive device 1
The part related to the movement of 8 is built in the base 1A,
The wheels are driven electrically. Further, in the portion for positioning the permanent magnet 11 of the drive device 18, the portion below the permanent magnet 11 is a drive mechanism.

FIG. 6 shows the connector 19 of the gantry 1 of FIG.
FIG. 7 is an external view showing details of the vicinity and FIG. 7 is a sectional view showing a state before the connector 19 and the connector 1A are coupled. The connector 19 is provided with a plurality of connection terminals that serve as connection portions for various signals and electric power. Connector 1
On both sides of 9 are provided tapered guide holes 1D and 1E. The guide pins 2D and 2E of the connector 2A on the control device 2 side are inserted and coupled into the guide holes 1D and 1E. As a result, the connector 19 and the connector 2A
Are bound together. A mechanism may be added to this connecting portion to lock it at a fixed distance.
This locking mechanism prevents the connection portion from coming off even if an operator such as a doctor touches the gantry 1 during photographing.

In the above-described embodiment, the gantry 1
The case where one connector 19 is provided in the above is described, but two sets of similar connectors are provided in the base 1A, and each connector has connectors 2A1 and 2A in FIG.
They may be combined in association with each other. When the gantry 1 is in the state shown in FIG. 4, the connector 19 and the connector 2A2 can be connected by simply moving the gantry 1 to the right. However, in order to connect the connector 19 and the connector 2A1 from this state, , Gantry 1 must turn itself. However, Gantry 1 in Figure 4
In the above, when the connectors 19 are provided on the right side and the upper side of the gantry 1, the gantry 1 can be coupled to the respective connectors 2A1 and 2A2 only by moving vertically and horizontally in the room. Further, when the connector 2A1 is located on the left side of the operating room 40 and faces the connector 2A2, the gantry 1 only needs to move left and right in the room, and simplifies control during movement. You can

In the above-mentioned embodiment, the permanent magnet has been described as an example of the means for generating the static magnetic field. However, when the superconducting magnet is used, a refrigerator for cooling the superconducting coil is mounted on the gantry. Therefore, a power line for supplying electric power to the refrigerator, a signal line for degaussing in an emergency, and the like are connected through the connector. When a normal conducting magnet is used, a power supply line for exciting the coil, a signal line for temperature monitoring, etc. are connected via a connector.

If the state in which the gantry 1 is not connected to the connector continues for a long time, the battery 17 mounted on the gantry 1 may be discharged and the drive mechanism may not be able to operate. The charge amount of 17 may be monitored, and when the charge amount falls below a predetermined level, some alarm may be sounded or a warning light may be turned on.

[0028]

According to the present invention, it is necessary to supply electric power to a magnetic resonance imaging apparatus which can move in a radiographing room and to carry out a work such as a cable or a cable duct for exchanging control signals. Because there is no
It is possible to drastically reduce the occurrence of obstacles such as falls due to being caught or tripped over the cable or the cable duct.

[Brief description of drawings]

FIG. 1 is a diagram showing a conventional schematic configuration when a magnetic resonance imaging apparatus is installed in an operating room and a non-percutaneous treatment is performed there.

FIG. 2 is a diagram showing a state of a cable (cable duct) when a gantry is moved to a patient's head.

FIG. 3 is a block diagram showing the overall configuration of a magnetic resonance imaging apparatus according to the present invention.

FIG. 4 is a diagram schematically showing a state in an operating room equipped with the magnetic resonance imaging apparatus according to the embodiment of FIG.
It is the figure which looked at the room from above.

5 is a diagram showing an external configuration of the gantry of FIG.

FIG. 6 is an external view showing details near the connector of the gantry of FIG.

FIG. 7 is a cross-sectional view showing a state before the connectors are coupled to each other.

[Explanation of symbols]

1, 1B, 1C ... Gantry 11 ... Permanent magnet 12 ... Irradiation coil 13 ... Gradient magnetic field coil 14 ... Receiving coil 15 ... Temperature sensor 16 ... Heater 17 ... Battery 18 ... Drive device 19 ... Connector 1A ... base 1D, 1E ... Guide holes 2 ... Control device 21 ... Gradient magnetic field power supply 22 ... High frequency transmission / reception system 23 ... Temperature control device 24 ... Primary power supply 25 ... Interface 26 ... Synthesizer 27 ... Transmission system 28 ... Receiving system 29, 291, 292 ... Filter box 2A, 2A1, 2A2 ... Connector 2D, 2E ... Guide pin 3 ... Image processing device 31 ... High-speed array processor 32 ... Sequencer 33 ... External storage device 34 ... Setting switch 35 ... Display 40 ... Operating room

Claims (6)

[Claims] 1. A magnetic field generating means for applying a static magnetic field and a gradient magnetic field to a subject, a transmitting means for irradiating a high frequency magnetic field pulse to cause nuclear magnetic resonance in nuclear spins of atoms constituting the subject, and a nucleus. Receiving means for detecting an echo signal emitted by magnetic resonance, the magnetic field generating means, the transmitting means and the receiving means are mounted so as to be movable, and each of these means and an external control means are electrically connected. A gantry means having a first connector means for connecting to the body, and a gantry means provided near the bed on which the subject is mounted.
Second connector means for exchanging various signals and power supply with the gantry means by being connected to the connector means, and the first connector means provided at a place distant from the vicinity of the bed. Connected to the gantry means to supply at least electric power to the gantry means, and the magnetic field generating means and the magnetic field generating means via the first connector means and the second or third connector means. A magnetic resonance imaging apparatus comprising: a control unit that controls the transmission unit and the reception unit and that performs image reconstruction calculation using the echo signal to create a tomographic image of the subject. 2. The temperature detecting means for detecting the temperature of the permanent magnet, and the heater for maintaining the temperature of the permanent magnet, according to claim 1, wherein the magnetic field generating means uses a permanent magnet to generate a static magnetic field. Means on the gantry means side, and temperature control means for controlling the current supplied to the heater means based on the temperature detected by the temperature detection means, on the control means side. . 3. The magnetic field generating means according to claim 1 or 2, wherein the magnetic field generating means applies the gradient magnetic field using a gradient magnetic field coil for generating the gradient magnetic field and a gradient magnetic field power source for supplying a current to the gradient magnetic field coil. The gradient magnetic field coil is provided on the gantry means side, and the gradient magnetic field power source is provided on the control means side. 4. The irradiation coil according to claim 1, wherein the transmitting means irradiates a high frequency magnetic field pulse for causing nuclear magnetic resonance in atomic nuclei of atoms constituting the biological tissue of the subject, And a high-frequency transmitting means for repeatedly supplying a high-frequency pulse to the irradiation coil in a predetermined pulse sequence, the irradiation coil being provided on the gantry means side, and the high-frequency transmitting means being provided on the control means side. Magnetic resonance imaging system. 5. The gantry means according to claim 1, 2, 3 or 4, wherein the gantry means includes drive means for moving and battery means for supplying electric power to the drive means, and the first connector means is the A magnetic resonance imaging apparatus, wherein the battery means is charged while being connected to the second or third connector means. 6. The method according to claim 1, 2, 3, 4 or 5.
The magnetic resonance imaging apparatus, wherein the first connector means and the second and third connector means are coupled by a guide hole and a guide pin.