JP4369774B2 - Magnetic resonance imaging device using superconducting magnet device - Google Patents

Description

  The present invention relates to an open-type superconducting magnet apparatus and a magnetic resonance imaging (hereinafter referred to as MRI) apparatus using the same, and in particular, reduces the amount of refrigerant used and reduces the consumption of refrigerant to zero or infinitely zero. The present invention relates to an open superconducting magnet apparatus that maintains a close state and an MRI apparatus that improves inspection throughput by using this apparatus.

2. Description of the Related Art MRI apparatuses that obtain a tomographic image of a human body using a nuclear magnetic resonance (hereinafter referred to as NMR) phenomenon are widely used in medical institutions.
In order to improve the image quality in this MRI apparatus, a magnet having high magnetic field strength and high magnetic field uniformity is required. MRI systems using permanent magnets made of high-performance magnetic materials with a magnetic field strength of 0.4 Tesla or less are also commercially available, but the magnetic field uniformity of these permanent magnet systems is the performance of the pole piece incorporated in the magnetic circuit. It is almost determined by and is a value of more than 10 ppm. On the other hand, an air-core superconducting magnet that does not use pole pieces in the magnetic circuit is the only option for achieving a magnetic field uniformity of 3.5 ppm or less with a magnetic field strength of 0.5 Tesla or higher. The MRI apparatus using this superconducting magnet is currently used in general clinical practice from 0.5 to 3 Tesla, and its magnetic field uniformity is less than 3 ppm.

With such a magnet, the intensity of the NMR signal is proportionally improved in accordance with the magnetic field intensity, and the imaging time can be shortened. Echo planar imaging (EPI) is a typical technique for high-speed imaging.
The basic imaging technique of EPI is to excite a nuclear spin once, reverse the polarity of a uniaxial gradient magnetic field at high speed within the relaxation time of the nuclear spin, and adjust the echo signal to the reversal of the gradient magnetic field. A gradient magnetic field of another axis that is generated each time and is orthogonally applied to the echo signal is applied to the echo signal to label position information, and 128 to 256 matrix data necessary for the two-dimensional image is measured.

In addition, while improving the diagnostic ability, the opening of the examination space is widened so as not to give the subject a feeling of pressure as much as possible. An open MRI system was also developed.
Even in this open MRI apparatus, high-speed imaging and high-function measurement have been demanded by increasing the magnetic field strength and using a high magnetic field uniform magnet. Therefore, an open superconducting magnet was also made.

As an example, as shown in [Patent Document 1], as with a permanent magnet device, there is a pole piece made of a ferromagnetic material vertically with a shooting space in between, and a pair of superconductors around it. An MRI superconducting magnet with a coil is constructed.
However, there is still a demand for an open MRI apparatus to have both a high magnetic field strength and a high magnetic field uniformity as in the conventional air-core type superconducting magnet, and to enable high-speed imaging functions and high-function imaging. Therefore, as shown in [Patent Document 2], an open MRI apparatus using a superconducting magnet having an open structure that does not use a pole piece has been developed.
JP 2000-331820 A Japanese Patent Application No. 2002-063569

  In the open MRI apparatus, the shape of the device incorporated in the magnet is devised so as not to hinder the open structure of the magnet. That is, the gradient magnetic field coil has a two-plate structure and is arranged above and below the imaging space so as to function as one gradient magnetic field coil. As a result, this flat magnetic field gradient coil tends to have a larger leakage magnetic flux than a conventional cylindrical magnetic field gradient coil.

  Furthermore, when high-speed imaging is performed with an open MRI system that uses an air-core type superconducting magnet with an open structure, especially when the EPI method is implemented, the high-speed reversal operation of the gradient magnetic field constitutes the metal material that constitutes the superconducting magnet. An eddy current is generated in the inside, and as a result, heat is generated in the superconducting magnet. This heat causes the liquid helium to evaporate, but compared to the amount of heat generated by conventional imaging methods, the amount of heat that cannot be ignored by EPI is generated in the superconducting magnet. Increase the evaporation of

  The open-structure superconducting magnet has a structure in which the helium vessel-cryostat-that houses the superconducting coil with the imaging space in between is divided into two parts. The volume of each helium vessel is the same as that of a conventional cylindrical superconducting magnet. Since it is much smaller than that, the amount of liquid helium used to cool the superconducting coil is small.

  In order to make up for the evaporated liquid helium, it is necessary to replenish the liquid helium. However, in an open MRI apparatus using an air-core type superconducting magnet with an open structure, it is necessary to replenish liquid helium frequently for the above reasons. . As a result, inspection pauses frequently occur due to liquid helium replenishment, and the operation cost increases. Furthermore, it was discovered that the uniformity of the magnetic field is not stable for about 10 hours until the internal pressure of the cryostat changes due to replenishment of liquid helium and the internal pressure becomes stable again. Therefore, even if the high-speed imaging method such as the folding angle EPI is adopted to shorten the inspection time per time, the inspection efficiency is not improved at all.

  In a superconducting magnet using a pole piece as in [Patent Document 1], most of the eddy current is generated in this pole piece, so the problem of violent evaporation of liquid helium due to eddy current can be avoided. As described above, it is difficult to achieve high magnetic field uniformity. In addition, the stability of the magnetic field may change due to eddy currents or temperature changes.

  In addition, in an open core type superconducting magnet that does not use a pole piece as in [Patent Document 2], the superconducting coil is placed on the imaging space side (bottom surface) in the upper helium container in order to increase the static magnetic field generation efficiency. The superconducting coils are arranged close to the imaging space side (upper surface) in the lower helium container. For this reason, many liquid heliums located below the superconducting coil in the lower helium container do not immerse the superconducting coil directly, so that the use efficiency of liquid helium can be improved and the liquid helium evaporation consumption can be afforded. There is still room for improvement.

  From the above, in order to realize EPI in an open MRI apparatus using a superconducting magnet with an open structure, the static magnetic field intensity that can obtain a sufficient S / N signal intensity with one nuclear spin excitation, In addition to the magnet performance with high static magnetic field uniformity that does not attenuate the NMR signal due to the inhomogeneous component of the static magnetic field, there is a superconducting magnet with an open structure that has a margin for heat entry due to eddy current and such a superconducting magnet. The MRI apparatus used is required.

Therefore, the present invention has been made in view of the above viewpoints, and the object of the present invention applied to an open-core air-core type superconducting magnet and an MRI apparatus using the same are as follows. That is, the first purpose is to prevent the consumption of the rim to the liquid even if heat is generated by the eddy current inside the superconducting magnet, making the replenishment work substantially unnecessary, and maintaining the superconducting magnet performance stably. Thus, an open structure superconducting magnet that improves the efficiency of inspection is provided.

A second object is to provide a superconducting magnet having an open structure that can increase the use efficiency of liquid helium for cooling the superconducting coil. A third object is to provide two helium containers in the superconducting magnet. The amount of liquid helium is measured at a predetermined time interval, the measured value is recorded, and the amount of liquid helium in the two helium containers is managed, so that the operating state of the liquid helium consumption reduction system can be remotely controlled. Is to provide a means of monitoring.
A fourth object is to provide an open MRI apparatus that has the above-described superconducting magnet and that does not consume rims in liquid even when high-speed imaging such as EPI is performed.

An open superconducting magnet to which the present invention for solving the above problems is applied is configured as follows. That is,
(1) A superconducting magnet in which a pair of cryostats having a liquid refrigerant container in which a superconducting coil is incorporated is vertically opposed to each other with an imaging space in which a subject is disposed, and the superconducting coil in a superconducting state. means for connecting the upper and lower liquid cryogen vessels to inject beneath the liquid refrigerant container to the liquid refrigerant for maintaining the temperature from above the liquid cryogen vessel, a gas in which the liquid refrigerant is vaporized is disposed in the cryostat again In the superconducting magnet apparatus provided with a cooling means for condensing into liquid, the connecting means has upper and lower opening ends at positions above the upper end surfaces of the superconducting coils disposed in the upper and lower liquid refrigerant containers, respectively. Connected .

In particular, the cryostat has an annular shape having a through hole in its central portion.
As a result, when the liquid refrigerant is vaporized by the heat generated by the eddy current in the cryostat generated by the operation of the gradient magnetic field coil, the liquid refrigerant corresponding to the vaporization is constantly replenished from the upper liquid refrigerant container to the lower liquid refrigerant container via the connecting means. Is done. On the other hand, the upper liquid refrigerant container is always replenished with the liquid refrigerant by the cooling means for condensing and liquefying the vaporized refrigerant gas. In particular, in the case of an annular cryostat having a through hole in the central portion, a higher static magnetic field uniformity can be easily achieved in addition to the above effects. As a result, the first object of the present invention can be achieved.

(2) In a preferred embodiment of the present invention, the capacity of the lower liquid refrigerant container is made smaller than the capacity of the upper liquid refrigerant container. Specifically, the vertical length of the lower liquid refrigerant container, not shorter than the vertical length of the upper liquid cryogen vessel. Alternatively, a recess is formed in the bottom surface of the lower liquid refrigerant container.
By these, the capacity | capacitance of a lower liquid refrigerant | coolant container, especially the capacity | capacitance of the lower part of a superconducting coil can be made small, and the amount of liquid helium which does not immerse a superconducting coil directly can be reduced. As a result, the second object of the present invention can be achieved.

(3) Further, in a preferred embodiment of the present invention, the lower liquid refrigerant container has at least one gas reservoir therein .
As a result, the evaporated liquid refrigerant gas stays in the gas reservoir, so that the liquid refrigerant originally contained therein is driven out, and the lower superconducting coil is immersed in the liquid refrigerant for a long time.
Alternatively, the liquid refrigerant that can no longer be accommodated in the lower liquid refrigerant container flows into the upper liquid refrigerant container through the connecting pipe, and the superconducting coil in the upper liquid refrigerant container is immersed and directly cooled. Therefore, liquid helium that does not directly immerse the superconducting coil can be effectively used. As a result, the second object of the present invention can be achieved.

(4) Moreover, the preferable embodiment of this invention is provided with the display means which displays the measurement result of the liquid quantity of the said liquid refrigerant, and the means to measure the liquid quantity of the said liquid refrigerant at least inside the said upper liquid refrigerant container. . Further, the cooling means includes a monitoring means for the operating state and a timer means for integrating the operating time, at least the upper liquid refrigerant container includes a pressure sensor therein, the display means includes the monitoring means, the timer, and the At least one of the output values of the pressure sensor and their change values is displayed . And means for issuing an alarm when the monitoring information of the cooling means, the liquid amount of the liquid refrigerant, the internal pressure of the liquid refrigerant container, each measured value of the timer or a change value thereof exceeds a preset threshold value, Means for transmitting the measured value or change value and the alarm to a remote location .
As a result, it is possible to operate while always grasping the internal state of the superconducting magnet, and it is possible to respond immediately when a problem occurs. As a result, the third object of the present invention can be achieved.

(5) Moreover, the preferable embodiment of this invention is set as the MRI apparatus provided with the superconducting magnet which has the structure of said (1) thru | or (4) .
According to this, imaging using a pulse sequence that switches a large-amplitude gradient magnetic field such as EPI at high speed is performed, and evaporation of liquid refrigerant is promoted due to eddy current generated by application of such a gradient magnetic field. Even if it is done, loss of the liquid refrigerant does not occur and the inspection can be performed stably. As a result, the fourth object of the present invention can be achieved.

  According to the present invention, in an air-core type superconducting magnet having an open structure capable of achieving high magnetic field strength and high magnetic field uniformity, rim consumption in liquid is not substantially generated even when high-speed imaging is performed. At the same time, the use efficiency of liquid helium can be increased, the liquid helium replenishment operation can be substantially eliminated, and the performance of the superconducting magnet can be stably maintained.

  Furthermore, according to the present invention, information necessary for grasping the liquid refrigerant amount of the superconducting magnet and other magnet operating conditions is automatically measured and recorded at predetermined time intervals, and within a predetermined allowable range. By determining whether or not there is an alarm display, it is possible to appropriately grasp the operating state of the superconducting magnet. Furthermore, since the operating state of the superconducting magnet can be ascertained from a remote location, it is not too late to deal with an abnormality and maintenance service for preventive maintenance is also possible.

  In an open MRI apparatus using a superconducting magnet to which the present invention is applied, it is possible to improve the efficiency of examination by high-speed imaging and to perform advanced diagnostic functions by high-functional imaging modes such as water / fat separation, and superconductivity It becomes possible to perform a stable inspection while constantly monitoring the operating state of the magnet.

Hereinafter, embodiments of the present invention will be described with reference to the accompanying drawings. Note that components having the same function are denoted by the same reference symbols throughout the drawings for describing the embodiments of the invention, and the repetitive description thereof is omitted.
First, an overall outline of an open MRI apparatus using a superconducting magnet having an open structure to which the present invention is applied will be described with reference to FIGS.

  A magnet for generating a magnetic field of the MRI apparatus shown in FIG. 1 includes an upper cryostat 102 and a lower cryostat 103 with an imaging space in which the subject 101 is placed interposed therebetween. For this reason, the front, rear, left and right sides of the shooting space are greatly open. Each of the upper cryostat 102 and the lower cryostat 103 incorporates a superconducting coil (not shown in the figure), and generates a magnetic field strength of, for example, 1.0 Tesla at the center of the imaging space, and its magnetic field uniformity. Achieves 2 ppm or less in a spherical space with a diameter of 40 centimeters, for example. The upper cryostat 102 and the lower cryostat 103 have a connecting pipe 104, which allows connection of the upper and lower superconducting coils by connecting the upper and lower cryostats, and has a function of circulating liquid helium described in detail later.

  A refrigerator 105 is attached to the upper part of the upper cryostat 102, and functions to condense the evaporated helium gas and return it to liquid helium together with the compressor 106 that drives the refrigerator 105. In addition to this, the compressor 106 is provided with a timer function for integrating the operation time of the refrigerator 105, a sensor function for monitoring the operation state of the refrigerator 105, and a function for outputting the results.

  Further, the upper cryostat 102 and the lower cryostat 103 each incorporate a sensor (for example, a liquid level sensor, not shown) that measures the amount of liquid helium, and the upper cryostat 102 has a pressure sensor above it. (Not shown in the figure) is incorporated. The output signals of these sensors are input to the cryostat control unit 107, changed to appropriate numerical values, and output. Since the upper and lower cryostats are connected by the connecting pipe 104 and liquid helium is circulated between the upper and lower cryostats, the sensor for measuring the amount of liquid helium may be disposed only in the upper cryostat 102.

  A gradient coil 108 that generates a gradient magnetic field is attached to the inside of the magnet. The gradient magnetic field coil 108 is a flat coil so as not to hinder the open structure of the magnet. A pair of upper and lower coils are stacked with x, y and z coils (not distinguished in the figure) that generate gradient magnetic fields in three axial directions orthogonal to each other. For example, when a current is applied to the upper z coil and the lower z coil, the upper coil generates a magnetic field so as to generate a magnetic flux in the same direction as the magnetic flux generated by the magnet, and the lower coil is 180 degrees opposite to that. Generate magnetic flux. As a result, a gradient magnetic field is created in which the magnetic flux density decreases linearly from above to below the vertical axis (z axis) of the imaging space in which the subject 101 is placed. Similarly, the upper and lower coils are configured so that the magnetic flux density generated by the magnet can be changed linearly along the x-axis and y-axis, respectively. A gradient power amplifier unit 109 is connected to the gradient coil 108 so that currents are supplied to x, y, and z independently of each other. This gradient magnetic field power amplifier 109 has a switching operation and current intensity that can sufficiently withstand EPI measurement. That is, the gradient magnetic field has a performance of changing the gradient magnetic field from the plus maximum to the minus maximum at a speed of, for example, 100 microseconds with respect to the load of the gradient magnetic field coil 108. The gradient magnetic field coil 108 and the gradient magnetic field power amplifier 109 serve to specify the examination site of the subject 101 and to label position information on the subsequent NMR signal.

  A high-frequency coil 110 is attached further inside the gradient magnetic field coil 108. The high-frequency coil 110 is also a flat-plate coil so as not to hinder the open structure of the magnet. By applying a high-frequency current that matches the resonance frequency of a specific nucleus from the high-frequency power amplifier 111 to a pair of upper and lower coils, a substantially uniform high-frequency magnetic field is generated in the arrangement space of the subject 101. In the case of the present embodiment, the hydrogen nuclei contained in the tissue at the examination site of the subject 101 are resonantly excited by flowing a high-frequency current of 42 megahertz (resonance frequency of hydrogen nuclei under a magnetic field intensity of 1 Tesla).

  A receiving coil 112 for detecting an NMR signal is placed on the innermost side, that is, in the immediate vicinity of the subject 101. The receiving coil 112 has a function of detecting the magnetic behavior of the nuclear spin as an electric signal. The NMR signal detected as an electrical signal is input to the high frequency amplification unit 113. The high frequency amplification unit 113 amplifies and detects the weak NMR signal inputted, converts it into a digital signal suitable for computer processing, and outputs it.

  A computer 114 for controlling the operations of the gradient magnetic field power amplifier 109, the high-frequency power amplifier 111, and the high-frequency receiving unit 113 at predetermined time intervals is combined. Input / output signals of the computer 114 are connected to each unit as a system bus 115. On the other hand, the computer 114 converts the NMR signal converted into a digital signal into a spectrum or image for diagnosis and saves it in a memory device (not shown) in the computer 114, or stores it in the display device 116. Execute the process to be displayed. Further, the computer 114 is in charge of monitoring and recording the operation state of the MRI apparatus at regular intervals or at regular intervals, in addition to the control of the inspection sequence and the processing of NMR signals. In particular, in this embodiment, the operating state and operating time of the refrigerator 105 and the compressor 106 are measured and recorded in another area of the memory device. Also, the amount of liquid helium and the pressure of the cryostat are measured, for example, once / day, and the absolute value and rate of change are recorded. In addition, when the measured data exceeds a predetermined upper limit value or lower limit value, it has a function of displaying on the display device 116 as an alarm or generating an alarm sound. Furthermore, these monitoring data and alarms can be retrieved from the outside by remote control via a modem 117 connected to the computer 114.

  FIG. 2 is a diagram for explaining the operation of the GM refrigerator 105 shown in FIG. 1 and the compressor 106 that drives it. In the figure, there is a motor 301 at the top of the GM refrigerator 105, and there are a first stage 207 displacer 302 and a second stage 208 displacer 303 that move up and down by the rotation of the motor 301. Further, it has a mechanism of a high pressure valve 304 and a low pressure valve 305 that open and close in opposite phases in synchronization with the rotation of the motor 301. The outline of the operating principle of the GM refrigerator 105 is as follows. When the first stage displacer 302 and the second stage displacer 303 reach the top dead center, the high pressure valve 304 is opened, and the compressor 106 compresses it to about 2.4 megapascals, for example. High purity helium gas is injected into the displacer. As the first stage displacer 302 and the second stage displacer 303 descend, the helium gas expands and cools in the space of the regenerator material in each displacer, and is discharged from the low pressure valve 305 and returns to the compressor 106 in accordance with the upward movement of the displacer. . By repeating this process, the temperature of the regenerator material decreases, and the first stage 207 reaches a temperature of 50 degrees Kelvin and the second stage 208 reaches a temperature of 4 degrees Kelvin or less. As a result, the first stage 207 cools the radiant heat shield plate 212, and the second stage 208 cools and condenses the vaporized helium gas and returns it to the liquid helium in the upper helium container 203.

  The compressor 106 has functions of supplying a three-phase voltage to the motor 301 and compressing and cooling helium gas. Therefore, the GM refrigerator 105 is connected by the power cable 306 of the motor 301, the high pressure helium gas pipe 307, and the low pressure helium gas pipe 308. Further, the compressor 106 includes a power monitor circuit 309 for the motor 301, a helium gas pressure monitor 310, an integration timer 311 for recording the operation time of the GM refrigerator 105, and an interface circuit 312 for outputting these monitor signals to the computer 115. Is incorporated.

FIG. 3 is a flowchart showing an example of a program installed in the computer 115 for measuring values of various sensors attached to the magnet and determining an operating state. With the MRI apparatus shown in FIG. 1 installed in a medical institution, the following steps are executed. That is, the software timer in the computer 114 is set simultaneously with the start of operation in step 401.

  In step 402, the software timer reads the values of various sensors from the output interface of the compressor 106 and the cryocontrol unit 107 at regular intervals, and records the values and measurement date and time. In this embodiment, the pressure in the upper helium vessel 203 and the high pressure helium pressure in the compressor 106 are measured at a rate of once per hour, and the values are recorded. Further, the amount of liquid helium in the upper helium container 203 and the lower helium container 204 and the time of the integration timer 311 of the GM refrigerator 105 are measured once a day, and the values are recorded.

  In step 403, the measured values are compared with the values determined for each to determine whether the operating state of the magnet and the GM refrigerator 105 is normal or abnormal. That is, the amount of liquid helium in the upper helium vessel 203 is, for example, 30% or more above the connection portion of the pipe 205 (that is, 30% from the bottom when the height of the upper helium vessel 203 is 100%) or more. In the case of the lower helium vessel 204, it is determined whether the value of 100% is maintained.

  In step 404, the pressure of the helium gas in the upper helium vessel 203 balances the amount of helium vaporized by the amount of heat such as eddy current entering the upper cryostat 102 and the lower cryostat 103 and the amount of helium condensed in the GM refrigerator 105. Judge whether it is.

In step 405, in the case of the GM refrigerator 105 alone, it is determined whether the pressure of the high pressure helium is within a normal value of, for example, 2.3 megapascals to 2.4 megapascals.
In step 406, it is determined whether or not the time of the integration timer 311 exceeds, for example, 10,000 hours that require regular maintenance.

In step 407, when the determination results of 403 to 406 are outside the allowable range, warning information corresponding to the content is displayed on the display 116 as error information.
In step 408, these measurement values, measurement date / time, and determination result are output together to the modem 117, enabling remote monitoring outside the room where the MRI apparatus is installed or at a remote service station.

The first embodiment of the present invention will be described below. In the present embodiment, a superconducting magnet having a cylindrical cryostat having no through hole in the central portion is used.
FIG. 4 is a diagram showing a first example of the present embodiment, and is a diagram showing in detail a cross section of a superconducting magnet used in the MRI apparatus shown in FIG. In FIG. 4, an upper cryostat 102 and a lower cryostat 103 house an upper superconducting coil 201 and a lower superconducting coil 202 that generate a magnetic field, respectively. In the figure, the case of one coil is shown, but it is usually composed of a combination of a plurality of coils in order to satisfy the target specifications of magnetic field strength, magnetic field uniformity and leakage magnetic field. Outside the superconducting coil are an upper helium vessel 203 and a lower helium vessel 204 that store liquid helium. The upper helium vessel 203 and the lower helium vessel 204 are connected by a thin pipe 205. Here, the connection position of the upper helium container 203 and the pipe 205 is a position above the upper end surface of the upper superconducting coil 201 (for example, 30% from the bottom when the height of the upper helium container 203 is 100%). The same shall apply hereinafter). On the other hand, the connection between the lower helium vessel 204 and the pipe 205 is also connected to a position above the upper end surface of the lower superconducting coil 202 (actually, the uppermost portion of the lower helium vessel 204). Here, as shown in FIG. 4, the connection location between the liquid helium containers 203, 204 and the pipe 205, which are opposed to each other in the vertical direction, prevents the imaging space in which the subject is disposed from interfering with the helium containers 203, 204 as much as possible. It is necessary that it is in the vicinity of the periphery away from the center, preferably on the side surface.

  A GM refrigerator 105 is incorporated in the upper center of the upper helium vessel 203. The GM refrigerator 105 of this embodiment has two cooling stages, for example, the first stage 207 has a cooling capacity of 50 watts at 50 degrees Kelvin temperature, and the second stage 208 has a cooling capacity of 2 watts at 4 degrees Kelvin temperature. Have. The second stage 208 of the GM refrigerator 105 is located directly in the upper helium vessel 203, and the helium gas is cooled by heat exchange on the surface of the second stage 208. In the embodiment, the method of directly cooling the helium gas is used, but it is also possible to cool the helium gas indirectly by contacting the second stage 208 with a good part of the heat conduction of the helium vessel 203. . Since the boiling point of helium gas is 4.2 degree Kelvin temperature, helium gas is recondensed on the surface of the second stage 208 to become liquid helium, and accumulates in the upper helium container 203.

  A helium liquid level sensor 209 for detecting the liquid level of liquid helium is incorporated in each of the upper helium container 203 and the lower helium container 204. Further, a pressure sensor 210 is incorporated in the upper part of the upper helium vessel 203. Outputs of these sensors are collected at a service port 211 attached to the upper helium vessel 203 and connected to the cryocontrol unit 107.

  A radiation heat shield plate 212 exists outside the upper helium vessel 203 and the lower helium vessel 204. This radiant heat shield plate 212 is in thermal contact with the second stage 207 of the GM refrigerator 105 at the top, so that the overall temperature becomes the 50 degree Kelvin temperature of the second stage 207, for example, 1 mm with good heat conduction Made of thick pure aluminum board. Radiant heat shield plate 212 is provided with slits (not shown in the figure) at several locations to prevent large eddy currents from being generated due to magnetic field changes during quenching of superconducting coils 201 and 202, and to deform itself. Reduced. For this reason, the magnetic flux change generated by the gradient magnetic field coil 108 passes through the radiant heat shield plate 212, and an eddy current is generated in the upper helium vessel 203 and the lower helium vessel 204.

  On the outer side of the radiation shield plate 212, a vacuum vessel (shared with the numbers 102, 103, and 104) made of stainless steel having a thickness of 15 mm, for example, is provided. The gaps between the vacuum vessel and the upper helium vessel 203, the lower helium vessel 204, and the pipe 205 form a vacuum layer, which prevents heat from entering together with the radiation shield plate 212 present in the middle.

  In this way, the pipe 205 and the GM refrigerator 105 are combined to form a liquid helium liquid surface where the connection position (30% position) of the pipe 205 in the upper helium vessel 203, that is, from the upper end surface of the upper superconducting coil 201. If liquid helium is injected so as to be on the top, all the helium gas generated in the lower helium container 204 gathers on the upper helium container 203 through the pipe 205, and conversely, the liquid helium passes through the pipe 205 and the upper helium The lower helium container 204 is replenished from the container 203. At the same time, helium gas collected at the upper part of the upper helium container 203 can be recondensed in the second stage 208 of the GM refrigerator 105 and stored in the upper helium container 203.

  Further, considering the magnetic field generation efficiency, it is desirable that the position of the superconducting coil be as close as possible to the imaging space in which the subject 101 is disposed. That is, the upper superconducting coil 201 is disposed as low as possible in the upper helium vessel 203, and the lower superconducting coil 204 is disposed as high as possible in the lower helium vessel 204. With the configuration of the present embodiment described above, the liquid helium in the upper helium vessel 203 is maintained at 30% or more higher than the upper end surface of the superconducting coil 201, and the lower helium vessel 204 is always filled with liquid helium. . Furthermore, even if the superconducting coil is disposed at the position where the magnetic field generation efficiency is the highest, that is, the upper superconducting coil 201 is disposed at the lowermost portion of the upper helium vessel 203 and the lower superconducting coil 202 is disposed at the uppermost portion of the lower helium vessel 204, Can be infiltrated into liquid helium and kept stable at 4.2 degrees Kelvin temperature which maintains the superconducting state.

Next, another example of the first embodiment will be described with reference to FIG. FIG. 5 is a cross-sectional view showing only the lower part of the superconducting magnet of FIG.
FIG. 5 (a) is a second embodiment, which is an example in which the height (length in the vertical direction) of the lower helium vessel 204 is shorter than that of the upper helium vessel. As a result, the height of the lower radiant heat shield plate 212 and the vacuum vessel 103 is also shortened. With this structure, the amount of liquid helium below the lower superconducting coil 202 can be reduced, so that the amount of liquid helium that does not directly immerse the superconducting coil 202 can be reduced.

  FIG. 5B shows a third embodiment, which is an example in which a depression 214 is provided on the bottom surface of the lower helium container 204. With this structure, the amount of liquid helium below the lower superconducting coil 202 can be reduced as in the second embodiment, so that the amount of liquid helium that does not directly immerse the superconducting coil 202 can be reduced. In general, the strength of the gradient magnetic field is weak at the central portion of the helium vessel and strong near the outer periphery. Therefore, the eddy current generated on the bottom surface of the helium vessel is small at the central portion and increases near the outer periphery. Therefore, by setting the shape of the depression so as to be convex toward the imaging space near the center of the helium container, the capacity of the helium container can be reduced without substantially increasing the generation of eddy currents.

FIG. 5C shows a fourth embodiment, which is an example in which at least one gas reservoir 215 is provided in the lower helium container 204. This gas reservoir 215 has a convex shape on the imaging space side so that the helium gas evaporated in the lower helium container stays inside. As the evaporated helium gas stays in the gas reservoir 215, the liquid helium that was originally in the gas reservoir 215 is expelled. As a result, the lower superconducting coil 202 is immersed in liquid helium for a long time. Alternatively, liquid helium that can no longer fit in the lower helium vessel 204 flows into the upper helium vessel 203 through the pipe 205, and the superconducting coil 201 in the upper helium vessel 203 is immersed and directly cooled. In this way, the liquid helium in the lower helium vessel 204 can be effectively used to provide a margin for heat entry due to eddy current.
Note that any combination of the second to fourth embodiments can be applied.

Next, a second embodiment of the present invention will be described. In the present embodiment, a superconducting magnet having an annular cryostat having a through hole in the central portion is used, and this through hole is basically hollow and no pole piece is disposed.
FIG. 6 is a diagram showing in detail the cross section of the superconducting magnet of the first example of the present embodiment. Compared to FIG. 4, the upper and lower cryostats 102 and 103 have through holes 220 at the center portions thereof. Therefore, the position of the GM refrigerator 105 and the liquid level sensor 209 has been changed so as to avoid the through hole 220, but is not limited to this arrangement, the GM refrigerator 105 is placed on the upper surface of the upper cryostat 102. The liquid level sensor 209 may be disposed from the upper surface to the bottom surface of the helium containers 203 and 204. The other parts are the same as in FIG.

Also in the second embodiment, the structure of the lower helium vessel 204 can be made different from that of the upper helium vessel 203 as in the second to fourth examples of the first embodiment.
FIG. 7 is a sectional view showing only the lower part of the superconducting magnet of FIG.
FIG. 7 (a) is a second embodiment, and in the same way as FIG. 5 (a), the height of the lower helium vessel 204 (length in the vertical direction) is shorter than that of the upper helium vessel 203. It is. The effect is also the same as in FIG.

FIG. 7B is a third embodiment, and is an example in which a recess 214 is provided on the bottom surface of the lower helium container 204, as in FIG. 5B. The effect is also the same as in FIG. 5 (b).
FIG. 7 (c) is a fourth embodiment, and is an example in which at least one gas reservoir 215 is provided in the lower helium container 204, as in FIG. 7 (c). The effect is also the same as in FIG. 5 (c).
As in the case of FIG. 5, any combination of the second to fourth embodiments can be applied.

1 is an overall configuration diagram of an open MRI apparatus using the present invention. FIG. 2 is a connection diagram of a GM refrigerator and a compressor incorporated in the superconducting magnet of FIG. The flowchart of a magnet operation state monitor and a state determination program. FIG. 2 is an internal structural diagram of a superconducting magnet used in the open MRI apparatus of FIG. 1 (first example relating to the first embodiment of the present invention). 6 shows another example of the lower helium container in the first embodiment of the present invention. (a) is an example in which the height of the lower helium container is shortened, (b) is an example in which a recess is provided on the bottom surface of the lower helium container, and (c) is an example in which a gas reservoir is provided in the lower helium container. FIG. 5 is an internal structure diagram of a superconducting magnet in a second embodiment of the present invention. 10 shows another example of the lower helium container in the second embodiment of the present invention. (a) is an example in which the height of the lower helium container is shortened, (b) is an example in which a recess is provided on the bottom surface of the lower helium container, and (c) is an example in which a gas reservoir is provided in the lower helium container.

Explanation of symbols

  102 Upper cryostat, 103 Lower cryostat, 104 Connecting pipe, 105 Refrigerator, 106 Compressor, 107 Cryo control unit, 109 Gradient magnetic field power amplifier, 111 High frequency power amplifier, 113 High frequency amplification unit, 114 Computer, 116 Display device, 117 Modem , 203 Upper helium vessel, 204 Lower helium vessel, 205 pipe, 207 First stage of refrigerator, 208 Second stage of refrigerator, 209 Liquid level sensor, 210 Pressure sensor, 211 Service port, 212 Radiation heat shield plate

Claims (7)

A pair of cryostats having a liquid refrigerant container with a superconducting coil incorporated therein, a superconducting magnet disposed vertically opposite to each other with an imaging space in which the subject is disposed, and the superconducting coil maintained at a superconducting temperature. Means for connecting the upper and lower liquid refrigerant containers so as to inject liquid refrigerant from the upper liquid refrigerant container into the lower liquid refrigerant container, and cooling disposed in the cryostat to condense the gas evaporated by the liquid refrigerant into liquid again and means,
In less than the amount superconducting magnet apparatus of the capacity the upper liquid refrigerant container of the lower liquid refrigerant container, at least the upper liquid coolant container superconducting magnet apparatus characterized by comprising a pressure sensor therein.   2. The superconducting magnet device according to claim 1, wherein a depression is formed on a bottom surface of the lower liquid refrigerant container.   The superconducting magnet apparatus according to claim 1 or 2, wherein the lower liquid refrigerant container has at least one gas reservoir therein.   The superconducting magnet device according to any one of claims 1 to 3, wherein at least a means for measuring the liquid amount of the liquid refrigerant is displayed in the upper liquid refrigerant container, and a measurement result of the liquid amount of the liquid refrigerant is displayed. A superconducting magnet device comprising display means for performing the above operation. A superconducting magnet apparatus according to claim 4, wherein the cooling means comprises a timer means for accumulating the operating time monitoring means of the operating state, before Symbol display means said monitoring means and said timer output value of said pressure sensor And a superconducting magnet device that displays at least one of the change values thereof.   6. The superconducting magnet device according to claim 5, wherein the monitoring information of the cooling means, the liquid amount of the liquid refrigerant, the internal pressure of the liquid refrigerant container, each measured value of the timer, or a change value thereof exceeds a preset threshold value. A superconducting magnet apparatus comprising: means for issuing an alarm when the alarm occurs; and means for transmitting the measured value or change value and the alarm to a remote place. Magnetic resonance imaging apparatus having a superconducting magnet apparatus according to any one of claims 1 to 6.

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