JP3392182B2 - Magnetic resonance imaging equipment - Google Patents

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 in which a static magnetic field generator is heat-insulated, and in particular, the temperature of the static magnetic field generator even when the temperature of a magnetic resonance imaging apparatus installation room (imaging room) changes. The present invention relates to a magnetic resonance imaging apparatus capable of keeping a constant value.

[0002]

2. Description of the Related Art FIG. 5 is a block diagram showing the overall configuration of a magnetic resonance imaging apparatus. This magnetic resonance imaging apparatus obtains a tomographic image of the subject 1 by utilizing a magnetic resonance (NMR) phenomenon. Therefore, a static magnetic field generator 10 having a necessary and sufficiently large bore diameter, and a central processing unit. (Hereinafter referred to as CPU) 11, sequencer 12,
It comprises a transmission system 13, a gradient magnetic field system 14, a reception system 15 and a signal processing system 16.

The static magnetic field generator 10 generates a uniform magnetic flux around the subject 1 in the body axis direction or in a direction perpendicular to the body axis, and has a certain space around the subject 1. A magnetic field generating means of permanent magnet type, normal conducting type or superconducting type is arranged in. Sequencer 1
2 operates under the control of the CPU 11 and sends various commands necessary for collecting data of a tomographic image of the subject 1 to the transmission system 13, the gradient magnetic field system 14 and the reception system 15.

The transmission system 13 includes a high frequency oscillator 17, a modulator 18, a high frequency amplifier 19, and a transmission side high frequency coil 20.
a and the high-frequency pulse output from the high-frequency oscillator 17 is modulated by the modulator 18 according to the instruction of the sequencer 12.
The electromagnetic wave is irradiated to the subject 1 by amplitude-modulating it and supplying it to the high-frequency coil 20a arranged close to the subject 1 after amplifying the amplitude-modulated high-frequency pulse by the high-frequency amplifier 19. It has become.

The gradient magnetic field system 14 includes gradient magnetic field coils 21 wound in three directions of X, Y and Z and respective coils 21.
And a gradient magnetic field power source 22 for driving each of the coils 21 in accordance with a command from the sequencer 12 to generate gradient magnetic fields Gx, Gy, Gz in three directions of X, Y, Z. It is adapted to be applied to the subject 1. The slice plane for the subject 1 can be set by the method of applying the gradient magnetic field.

The receiving system 15 includes a high frequency coil 2 on the receiving side.
0b, an amplifier 23, a quadrature phase detector 24, and an A / D converter 25, and the electromagnetic wave (NM) of the response of the subject 1 due to the electromagnetic wave emitted from the high-frequency coil 20a on the transmission side.
The R signal) is detected by the high frequency coil 20b arranged close to the subject 1, and the amplifier 23 and the quadrature phase detector 24 are detected.
Via the A / D converter 25 to be converted into a digital amount, and further converted into two series of collected data sampled by the quadrature phase detector 24 at the timing according to the instruction from the sequencer 12, and the signal is processed. It is designed to be sent to the system 16.

The signal processing system 16 includes a CPU 11, a recording device such as a magnetic disk 26 and a magnetic tape 27, and a CR.
And a display 28 such as T.
Fourier transform, correction coefficient calculation value image reconstruction, and the like are performed, and the signal intensity distribution of an arbitrary section or a distribution obtained by performing an appropriate calculation on a plurality of signals is imaged and displayed on the display 28. ing.

In FIG. 1, the high frequency coils 20a and 20b and the gradient magnetic field coil 21 on the transmitting side and the receiving side are
Static magnetic field generator 10 arranged in the space around the subject 1
In such a magnetic resonance imaging apparatus arranged in the magnetic field space of FIG. 6, a general example of a permanent magnet type static magnetic field generating apparatus 10 using a permanent magnet for generating the static magnetic field is shown in FIG.
7 and FIG. That is, a pair of yokes 41a and 41b
Support the permanent magnets 42a, 42b and the pole pieces 43a, 43b, respectively, and connect the yokes 41a, 41b to the four columns 47a.
It is configured to be held facing each other at a predetermined distance of about 47d.

In such a static magnetic field generator 10,
The polarities of the permanent magnets 42a and 42b are different from each other, and the magnetic circuit has a permanent magnet 42a → a magnetic pole piece 43a → a magnetic pole piece 43b → a permanent magnet 42b → a yoke 41b → a column 47a.
47d → yoke 41a → permanent magnet 42a.

Of these components, the pole pieces 43a,
43b is for making the magnetic field homogeneity more uniform in the space 44 in which the subject 1 (see FIG. 5) enters, that is, the central portion between the pole pieces 43a, 43b. The effective gap in which the subject 1 can enter is the distance between the projections 46, 46 of the pole pieces 43a, 43b. In this space, in addition to the subject 1, a gradient magnetic field coil 45, an RF irradiation coil, necessary for imaging,
An RF receiver coil (not shown) is arranged.

Since the static magnetic field generator 10 uses a permanent magnet, there is a problem that the magnetic field strength changes due to a change in ambient temperature. Generally, its temperature coefficient is -1000pp
m / ° C, that is, the static magnetic field strength becomes 1 when the temperature rises by 1 ° C.
000ppm weakens. In a nuclear magnetic resonance imaging apparatus, a gradient magnetic field is added to a static magnetic field so that the position corresponds to the magnitude of the magnetic field and a resonance frequency corresponding to the position is generated. A nuclear magnetic resonance (NMR) signal having this frequency is detected to identify the position. However, if the intensity of the static magnetic field changes under the influence of temperature, the position identification will eventually include an error. This misalignment causes distortion and blurring on the image.

The change limit of the magnetic field strength that does not cause a problem on the image is generally 5 ppm / imaging time. According to this standard, it is necessary to suppress the temperature change within 5/1000 ° C. within the photographing time. As one of the methods, the inventors have covered the periphery of the static magnetic field generator 10 (magnetic circuit) with a heat insulating material as shown in Japanese Patent Application No. 61-185277, provided a heater inside, and provided a current to the heater. It proposes a control method for controlling and keeping the temperature of the static magnetic field generator 10 constant.
8 and 9 show a configuration in which the temperature of the static magnetic field generator 10 is controlled to be kept constant by using such a heat insulating unit.

FIG. 8 shows the static magnetic field generator 10 shown in FIG. 6 with the adiabatic part attached, with the right half omitted. FIG. 9 is a static magnetic field generator 1 viewed from the YZ plane of FIG.
0 is a cross-sectional view of the lower part. As shown in the figure, the heat insulating part 60 is composed of a heat insulating material 56, an aluminum plate 58, and a heater 59 in this order from the outside, and faces the static magnetic field generator 10 with an air layer 61 interposed therebetween. The temperature sensor (not shown) is provided at a position where the temperature of the static magnetic field generator 10 can be detected, and controls the current to the heater 59 to keep the temperature of the static magnetic field generator 10 constant.

[0014]

However, the above-mentioned prior art does not consider the convection of the air layer 61. That is, the air layer 61 can be a good heat insulating material when there is no convection, but it becomes easy to transfer heat when there is convection. Therefore, in the conventional heat insulation structure, the heater 5
The temperature unevenness is likely to occur due to the local temperature rise of the static magnetic field generation device 10 that occurs because the heat of 9 is directly transmitted to the static magnetic field generation device 10.

Further, the control method is to detect and control the temperature of the static magnetic field generator 10 having a long temperature time constant as described above. However, in this control method, since the time constant is long, the current temperature is determined by a long thermal history, and the temperature sensor detects the current temperature of the static magnetic field generation device 10 to determine the heat generation amount of the heater 59. Even if controlled, the temperature of the static magnetic field generator 10 does not follow the heat generated by the heater 59. Therefore, in this control method, temperature stability due to the recent high performance (the recent magnetic resonance imaging apparatus uses a high-performance imaging method and the allowable value of the magnetic field strength change is becoming more severe) The structure is becoming difficult to improve.

Further, in the prior art, as can be seen from FIG. 9, the heat insulating structure near the pole pieces 43 (43a, 43b) is not provided with the heater 59 only by inserting the heat insulating material 56, and therefore the gradient magnetic field coil (see FIG. The fever (not shown) became a problem. That is, when the apparatus is not used, the heat radiation from the vicinity of the pole piece 43 is large, and when the apparatus is used, the vicinity of the pole piece 43 is warmed by the heat generated by the gradient magnetic field coil arranged outside the heat insulating portion. Therefore, it means that the temperature of the static magnetic field generator 10 is different between the time of use and the time of non-use, that is, the temperature changes. This is especially in view of the increase in the heat generation amount of the gradient magnetic field coil due to the recent speeding up. It became a big problem.

An object of the present invention is to provide a magnetic resonance imaging apparatus capable of keeping the temperature of the static magnetic field generator constant even if the temperature of the apparatus installation place (such as an imaging room) changes.

[0018]

In order to achieve the above object, the present invention provides a first heat insulating material that covers the periphery of a static magnetic field generator, and a heater provided on the outer surface of the first heat insulating material. ,
A second heat insulating material that covers the outer surface of the heater and a current or voltage to the heater are controlled according to the temperature detected by a temperature sensor provided at a predetermined location to keep the temperature of the static magnetic field generator constant. It is provided with a control means for controlling (Claim 1).

Further, the first heat insulating material covering the static magnetic field generator and the non-magnetic material formed on the outer surface of the first heat insulating material so as to have a surface area substantially the same as that of the first heat insulating material. Of high thermal conductivity, a heater provided on the outer surface or the inner surface of the heat equalizing material, a second heat insulating material that covers the outer surface of the heater, and a temperature sensor provided at a predetermined location. And a control means for controlling the current or voltage to the heater according to the detected temperature to keep the temperature of the static magnetic field generator constant (claim 2). Further, the opening of the static magnetic field generator is such that the RF shield is also used as the heat equalizing material (claim 3).

Further, the control means comprises one or more temperature sensors for detecting the temperature of the heater, a control circuit and a power source, and controls the temperature of the heater to be constant according to the temperature detected by the sensor. However, the temperature of the static magnetic field generator is kept constant (claim 4), or at least one first temperature sensor for detecting the temperature outside the second heat insulating material, A second temperature sensor that detects the temperature of the heater, a control circuit, and a power supply are provided, and the second temperature sensor controls the temperature of the heater to a certain set value, and the first temperature sensor The sensor controls the set value (claim 5).

[0021]

In the invention described in claim 1, heat insulation and heat retention are performed by the first heat insulating material, the heater and the second heat insulating material. In this case, the first heat insulating material acts to prevent the heat generated by the heater from being directly conducted to the static magnetic field generator to locally raise the temperature, and the heater generated when the temperature of the heater is controlled to a desired value. The effect of preventing the temperature ripple from directly transmitting to the static magnetic field generator. That is, when the temperature of the heater is controlled at a desired temperature of ± 0.1 ° C, for example, the desired temperature of ± 0.01 ° C depending on the first heat insulating material.
It becomes the following. The second heat insulating material acts to reduce the amount of heat generated by the heater. That is, since the heat of the heater is prevented from being released to the outside air, the efficiency of heat generation (heat retention) with respect to the static magnetic field generator is improved.

In the invention according to claim 2, the first,
Heat insulation and heat retention are performed by interposing a non-magnetic and highly heat-conductive soaking material (for example, an aluminum material) and a heater between the second heat insulating material. In this case, the action of the first and second heat insulating materials is the same as described above. Further, the heat equalizing material having high thermal conductivity evenly dissipates the heat of the heater between the first and second heat insulating materials, and has the same function as if the heater has a large area even if the heater area is small. That is, uneven temperature distribution is less likely to occur.

In the third aspect of the invention, the RF shield is also used as a heat equalizing material for the opening of the static magnetic field generator. That is, the static magnetic field generator opening cannot have a low electric resistance because of the eddy current generated by the pulsed magnetic field generated by the gradient magnetic field coil. In general, a material having a high electric resistance has a low thermal conductivity, and therefore a soaking material having high heat conductivity (for example, an aluminum material) cannot be used. However, since the commonly used RF shield is a copper foil or a copper net, this is also used as a soaking material having high thermal conductivity, and the effect of making uneven temperature distribution less likely is the same as that of the above-described invention. is there.

The temperature sensor according to the fourth aspect functions to feed back the temperature of the heater to the control circuit and keep the heater temperature constant. The two temperature sensors according to claim 5 are temperature sensors that detect the temperature of the heater, control the temperature of the heater to a certain set value, and detect the temperature of the device installation location (imaging room). Serves to control the set value. This is because the amount of heat radiation changes depending on the outside air temperature, and the temperature set value of the heater must be changed according to the outside air temperature.

[0025]

Embodiments of the present invention will be described below with reference to the drawings. FIG. 1 is a view showing a part of an essential part of an embodiment of a magnetic resonance imaging apparatus according to the present invention, in which the entire structure of a static magnetic field generator that is heat-insulated and kept warm is viewed from the XZ plane of FIG. In the figure, the right half and the left part are cut away from the center.

In FIG. 1, reference numeral 10 denotes a static magnetic field generator (whole), and this portion has the same structure as that of a conventional magnetic resonance imaging apparatus. That is, the pair of permanent magnets 101 have the magnetic pole pieces 105 on the opening side, and the air gaps A in which the subject can enter are formed between the magnetic pole pieces 105 and are vertically opposed to each other. These permanent magnets 10
Reference numeral 1 is for generating a static magnetic field in the space A, and is formed in a disc shape, for example, and is supported by upper and lower yokes 102, respectively. These yokes 102 consist of upper and lower permanent magnets 101 and pole pieces 105.
The pairs are arranged facing each other with a predetermined space, and the column 1
And 03 for forming a magnetic path. Since the operating principle of the magnetic circuit has been described in the prior art, it is omitted here.

The heat insulating and heat retaining structure of the static magnetic field generator 10 of the present invention is as follows. That is, a space 11 around the static magnetic field generator 10 is small enough to prevent air convection between the surfaces of the static magnetic field generator 10.
A heat insulating portion 110 (110a, 110b) is formed so as to cover 6 at a position.

The heat insulating portion 110a is a first heat insulating material 111 made of a heat insulating material having a low thermal conductivity such as foamed resin (eg, melamine resin, styrofoam, urethane foam).
And an aluminum plate 114, which is located on the opposite side of the first heat insulating material 111 from the gap 116 and is bonded to the first heat insulating material 111 in the same area as the first heat insulating material 111, and the aluminum plate 114. Of the planar heater 112 adhered to the opposite side of the space 116 and the aluminum plate 114.
Alternatively, the second heat insulating material 113 adhered to the planar heater 112
(Made of the same material as the first heat insulating material 111).

The heat insulating section 1 on the opening side of the static magnetic field generator 10
No. 10b cannot be used because the aluminum plate 114 has a problem of eddy current generation. Therefore, instead, an RF shield 117 formed so as to cover the opening with a copper foil or a copper net used for improving the S / N of the receiving coil in the magnetic resonance imaging apparatus is used, and the planar heater 112 is attached to it. ing. Others are heat insulation part 110
It is constructed similarly to a. In the illustrated example, since the entire circumference of the static magnetic field generator 10 is not the structure of the heat insulating section 110a or 110b, the details of the heat insulating structure around the static magnetic field generator 10 will be described below. That is,
B, C, and H are the structure of the heat insulating part 110a, and CHI is the structure of the heat insulating part 110b. Also, ro and ha are the heat insulating structure of the first heat insulating material 111, the aluminum plate 114, and the second heat insulating material 113, and the heat is the first heat insulating material 111 and the second heat insulating material. Material 11
3 is a heat insulating structure with respect to No. 3, and the torch is a heat insulating structure with the first heat insulating material 111, the RF shield 117, and the second heat insulating material 113.

Here, the aluminum plate 114, RF
The stacking order of the shield 117 and the planar heater 112 may be the reverse of the above example.

An example of a method of fixing the heat insulating section 110 to the static magnetic field generator 10 will be described with reference to FIG. As shown, the stud bolt 121 having a screw shaft on the static magnetic field generator 10 side and a screw hole on the opposite side is fixed to the static magnetic field generator 10 on the screw shaft side, and is drilled in the first heat insulating material 111. The stud bolt 121, and the aluminum plate 114 at the screw hole side of the stud bolt 121 through a large hole.
The heat insulating part 110 is fixed to the static magnetic field generator 10 by screwing. A hole larger than the head of the screw 122 screwed into the screw hole of the stud bolt 121 is formed in the heat insulating material 113 so that the screw can be fixed.

In addition, at least one temperature sensor using a high precision thermistor for controlling the temperature is used.
Two planar heaters 112 are provided at two locations, and one planar heater 112 is controlled by the temperatures detected at the two locations. Here, the first temperature sensor 118 fixed in contact with the planar heater 112 (or the first temperature sensor 119 fixed in contact with the static magnetic field generator 10) and the second heat insulating material 113. A second temperature sensor 120 that detects the temperature of the air in the imaging room (magnetic resonance imaging apparatus installation room) is provided outside.

FIG. 3 shows an example of a control circuit for the sheet heater 112. This is because the static magnetic field generation device 10 is provided by detecting the temperature at two locations and keeping the temperature of the planar heater 112 constant.
In the control circuit that stabilizes (keeps constant) the temperature of the sheet heater 112, the temperature of the sheet heater 112 is controlled to a certain set value by the first temperature sensor 118 that detects the temperature of the sheet heater 112. The second temperature sensor 120, which detects the temperature of, controls the set temperature. The purpose is that the heat radiation amount of the planar heater 112 changes depending on the outside air temperature, so that the set value must be changed according to the outside air temperature.

Details of such a control circuit will be described below. In FIG. 3, the bridge circuit 130 is a reference resistor 13
1, 132 and the first temperature sensor 118, the bridge circuit 140 includes reference resistors 141 and 142 and the second temperature sensor 120. The first temperature sensor 118 detects the temperature of the planar heater 112, and the second temperature sensor 1
Reference numeral 20 is a sensor for detecting the temperature of the photographing room. Since the resistance values of the temperature sensors 118 and 120 change with temperature, they can be incorporated in the bridge circuits 130 and 140.

If the reference voltage 135 serves as a power source for the bridge circuits 130 and 140, and the resistance value of the temperature sensor 118 corresponding to the target set temperature of the planar heater 112 and the resistance value of the reference resistor 132 are made the same. The voltages V1 and V2 become the same, and the output of the differential amplifier 136a becomes zero. In other words, when the first temperature sensor 118 has the resistance value of the target set temperature, the planar heater 112 does not generate heat. Here, the differential amplifiers 136a and 136b output a positive voltage when the voltage V1 <V2. Therefore, when the temperature of the first temperature sensor 118 decreases, the resistance value of the first temperature sensor 118 increases, V3 becomes a positive output voltage, and the planar heater 112 generates heat.

Similarly, if the resistance value of the second temperature sensor 120 and the resistance value of the reference resistor 142 of the bridge circuit 140 at the temperature of the photographing room at the target set temperature are the same, the differential amplifier 136b at that time is set. Output of V4 becomes zero. The voltage applied to the planar heater 112 at that time is as shown by the solid line in the graph of FIG. If the temperature of the photographing room rises from this state, the output of the differential amplifier 136b becomes a negative voltage and is added to the voltage V3, and the result is as shown by the dotted line in the graph of FIG. It can be changed by (temperature of the shooting room). In addition, 141 is an amplifier which gives the applied voltage (determined value) to the planar heater 112.

Here, since it is preferable to distribute the planar heater 112 over the entire static magnetic field generator 10 (magnetic circuit), a large number of planar heaters 112 are needed, but the first temperature sensor 118 and the second temperature sensor 118 for controlling the planar heater 112 are required. A pair of temperature sensors 120 is provided for each planar heater 112, and a pair of temperature sensors 118, 12 is provided.
One planar heater 112 may be controlled by 0, or a plurality of planar heaters 112 may be controlled by the pair of temperature sensors 118, 120. Also,
Both the first temperature sensor 118 and the second temperature sensor 120 1
However, the temperature sensors 118 and 120 may be connected in parallel to the temperature sensor positions of the bridge circuits 130 and 140 of FIG. 3, respectively. In this case, for example, when a plurality of second temperature sensors 120 are used and the positions where the sensors are arranged are made different, the average temperature of the air temperature in the photographing room at each position where the sensors are arranged is controlled.

According to the apparatus of the present invention described above, the first heat insulating material 1
11 prevents the heat generated by the heater from being directly conducted to the static magnetic field generator 10 (magnetic circuit) to locally raise the temperature, and when the temperature of the planar heater 112 is controlled to a desired value. The generated temperature ripple of the planar heater 112 is prevented from being directly transmitted to the static magnetic field generator 10. Then, the heat generated by the planar heater 112 is prevented from being released to the external air by the second heat insulating material, the heat generation (heat retention) efficiency for the static magnetic field generation device 10 is improved, and the temperature of the static magnetic field generation device 10 is increased. It can be held constant.

Further, the first and second heat insulating materials 111 and 113
Since the aluminum plate 114, which is a non-magnetic and highly heat-conductive soaking material, is interposed together with the planar heater 112, the heat of the planar heater 112 is absorbed by the first and second heat insulating materials 111, 11.
There is an effect that it can be diffused uniformly among the three, and the temperature of the static magnetic field generator 10 can be kept constant even if the heater capacity is small.

[0040]

As described above, according to the present invention, since the heater having a short time constant is controlled to be constant, the control accuracy is improved, and the heat of the heater directly affects the static magnetic field generator. Since it is not heated, uneven temperature distribution is less likely to occur, and the temperature of the static magnetic field generator can be kept constant, which has the effect that a good magnetic resonance imaging image without blurring and distortion can be obtained.

[Brief description of drawings]

FIG. 1 is a diagram showing a part of an essential part of an embodiment of a device of the present invention.

FIG. 2 is a cross-sectional view for explaining an example of a method of fixing the heat insulating unit in FIG. 1 to the static magnetic field generator.

FIG. 3 is a diagram showing an example of a control circuit for the sheet heater in FIG.

FIG. 4 is a graph showing the relationship between the temperature of the upper surface heater and the voltage applied to the surface heater.

FIG. 5 is a block diagram showing the overall configuration of a magnetic resonance imaging apparatus equipped with a static magnetic field generator that uses a permanent magnet to generate a static magnetic field.

FIG. 6 is a perspective view of a static magnetic field generation device in which a permanent magnet is used to generate a static magnetic field.

FIG. 7 is a sectional view of the same.

FIG. 8 is a perspective view showing a part of an essential part of a conventional device.

FIG. 9 is a sectional view of the same.

[Explanation of symbols]

10 Static Magnetic Field Generator (Magnetic Circuit) Using Permanent Magnet for Generating Static Magnetic Field 101 Permanent Magnet 111 First Heat Insulating Material 112 Sheet Heater 113 Second Heat Insulating Material 114 Aluminum Plate (Soaking Material) 116 Void 117 RF Shield 118 First temperature sensor 120 Second temperature sensor

Continuation of front page (56) Reference JP-A-4-269941 (JP, A) JP-A-3-92138 (JP, A) JP-A-3-70544 (JP, A) JP-A-63-258002 (JP , A) JP-A-63-43649 (JP, A) (58) Fields investigated (Int.Cl. ⁷ , DB name) A61B 5/055

Claims (5)

(57) [Claims] 1. A magnetic resonance imaging apparatus including a static magnetic field generator that uses a permanent magnet for generating a static magnetic field, and a first heat insulating material that covers the periphery of the static magnetic field generator.
A heater provided on the outer surface of the first heat insulating material, a second heat insulating material covering the outer surface of the heater, and a current to the heater or a current depending on the temperature detected by a temperature sensor provided at a predetermined location. A magnetic resonance imaging apparatus comprising: a control unit that controls a voltage to keep the temperature of the static magnetic field generator constant. 2. A magnetic resonance imaging apparatus equipped with a static magnetic field generator using a permanent magnet for generating a static magnetic field, wherein a first heat insulating material covering the periphery of the static magnetic field generator,
A non-magnetic, highly heat-conductive soaking material formed on the outer surface of the first heat insulating material so as to have a surface area substantially the same as that of the first heat insulating material, and an outer surface or an inner surface of the soaking material. A heater provided in the heater, a second heat insulating material that covers the outer surface of the heater, and the static magnetic field generation by controlling the current or voltage to the heater according to the temperature detected by a temperature sensor provided at a predetermined location. A magnetic resonance imaging apparatus comprising: a control unit that keeps the temperature of the apparatus constant. 3. The magnetic resonance imaging apparatus according to claim 2, wherein an RF shield is also used as the soaking material in the opening of the static magnetic field generator. 4. The control means comprises one or more temperature sensors for detecting the temperature of the heater, a control circuit, and a power supply, and controls the temperature of the heater to be constant according to the temperature detected by the sensor. The magnetic resonance imaging apparatus according to claim 1, wherein the temperature of the static magnetic field generator is kept constant. 5. The one or more first temperature sensors for detecting at least the temperature outside the second heat insulating material, the second temperature sensor for detecting the temperature of the heater,
A control circuit and a power supply are provided, the temperature of the heater is controlled to a certain set value by the second temperature sensor, and the set value is controlled by the first sensor. The magnetic resonance imaging apparatus according to claim 1, 2, or 3.