JP2009034479A - Magnetic resonance imaging apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To perform an efficient imaging using hardware up to the limit. <P>SOLUTION: This magnetic resonance imaging apparatus obtains temperature information providing indications of the temperatures of a gradient magnetic field coil unit 6 and a gradient magnetic field amplifier 7 from temperature sensors 18, 19 and 20 and a current monitor 21. A host computer 16 detects the occurrence of an alert state where the temperatures of the gradient magnetic field coil unit 6 and the gradient magnetic field amplifier 7 are likely to rise enough to affect the imaging, on the basis of the obtained information, and controls the imaging so as to suppress temperature rise of the gradient magnetic field coil unit 6 and the gradient magnetic field amplifier 7 according to the detection. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates to a magnetic resonance imaging apparatus that performs magnetic resonance imaging using hardware such as a gradient magnetic field coil and a gradient magnetic field amplifier that may increase in temperature with an imaging operation.

  In a magnetic resonance imaging apparatus, when performing diffusion imaging or the like in which a large load is applied to a gradient magnetic field, the temperature of hardware such as a gradient magnetic field coil and a gradient magnetic field amplifier may greatly increase. Such a rise in the temperature of the hardware may cause a situation where shooting cannot be continued.

Based on the current waveform supplied to the gradient coil according to the tentative protocol, the change in the residual heat quantity of the gradient coil is predicted, and based on this, the protocol is changed so that the residual heat quantity of the gradient coil does not exceed the abort level. There is known a technique for enabling an operator to perform the above (for example, see Patent Document 1). Japanese Patent Application Laid-Open No. H10-228561 also discloses that the shooting is stopped when the residual heat amount of the gradient coil after the start of shooting exceeds the abort level.
US Pat. No. 6,977,501

  However, according to the technique described above, the load on the gradient magnetic field coil may differ from the predicted value, and in this case, the predicted value of the residual heat quantity of the gradient magnetic field coil differs from the actual residual heat quantity. When the predicted value is estimated to be small, if shooting is performed according to a protocol determined based on the predicted value, the residual heat amount exceeds the abort level, and there is a high possibility that shooting will be stopped. . If the predicted value is estimated to be large, the protocol determined based on the predicted value is determined to be inefficient because the hardware is determined to have a margin more than necessary with respect to the limit. turn into. That is, when the prediction accuracy is low, efficient shooting cannot be performed.

  The present invention has been made in view of such circumstances, and an object of the present invention is to provide a magnetic resonance imaging apparatus capable of performing efficient imaging using hardware to the limit. It is in.

  The magnetic resonance imaging apparatus according to the first aspect of the present invention is a magnetic resonance imaging apparatus that performs imaging by a magnetic resonance imaging method using hardware whose temperature may increase with an imaging operation. The acquisition means for acquiring information serving as an index of the temperature during the shooting, and the acquired information on the occurrence of a warning situation that may increase so that the temperature of the hardware affects the shooting And a control unit that controls the photographing so as to suppress a rise in the temperature of the hardware in response to detection of occurrence of the warning state.

  A magnetic resonance imaging apparatus according to a second aspect of the present invention is a magnetic resonance imaging method using a gradient magnetic field coil that generates a gradient magnetic field upon supply of electric power, and a gradient magnetic field amplifier that supplies the electric power to the gradient magnetic field coil. In the magnetic resonance imaging apparatus that performs imaging by the cooling device, a cooling device that cools a cooling medium for cooling the gradient magnetic field coil and the gradient magnetic field amplifier, a temperature of the cooling medium cooled by the cooling device, and the gradient magnetic field coil The temperature of the cooling medium after being used for cooling the temperature, the temperature of the cooling medium after being used for cooling the gradient magnetic field amplifier, or the current supplied to the gradient coil by the gradient magnetic field amplifier An acquisition unit that acquires at least one of the values, and one of the values acquired by the acquisition unit Means for detecting occurrence of a warning situation in response to one exceeding a first threshold value associated with each value, and said gradient magnetic field in response to detection of occurrence of the warning situation Any one of the means for controlling the imaging so as to suppress the temperature rise of the coil and the gradient magnetic field amplifier, and the value acquired by the acquisition means is associated with each value and is more than the first threshold value, respectively. Means for detecting the occurrence of a limit situation in response to exceeding a largely defined second threshold; and means for temporarily stopping the imaging in response to the occurrence of the limit situation being detected. Prepare.

  According to the present invention, efficient shooting can be performed using hardware to the limit.

  Hereinafter, an embodiment of the present invention will be described with reference to the drawings.

  FIG. 1 is a diagram showing a schematic configuration of a magnetic resonance imaging apparatus (MRI apparatus) 100 according to the present embodiment.

  The MRI apparatus 100 includes a bed unit on which a subject 200 is placed, a static magnetic field generation unit that generates a static magnetic field, a gradient magnetic field generation unit for adding position information to the static magnetic field, and a transmission / reception unit that transmits and receives high-frequency signals. A control / arithmetic unit that controls the entire system and image reconstruction, a cooling unit that cools the gradient magnetic field generation unit, and an information acquisition unit that acquires temperature information about the gradient magnetic field generation unit. The MRI apparatus 100 includes a magnet 1, a static magnetic field power source 2, a shim coil 3, a shim coil power source 4, a top plate 5, a gradient magnetic field coil unit 6, a gradient magnetic field amplifier 7, an RF coil unit 8, and a transmitter as constituent elements of these parts. 9T, receiver 9R, sequencer (sequence controller) 10, arithmetic unit 11, storage unit 12, display 13, input device 14, sound generator 15, host computer 16, chilled water device 17, temperature sensors 18, 19, 20 and It has a current monitor 21. The MRI apparatus 100 is connected to an electrocardiogram measurement unit that measures an ECG signal as a signal representing the cardiac time phase of the subject 200.

The static magnetic field generation unit includes a magnet 1 and a static magnetic field power supply 2. For example, a superconducting magnet or a normal conducting magnet can be used as the magnet 1. The static magnetic field power supply 2 supplies a current to the magnet 1. Thus, the static magnetic field generator generates a static magnetic field B ₀ in a cylindrical space (diagnostic space) into which the subject 200 is sent. The magnetic field direction of the static magnetic field B ₀ substantially coincides with the axial direction (Z-axis direction) of the diagnostic space. A shim coil 3 is further provided in the static magnetic field generator. The shim coil 3 generates a correction magnetic field for making the static magnetic field uniform by supplying current from the shim coil power supply 4 under the control of the host computer 16.

  The bed part sends the top plate 5 on which the subject 200 is placed into the diagnostic space, or extracts it from the diagnostic space.

The gradient magnetic field generation unit includes a gradient magnetic field coil unit 6 and a gradient magnetic field amplifier 7. The gradient coil unit 6 is disposed inside the magnet 1. The gradient coil unit 6 includes three sets of coils 6x, 6y, and 6z for generating respective gradient magnetic fields in the X-axis direction, the Y-axis direction, and the Z-axis direction that are orthogonal to each other. The gradient magnetic field amplifier 7 supplies a pulse current for generating a gradient magnetic field to the coil 6x, the coil 6y, and the coil 6z under the control of the sequencer 10. Thus, the gradient magnetic field generation unit controls the pulse current supplied from the gradient magnetic field amplifier 7 to the coils 6x, 6y, 6z, and thereby each gradient in the three axes (X axis, Y axis, Z axis) directions which are physical axes. By synthesizing the magnetic fields, respective gradient magnetic fields in the logical axis direction composed of the slice direction gradient magnetic field G _S , the phase encode direction gradient magnetic field G _E , and the readout direction (frequency encode direction) gradient magnetic field G _R which are orthogonal to each other are arbitrarily set. To do. The gradient magnetic fields G _S , G _E , and G _R in the slice direction, the phase encoding direction, and the reading direction are superimposed on the static magnetic field B ₀ .

  The transmission / reception unit includes an RF coil unit 8, a transmitter 9T, and a receiver 9R. The RF coil unit 8 is disposed in the vicinity of the subject 200 in the diagnostic space. The transmitter 9T and the receiver 9R are connected to the RF coil unit 8. The transmitter 9T and the receiver 9R operate under the control of the sequencer 10. The transmitter 9T supplies the RF coil unit 8 with an RF current pulse having a Larmor frequency for generating nuclear magnetic resonance (NMR). After receiving MR signals such as echo signals received by the RF coil unit 8, the receiver 9R performs various signal processing such as preamplification, intermediate frequency conversion, phase detection, low frequency amplification, or filtering. , A / D conversion to generate digital data (raw data).

  The control / arithmetic unit includes a sequencer 10, an arithmetic unit 11, a storage unit 12, a display device 13, an input device 14, a sound generator 15, and a host computer 16.

  The sequencer 10 includes a CPU and a memory. The sequencer 10 stores the pulse sequence information sent from the host computer 16 in a memory. The CPU of the sequencer 10 controls the operations of the gradient magnetic field amplifier 7, the transmitter 9T, and the receiver 9R according to the sequence information stored in the memory, and once inputs the raw data output from the receiver 9R, and calculates this Transfer to unit 11. Here, the sequence information is all information necessary for operating the gradient magnetic field amplifier 7, the transmitter 9T, and the receiver 9R according to a series of pulse sequences. For example, pulses applied to the coils 6x, 6y, and 6z. Information on current intensity, application time, application timing, and the like is included. The sequence information includes information for realizing diffusion weighted imaging by a DWI (diffusion weighted imaging) sequence.

  The arithmetic unit 11 inputs the raw data output from the receiver 9 </ b> R through the sequencer 10. The arithmetic unit 11 places the input raw data in k space (also called Fourier space or frequency space) set in the internal memory, and applies the data arranged in the k space to two-dimensional or three-dimensional Fourier transform. Then, it is reconstructed into real space image data. In addition, the arithmetic unit 11 can also execute data composition processing and difference calculation processing (including weighted difference processing) as necessary. This synthesis processing includes processing for adding pixel values for each pixel, maximum value projection (MIP) processing, and the like. As another example of the above synthesis process, after aligning the axes of a plurality of frames in Fourier space, the raw data of the plurality of frames may be synthesized to obtain one frame of raw data. Note that the addition processing includes simple addition processing, addition averaging processing, weighted addition processing, and the like.

  The storage unit 12 stores the reconstructed image data and the image data that has been subjected to the above-described combining process and difference process.

  The display 13 displays various images to be presented to the user under the control of the host computer 16. A display device such as a liquid crystal display can be used as the display 13.

  The input device 14 inputs various types of information such as parameter information for selecting the synchronization timing desired by the operator, scan conditions, pulse sequences, information relating to image synthesis and difference calculation. The input unit 14 sends the input information to the host computer 16. The input device 14 is appropriately provided with a pointing device such as a mouse or a trackball, a selection device such as a mode change switch, or an input device such as a keyboard.

  The voice generator 15 emits a breath holding start and breath holding end message as a voice when instructed by the host computer 16.

  The host computer 16 has various functions that are realized by executing predetermined software procedures. One of these functions is to command the pulse sequence information to the sequencer 10 and control the overall operation of the apparatus. One of the functions described above is based on the temperature information acquired by the information acquisition unit, and the occurrence of a warning situation that may rise to such an extent that the temperature of the gradient magnetic field coil unit 6 and the gradient magnetic field amplifier 7 affects imaging. To detect. One of the above functions controls imaging so as to suppress the temperature rise of the gradient magnetic field coil unit 6 and the gradient magnetic field amplifier 7 in response to detection of occurrence of a warning situation. One of the above functions is to detect the occurrence of a limit situation where the temperature of the gradient magnetic field coil unit 6 or the gradient magnetic field amplifier 7 has increased so as to affect the imaging based on the temperature information acquired by the information acquisition unit. One of the above functions temporarily stops photographing in response to detection of occurrence of a limit situation.

  The cooling unit includes a chilled water device 17. The cold water device 17 cools the cooling water. The cooling water flows out from the chilled water device 17 to a conduit arranged so as to pass through the gradient coil unit 6 and the gradient magnetic field amplifier 7. The cooling water heated by cooling the gradient magnetic field coil unit 6 and the gradient magnetic field amplifier 7 is returned to the cold water device 17 through a conduit.

  The information acquisition unit includes temperature sensors 18, 19, 20 and a current monitor 21. The temperature sensor 18 detects the temperature of the cooling water flowing out from the chilled water device 17. The temperature sensor 19 detects the temperature of the cooling water flowing out from the gradient coil unit 6. The temperature sensor 20 detects the temperature of the cooling water flowing out from the gradient magnetic field amplifier 7. The current monitor 21 monitors a current value output from the gradient magnetic field amplifier 7 to the gradient coil unit 6 and calculates a feature value for the current in a recent fixed period (for example, 1 minute). As the feature value, a square integral value or an absolute value can be used. The temperature sensors 18, 19, and 20 provide the detected temperature to the host computer 16, and the current monitor 21 supplies the monitored feature value to the host computer 16 as temperature information. The temperature detected by the temperature sensor 18 is information representing how much the gradient magnetic field coil unit 6 and the gradient magnetic field amplifier 7 are cooled by the cooling water. The temperature detected by the temperature sensor 19 is information indicating how much the cooling water has been heated by the gradient coil unit 6. The temperature detected by the temperature sensor 20 is information indicating how much the cooling water has been heated by the gradient magnetic field amplifier 7. The characteristic value calculated by the current monitor 21 is information representing the amount of heat generated for the gradient magnetic field amplifier 7 to generate a pulse current and the amount of heat generated for the gradient coil unit 6 to generate a gradient magnetic field. Therefore, all of these temperature information is an index of the temperature of the gradient magnetic field coil unit 6 and the gradient magnetic field amplifier 7.

  The electrocardiogram measurement unit includes an ECG sensor 22 and an ECG unit 23. The ECG sensor 22 is attached to the body surface of the subject 200 and detects the ECG signal of the subject 200 as an electrical signal (hereinafter referred to as a sensor signal). The ECG unit 23 performs various processes including a digitization process on the sensor signal, and then outputs them to the host computer 16 and the sequencer 10. As this electrocardiograph, for example, a vector electrocardiograph can be used. The sensor signal from the electrocardiogram measurement unit is used as necessary by the sequencer 10 when a scan synchronized with the cardiac time phase of the subject 200 is executed.

  Next, the operation of the MRI apparatus 100 configured as described above will be described.

  The MRI apparatus 100 can perform imaging in various sequences realized by an existing MRI apparatus, but description thereof will be omitted. Here, an operation related to temperature management of the gradient magnetic field generation unit when photographing is performed will be described. Note that temperature management can be performed regardless of which sequence is used for imaging, and imaging is performed in a specific sequence such as a sequence in which a gradient magnetic field such as DWI is heavily loaded. It can also be done only if.

  When shooting is started, the host computer 16 starts processing as shown in FIG. 2 in parallel with this.

  In step Sa1, the host computer 16 acquires temperature information from the temperature sensors 18, 19, 20 and the current monitor 21, respectively. In step Sa2, the host computer 16 confirms whether or not the gradient magnetic field generation unit is in a warning state based on the temperature information acquired in step Sa1. The host computer 16 determines that it is in the alert state when at least one of the following conditions (1) to (4) is satisfied.

(1) sum_crt_wng1 ≦ sum_crt
(2) amptmp_out_wng1 ≦ amptmp_out
(3) coiltmp_out_wng1 ≦ coiltmp_out
(4) chillertmp_out_wng1 ≦ chillertmp_out
However, sum_crt is a feature value calculated by the current monitor 21, amptmp_out is a temperature detected by the temperature sensor 20, coiltmp_out is a temperature detected by the temperature sensor 19, chillertmp_out is a temperature detected by the temperature sensor 18, and sum_crt_wng1 is a feature A warning value of value sum_crt, amptmp_out_wng1 is a warning value of temperature amptmp_out, coiltmp_out_wng1 is a warning value of temperature coiltmp_out, and chillertmp_out_wng1 is a warning value of temperature chillertmp_out.

  If it is determined that it is not in the alert state, the host computer 16 proceeds from step Sa2 to step Sa3. In step Sa3, the host computer 16 waits for a predetermined waiting time T1. When waiting for the waiting time T1, the host computer 16 returns to step Sa1. Thus, the host computer 16 repeatedly acquires temperature information at the interval of the waiting time T1 in a state that is not in the alert state, and confirms whether or not it is in the alert state.

  If it is in the alert state, the host computer 16 proceeds from Step Sa2 to Step Sa4. In step Sa4, the host computer 16 waits for a change in the shooting operation. The change of the photographing operation is, for example, the change of the average in the averaging scan, the change of the slice to be imaged, or the change of the dynamic time phase in the dynamic scan. If the change of the shooting operation has come, the host computer 16 proceeds from step Sa4 to step Sa5. In step Sa <b> 5, the host computer 16 instructs the sequencer 10 to extend the repetition time TR in order to extend the duty related to the shooting being performed. Along with this, the host computer 16 controls the display unit 13 so as to display a warning indicating that the TR has been extended because of a warning state.

  Here, the extended TR is obtained from the relational expression between the predicted duty and the temperature rise, for example.

  That is, the extended TR can be obtained by the following equation.

TR after extension = current TR x ΔT / α
However, (alpha) is a heat | fever rise rate (degreeC / min) in the past 1 minute, and (DELTA) T is the warning state temperature range (limit value-warning value) (degreeC) of the parameter beyond the warning state.

  This TR control is performed at regular intervals, and the frequency may be changed when a warning state is reached.

  In addition, although the condition is represented by a simple mathematical expression here, there may be a case where a complicated behavior is exhibited such as when a delay occurs. For this reason, the TR extension coefficient and the like may be determined with reference to actual measurement data (change history curve measured in advance). Further, as a method of dynamic control of TR, TR may be unconditionally multiplied by a fixed value. Moreover, since it detects as heat, you may consider the delay by heat conduction.

  In step Sa6, the host computer 16 acquires temperature information from the temperature sensors 18, 19, 20 and the current monitor 21, respectively. Subsequently, in step Sa7 and step Sa8, the host computer 16 confirms whether or not the gradient magnetic field generation unit is in the limit state and whether the alert state is resolved based on the temperature information acquired in step Sa6. The host computer 16 determines that the state is the limit state when at least one of the following conditions (5) to (8) is satisfied.

(5) sum_crt> sum_crt_th
(6) amptmp_out> amptmp_out_th
(7) coiltmp_out> coiltmp_out_th
(8) chillertmp_out> chillertmp_out_th
However, sum_crt_th is the limit value of the feature value sum_crt, amptmp_out_th is the limit value of the temperature amptmp_out, coiltmp_out_th is the limit value of the temperature coiltmp_out, and chillertmp_out_th is the limit value of the temperature chillertmp_out.

  The host computer 16 determines that the alert state has been resolved when all of the following conditions (9) to (12) are satisfied.

(9) sum_crt_wng2> sum_crt
(10) amptmp_out_wng2> amptmp_out
(11) coiltmp_out_wng2> coiltmp_out
(12) chillertmp_out_wng2> chillertmp_out
However, sum_crt_wng2 is a warning cancellation value of the characteristic value sum_crt, amptmp_out_wng2 is a warning cancellation value of the temperature amptmp_out, coiltmp_out_wng2 is a warning cancellation value of the temperature coiltmp_out, and chillertmp_out_wng2 is a warning cancellation value of the temperature chillertmp_out.

  Note that the warning value, the limit value, and the warning release value related to the same temperature information have a relationship of limit value> warning value> warning release value. The limit value is set to a value that may increase so that the temperature of the gradient magnetic field coil unit 6 or the gradient magnetic field amplifier 7 interferes with imaging when the corresponding temperature information reaches that value. The alert value is set to a value obtained by subtracting an appropriate margin from the limit value. The alert release value is set to a value obtained by further subtracting an appropriate margin from the alert value. These limit values, warning values, and warning cancellation values may be appropriately set based on results of experiments and simulations, for example.

  If it is determined that the limit state has not been reached and the alert state has not been resolved, the host computer 16 proceeds from step Sa8 to step Sa9. In step Sa9, the host computer 16 waits for a predetermined waiting time T2. When waiting for the waiting time T2, the host computer 16 returns to step Sa6. Thus, in the alert state, the host computer 16 repeatedly acquires temperature information at the interval of the waiting time T2, and confirms whether or not the limit state has been reached and whether or not the alert state has been resolved. In addition, since it is desirable to be able to quickly determine that when the limit state is reached, it is desirable that the waiting time T2 is shorter than the waiting time T1.

  If it is determined that the alert state has been resolved, the host computer 16 proceeds from step Sa8 to step Sa3 and waits for a waiting time T1. At this time, the host computer 16 displays the state of the item exceeding the warning value or the remaining time of the waiting time T1 on the display 13 in real time. When waiting for the waiting time T1, the host computer 16 returns to step Sa1.

  On the other hand, when determining that the limit state has been reached, the host computer 16 proceeds from step Sa7 to step Sa10. In step Sa10, the host computer 16 instructs the sequencer 10 to stop shooting for a certain period. Along with this, the host computer 16 controls the display unit 13 so as to display a warning to the effect that photographing has been suspended due to the limit state. Then, when the photographing pause is finished and the photographing is resumed, the host computer 16 returns to Step Sa1. Note that this shooting pause may also be performed in accordance with the change of the shooting operation as in the case of extension of TR. Further, the change of the shooting operation for stopping the shooting can be a change of the application pattern of the MPG (motion probing gradient) pulse in the DWI sequence. In this way, shooting can be paused more quickly than when waiting for an average or slice change to arrive.

  The host computer 16 ends the above processing in response to the completion of shooting.

  As described above, according to the MRI apparatus 100, temperature information that is an index of the temperature of the gradient magnetic field coil unit 6 and the gradient magnetic field amplifier 7 is acquired during imaging, and the gradient magnetic field coil unit 6 and the gradient magnetic field coil 6 are obtained based on this temperature information. In response to the detection of the occurrence of a warning situation that may increase the temperature of the magnetic field amplifier 7 so as to affect the imaging, the temperature of the gradient coil unit 6 and the gradient field amplifier 7 is increased by extending TR. Therefore, the gradient magnetic field coil unit 6 and the gradient magnetic field amplifier 7 can be prevented from falling into a limit situation where the temperature of the gradient magnetic field coil unit 6 and the gradient magnetic field amplifier 7 has risen to such an extent that they affect the photographing. It is possible to perform efficient shooting using the limit.

  Further, according to the present embodiment, when the occurrence of a limit situation is detected in spite of the extension of TR, the imaging is suspended for a certain period in accordance with this, and the gradient coil unit 6 and the gradient magnetic field coil 6 Since the shooting is resumed after the temperature of the magnetic field amplifier 7 is lowered, the inappropriate shooting in the limit situation is not continued, and the shooting performed before falling into the limit situation is not wasted. It is possible to perform very efficient shooting.

  Note that the quality of the image obtained by extending the TR or stopping the shooting by extending the TR or stopping the shooting by changing the shooting operation such as the change of the average in the averaging scan or the change of the slice to be shot. Can be minimized.

  Further, according to the present embodiment, when the TR is extended or the shooting is stopped, the display unit 13 displays a warning to that effect so that the user can recognize that such control is being performed. Can be made.

  This embodiment can be variously modified as follows.

  The occurrence of a limit state may be detected by integrating and evaluating a plurality of conditions. For example, sum_crt, amptmp_out, coiltmp_out, and chillertmp_out are evaluated numerically with normal level = 0 and warning level = 1, and if the sum of these evaluation values is 2, it is detected that a limit state has occurred. Also good.

  Information serving as an index of hardware temperature may be only a part of the above-described four pieces of information, or may include other information such as the temperature of the liner tube. Alternatively, other information such as the temperature of the liner tube may be used without using the four pieces of information described above.

  The hardware subject to temperature monitoring may be either one of the gradient magnetic field coil unit 6 and the gradient magnetic field amplifier 7 or may include other hardware such as the shim coil 3. Alternatively, instead of targeting the gradient magnetic field coil unit 6 and the gradient magnetic field amplifier 7, another hardware such as the shim coil 3 may be the target of temperature monitoring. Furthermore, the temperature monitoring target hardware may be the RF coil unit 8. When separate RF coils are used for transmission and reception, these RF coils can also be hardware to be monitored.

  Various controls that reduce the addition of hardware that is the object of temperature monitoring can be arbitrarily applied as shooting control in the alert state. For example, a reduction in the number of averages in the averaging scan and a reduction in the number of imaging slices.

  When the imaging condition is changed in the alert state or the limit state, the host computer 16 may generate information indicating that as supplementary information of data obtained by imaging. Note that this incidental information may be information that only indicates that the shooting conditions have been changed. However, it is preferable that the imaging conditions after the change are understood. The incidental information may be generated for each image, each series, or each study. By generating such incidental information, it becomes possible for the user to recognize that the shooting condition has been changed during the shooting of the image, or the changed shooting condition when the image is observed. In addition, when the incidental information is generated for each series or each study, a warning display based on the incidental information may be always performed during the display of each image of the series or study. However, if the warning display based on the supplementary information is performed only prior to the display of the first image of the series or study, the warning display is always displayed during the display of each image, which may cause annoyance to the user. Can be avoided.

  The chilled water device 17 can be realized as a separate body without being mounted on the MRI apparatus 100. In this case, the chilled water device 17 may be used for purposes other than cooling the MRI device 100. In this way, if the chilled water device 17 is also used for other purposes, the cooling capability of the gradient magnetic field coil unit 6 and the gradient magnetic field amplifier 7 may be lowered, so that the application of the present application is more useful.

  Note that the present invention is not limited to the above-described embodiment as it is, and can be embodied by modifying the constituent elements without departing from the scope of the invention in the implementation stage. In addition, various inventions can be formed by appropriately combining a plurality of components disclosed in the embodiment. For example, some components may be deleted from all the components shown in the embodiment. Furthermore, constituent elements over different embodiments may be appropriately combined.

1 is a diagram showing a schematic configuration of a magnetic resonance imaging apparatus (MRI apparatus) 100 according to an embodiment of the present invention. The flowchart which shows the process of the host computer 16 in connection with the temperature management of the gradient magnetic field generation part when imaging | photography is performed.

Explanation of symbols

  DESCRIPTION OF SYMBOLS 100 ... Magnetic resonance imaging apparatus (MRI apparatus), 1 ... Magnet, 2 ... Static magnetic field power supply, 3 ... Shim coil, 4 ... Shim coil power supply, 5 ... Top plate, 6x, 6y, 6z ... Coil, 6 ... Gradient magnetic field coil unit, DESCRIPTION OF SYMBOLS 7 ... Gradient magnetic field amplifier, 8 ... Coil unit, 9R ... Receiver, 9T ... Transmitter, 10 ... Sequencer, 11 ... Arithmetic unit, 12 ... Memory unit, 13 ... Display, 14 ... Input device, 15 ... Sound generator , 16: Host computer, 17: Chilled water device, 18, 19, 20 ... Temperature sensor, 21 ... Current monitor.

Claims (12)

In a magnetic resonance imaging apparatus that performs imaging by magnetic resonance imaging using hardware whose temperature may increase with imaging operation,
Acquisition means for acquiring information serving as an index of the hardware temperature during execution of the photographing;
A warning situation detection means for detecting occurrence of a warning situation that may rise to such an extent that the temperature of the hardware affects the shooting, based on the acquired information;
A magnetic resonance imaging apparatus comprising: control means for controlling the imaging so as to suppress an increase in temperature of the hardware in response to detection of occurrence of the warning situation.   The hardware includes a gradient magnetic field coil that generates a gradient magnetic field by receiving a current supply, a gradient magnetic field amplifier that supplies the current to the gradient magnetic field coil, a high frequency coil that generates a high frequency magnetic field by receiving a current supply, and magnetic resonance The magnetic resonance imaging apparatus according to claim 1, wherein the magnetic resonance imaging apparatus is at least one of a high-frequency coil that receives a signal and generates a current.   The magnetic resonance imaging apparatus according to claim 2, wherein the acquisition unit acquires a current value supplied to the gradient coil by the gradient magnetic field amplifier as the information. The hardware is cooled by a cooling medium cooled by a cooling device,
The acquisition means acquires at least one of a temperature of the cooling medium cooled by the cooling device and a temperature of the cooling medium after being used for cooling the hardware as the information. The magnetic resonance imaging apparatus according to claim 1. The acquisition means acquires, as the information, a numerical value serving as an index of the hardware temperature,
The magnetic resonance imaging apparatus according to claim 1, wherein the warning status detection unit detects the occurrence of the warning status when a numerical value acquired as the information exceeds a threshold value.   The magnetic resonance imaging apparatus according to claim 1, wherein the control unit extends a repetition time in the imaging sequence in order to suppress a temperature rise of the hardware.   2. The magnetic resonance imaging according to claim 1, wherein the control unit controls the magnetic resonance imaging so as to suppress an increase in temperature of the hardware at a change of average in an average scan or a change of a slice to be imaged. Imaging device. Limit situation detection means for detecting the occurrence of a limit situation that has increased so that the temperature of the hardware affects the shooting, based on the acquired information;
The magnetic resonance imaging apparatus according to claim 1, further comprising means for temporarily stopping the imaging in response to detection of occurrence of the limit situation. The acquisition means acquires, as the information, a numerical value serving as an index of the hardware temperature,
The magnetic resonance imaging apparatus according to claim 8, wherein the limit situation detection unit detects the occurrence of the warning situation when a numerical value acquired as the information exceeds a threshold value.   The magnetic resonance imaging apparatus according to claim 1, further comprising notification means for notifying a user that the imaging has been controlled so as to suppress an increase in temperature of the hardware by the control means.   The apparatus further comprises means for generating incidental information representing the control for the data acquired by the photographing controlled so as to suppress a temperature rise of the hardware by the control means. 2. The magnetic resonance imaging apparatus according to 1. In a magnetic resonance imaging apparatus that performs imaging by a magnetic resonance imaging method using a gradient magnetic field coil that generates a gradient magnetic field upon receiving power and a gradient magnetic field amplifier that supplies the power to the gradient magnetic field coil,
A cooling device for cooling a cooling medium for cooling the gradient magnetic field coil and the gradient magnetic field amplifier;
The temperature of the cooling medium cooled by the cooling device, the temperature of the cooling medium after being used for cooling the gradient magnetic field coil, and the cooling medium after being used for cooling the gradient magnetic field amplifier Acquisition means for acquiring at least one of the temperature of the current or the current value supplied to the gradient coil by the gradient magnetic field amplifier;
Means for detecting the occurrence of a warning situation in response to any one of the values acquired by the acquisition means exceeding a first threshold defined in association with each value;
Means for controlling the imaging so as to suppress a temperature rise of the gradient coil and the gradient amplifier in response to detection of occurrence of the warning situation;
The occurrence of a limit situation is detected in response to any one of the values acquired by the acquisition means exceeding a second threshold value that is set larger than the first threshold value in association with each value. Means,
A magnetic resonance imaging apparatus comprising: means for temporarily stopping the imaging in response to detection of occurrence of the limit situation.

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