JPH08322815A - Mri equipment - Google Patents
Mri equipmentInfo
- Publication number
- JPH08322815A JPH08322815A JP7134168A JP13416895A JPH08322815A JP H08322815 A JPH08322815 A JP H08322815A JP 7134168 A JP7134168 A JP 7134168A JP 13416895 A JP13416895 A JP 13416895A JP H08322815 A JPH08322815 A JP H08322815A
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- cooling
- temperature
- magnetic field
- cooling device
- air
- Prior art date
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- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
Description
【０００１】[0001]
【産業上の利用分野】本発明は、医療診断用のＭＲＩ装
置に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an MRI apparatus for medical diagnosis.
【０００２】[0002]
【従来の技術】一般にＭＲＩ装置（磁気共鳴イメージン
グ装置）は図４に示すように診察用ベッド４４上の天板
４２に載せた被検者４５をガントリ４１の中央部に形成
されたガントリ穴４３に送り込み、磁気共鳴を利用して
人体内の断層像を写し出し診断する装置である。2. Description of the Related Art Generally, as shown in FIG. 4, an MRI apparatus (magnetic resonance imaging apparatus) has a gantry hole 43 formed in a central portion of a gantry 41 with a subject 45 placed on a top plate 42 on an examination bed 44. It is a device that sends a tomographic image to the inside of the human body and makes a diagnosis by using magnetic resonance.
【０００３】このガントリ４１の中には、ガントリ穴４
３に挿入された被検者の体軸方向に均一な磁場を発生さ
せるために、超電導マグネット等で構成される円筒状の
静磁場用マグネットと、被検者内の３次元位置情報を得
るために傾斜磁場を発生させる傾斜コイルが設けられて
おり、送受信アンテナからの高周波パルスによって体内
の各スピンの励起を行い、このアンテナで体内からの電
磁波を受信するようにしている。In this gantry 41, there are gantry holes 4
In order to generate a uniform magnetic field in the body axis direction of the subject inserted in 3, the cylindrical static magnetic field magnet composed of a superconducting magnet or the like and to obtain three-dimensional position information in the subject A gradient coil for generating a gradient magnetic field is provided in the device, and each spin in the body is excited by a high frequency pulse from a transmitting / receiving antenna, and this antenna receives an electromagnetic wave from the body.
【０００４】傾斜コイルは鞍形状をしており、その磁場
の大きさを直線的に変化させるために傾斜磁場電源から
電流を与えるようにしている。The gradient coil has a saddle shape, and an electric current is applied from a gradient magnetic field power source to linearly change the magnitude of the magnetic field.
【０００５】この傾斜コイルには大電流が流されるので
発熱量も多く、これを冷却するために例えば図５のよう
に冷媒（空気等）を用いて冷却を行っている。Since a large current is passed through the gradient coil, a large amount of heat is generated. To cool the gradient coil, cooling is performed using a refrigerant (air or the like) as shown in FIG. 5, for example.
【０００６】図５は図４のＡ−Ａ断面を上から見た図で
あり、５１は静磁場を発生させる円筒状の静磁場マグネ
ット、５２は傾斜磁場を発生させる傾斜コイル、５３は
ガントリカバー、５４は円筒状の巻き枠である傾斜コイ
ルボビン、５５は通気ダクトであり、傾斜コイル５２は
傾斜コイルボビン５４に巻回されて支持されている。装
置の外部から通気ダクト５５へ冷却用の空気が送り込ま
れ、図の矢印に沿って空気が移動する。冷却空気は傾斜
コイル５２を冷却した後、装置外部へ排気される。FIG. 5 is a view of the AA cross section of FIG. 4 seen from above, 51 is a cylindrical static magnetic field magnet for generating a static magnetic field, 52 is a gradient coil for generating a gradient magnetic field, and 53 is a gantry cover. , 54 is a gradient coil bobbin which is a cylindrical winding frame, 55 is a ventilation duct, and the gradient coil 52 is wound around and supported by the gradient coil bobbin 54. Air for cooling is sent from the outside of the device to the ventilation duct 55, and the air moves along the arrow in the figure. After cooling the gradient coil 52, the cooling air is exhausted to the outside of the device.
【０００７】ところで、傾斜コイルだけに限らず、静磁
場用マグネット、送受信アンテナに与える高周波パルス
を発生させる高周波回路やこの回路のための高周波電
源、傾斜磁場用電源、操作コンソール等についても熱が
生じるので、これらすべての発熱源を一つの冷却装置で
冷却したり、個々の発熱源についてそれぞれ適当な冷却
手段を設けて冷却を行っている。By the way, heat is generated not only in the gradient coil but also in the static magnetic field magnet, the high frequency circuit for generating high frequency pulses to be applied to the transmitting and receiving antennas, the high frequency power supply for this circuit, the gradient magnetic field power supply, the operation console and the like. Therefore, all of these heat sources are cooled by one cooling device, or an appropriate cooling means is provided for each heat source for cooling.
【０００８】[0008]
【発明が解決しようとする課題】しかし、発熱源のすべ
てを一つの冷却装置で冷却する場合には、一つの冷却装
置では、その冷却能力に限界があるので、完全に冷却す
ることができないばかりか、特定の発熱源に対しては冷
却効果がなかなか上がらず、一方、他の発熱源に対して
は冷却効果が上がりすぎて温度が下がり過ぎてしまうと
いうことがあり、冷却効率にも問題があった。However, when all of the heat sources are cooled by a single cooling device, the cooling capacity of the single cooling device is limited, so that it cannot be completely cooled. On the other hand, the cooling effect does not easily increase for a specific heat source, while the cooling effect for other heat sources may increase too much and the temperature may drop too much, causing a problem in cooling efficiency. there were.
【０００９】また、個々の発熱源について適当な冷却手
段を設けている場合には、冷却が継続して行われるの
で、各冷却手段の発熱源に対する冷却能力を高くした場
合には、各冷却手段の総消費電力が非常に大きくなって
いた。Further, when an appropriate cooling means is provided for each heat source, cooling is continuously performed. Therefore, when the cooling capacity of each cooling means for the heat source is increased, each cooling means is used. The total power consumption was very high.
【００１０】本発明は、上記課題を解決するために創案
されたもので、冷却効率を高め、冷却時の必要以上の消
費電力を抑えることができるようにしたＭＲＩ装置を提
供するものである。The present invention was devised to solve the above problems, and provides an MRI apparatus capable of improving cooling efficiency and suppressing unnecessary power consumption during cooling.
【００１１】[0011]
【課題を解決するための手段】上記目的を達成するため
に、本発明のＭＲＩ装置は、静磁場マグネットと、この
内側に配置された傾斜コイルと、これら全体を覆う磁気
シールドと、磁気シールド外に配置された制御機器部と
コンソール部と冷却能力、冷却方式の異なる複数の冷却
装置と、これら冷却装置の制御部を備えるとともに、装
置内の各発熱源に別個に温度測定部を設け、前記各温度
測定部からの測定信号に基づいて冷却装置の制御部が前
記複数の冷却装置を組み合わせて使用することを特徴と
している。In order to achieve the above object, the MRI apparatus of the present invention comprises a static magnetic field magnet, a gradient coil arranged inside the static magnetic field magnet, a magnetic shield covering the whole of them, and a magnetic shield outside. In addition to having a control device section and a console section, cooling capacity, and a plurality of cooling devices having different cooling methods, and a control section for these cooling devices, each heat source inside the apparatus is provided with a temperature measuring section, It is characterized in that the control unit of the cooling device uses the plurality of cooling devices in combination based on the measurement signal from each temperature measurement unit.
【００１２】[0012]
【作用】装置が作動すると、装置内の各発熱源に設けら
れた温度測定部からの温度測定信号が冷却装置の制御部
に伝達される。この信号に基づいて冷却装置の制御部は
冷却能力、冷却方式の異なる複数の冷却装置の最適な組
み合わせを判断してオン・オフ等を行うので、冷却効率
や消費電力の効率は非常に良くなる。When the device operates, the temperature measurement signal from the temperature measuring part provided in each heat source in the device is transmitted to the control part of the cooling device. Based on this signal, the control unit of the cooling device determines the optimum combination of the cooling devices having different cooling capacities and cooling methods and performs on / off operation, so that the cooling efficiency and the power consumption efficiency are very good. .
【００１３】[0013]
【実施例】本発明の一実施例を、以下、図面に基づいて
説明する。DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS An embodiment of the present invention will be described below with reference to the drawings.
【００１４】図１は本発明によるＭＲＩ装置の構成の全
体図を示している。FIG. 1 shows an overall configuration of the MRI apparatus according to the present invention.
【００１５】１は円筒形状を有し、被検者の体軸方向に
均一な静磁場を発生させるための静磁場マグネット、２
は励起されたスピンの３次元位置情報を得るために傾斜
磁場を発生させる傾斜磁場コイル、３は被検者を静磁場
マグネット１に送り込むベッド、４は磁気を遮断する磁
気シールド、５は送風機等の冷却機構と冷却方式を選択
する制御部６と冷却装置Ａ〜Ｃを備えた冷却システム、
７は励起波形を発生させる高周波回路および高周波電
源、傾斜磁場電源等からなる制御機器部、７は表示装置
や入力装置を備えた操作コンソール部である。Reference numeral 1 denotes a static magnetic field magnet having a cylindrical shape for generating a uniform static magnetic field in the body axis direction of the subject.
Is a gradient coil for generating a gradient magnetic field to obtain three-dimensional position information of the excited spins, 3 is a bed for feeding the subject to the static magnetic field magnet 1, 4 is a magnetic shield for blocking the magnetism, 5 is a blower, etc. A cooling system including a control unit 6 for selecting a cooling mechanism and a cooling method of the above and cooling devices A to C,
Reference numeral 7 is a control device section including a high-frequency circuit for generating an excitation waveform, a high-frequency power source, a gradient magnetic field power source, and the like, and 7 is an operation console section provided with a display device and an input device.
【００１６】ベッド３には温度検出部Ａが、傾斜磁場コ
イル２には温度検出部Ｂが、静磁場マグネット１には温
度検出部Ｃが、制御機器部７には温度検出部Ｄが、操作
コンソール部８には温度検出部Ｅが設けられている。The bed 3 has a temperature detecting section A, the gradient magnetic field coil 2 has a temperature detecting section B, the static magnetic field magnet 1 has a temperature detecting section C, and the control device section 7 has a temperature detecting section D. The console section 8 is provided with a temperature detecting section E.
【００１７】これらの各温度検出部Ａ〜Ｅは温度センサ
等から構成されるもので、温度センサ等が設置された場
所の温度を冷却装置制御部６へ送信するようになってい
る。また、冷却装置制御部６は温度検出部Ａ〜Ｅの温度
測定信号に基づいて、冷却装置Ａ〜Ｅを駆動するように
各冷却装置と接続されている。Each of these temperature detectors A to E is composed of a temperature sensor or the like, and transmits the temperature of the place where the temperature sensor or the like is installed to the cooling device controller 6. Further, the cooling device control unit 6 is connected to each cooling device so as to drive the cooling devices A to E based on the temperature measurement signals of the temperature detection units A to E.
【００１８】冷却装置Ａ〜Ｅは各々冷却能力や冷却方式
が異なり、例えば、静磁場マグネットが超電導コイルの
場合には、冷却装置Ｃは液体ヘリウム等の冷媒をダクト
Ｃを介して静磁場マグネット１に送り込むように構成さ
れ、冷却装置Ｂは冷却空気をダクトＢを介して傾斜磁場
コイル２に送るように、冷却装置Ａは冷却空気をダクト
Ａを介してベッド３上に載せられた被検者周辺の空間に
送るように構成されている。The cooling devices A to E have different cooling capacities and cooling systems. For example, when the static magnetic field magnet is a superconducting coil, the cooling device C uses a coolant such as liquid helium through the duct C to generate the static magnetic field magnet 1. The cooling device B sends the cooling air to the gradient magnetic field coil 2 via the duct B, and the cooling device A sends the cooling air to the bed 3 via the duct A. It is configured to send to the surrounding space.
【００１９】これら、冷却装置Ａ〜Ｃは駆動していると
きには、電磁ノイズを発生させるので、被検者からの検
出信号に影響を与えないために磁気シールド４の外部に
設置されている。Since the cooling devices A to C generate electromagnetic noise when they are driven, they are installed outside the magnetic shield 4 so as not to affect the detection signal from the subject.
【００２０】一方、制御機器部７や操作コンソール部８
は、電磁ノイズの影響をそれ程受けないので、冷却装置
Ｄ、Ｅはそれぞれ制御機器部７と操作コンソール部８の
内部に組み込まれて使用されるようになっており、例え
ば、直接熱源に風を吹き付ける送風ファン等が用いられ
る。On the other hand, the control device section 7 and the operation console section 8
Is not so affected by electromagnetic noise, the cooling devices D and E are used by being incorporated in the control device section 7 and the operation console section 8, respectively. A blower fan or the like for blowing is used.
【００２１】冷却装置制御部６は、ＣＰＵやメモリ等が
搭載されており、各温度検出部Ａ〜Ｅの電気信号を受け
取り、各部の温度によって、冷却装置をオン・オフでき
るようになっている。例えば、温度検出部Ａの温度を被
検者の最も快適な温度ｔ0 〜ｔ1 を維持しようとすれ
ば、冷却装置制御部６にあらかじめ閾値ｔ0 、ｔ1 を設
定しておき、温度検出部Ａからの信号がｔ1 を越えたと
きに冷却装置Ａをオンして冷却空気をダクトＡを介して
被検者空間へ送り込んで冷却し、温度検出部Ａからの信
号がｔ0 以下になったときに冷却装置Ａをオフして送風
を遮断する。The cooling device control unit 6 is equipped with a CPU, a memory, etc., receives electric signals from the temperature detecting units A to E, and can turn on / off the cooling device according to the temperature of each unit. . For example, in order to maintain the temperature of the temperature detection unit A at the most comfortable temperature t 0 to t 1 of the subject, the cooling device control unit 6 is set with the thresholds t 0 and t 1 in advance and the temperature detection is performed. When the signal from the section A exceeds t 1 , the cooling device A is turned on to send the cooling air to the space of the subject through the duct A to cool it, and the signal from the temperature detecting section A becomes less than t 0 . When this happens, turn off cooling device A to shut off the air flow.
【００２２】他の温度検出部Ｂ〜Ｅについても同様にし
てあらかじめ所定の温度範囲の閾値を冷却装置制御部６
に記憶させておけば、所定の温度範囲に制御できるの
で、冷却効率を高めることができ、冷却時の必要以上の
消費電力を抑えることができる。Similarly, for the other temperature detectors B to E, the cooling device controller 6 sets a threshold value in a predetermined temperature range in advance.
If stored in memory, the temperature can be controlled within a predetermined temperature range, so that the cooling efficiency can be increased and unnecessary power consumption during cooling can be suppressed.
【００２３】図２、図３はこの方式をさらにガントリ部
について適用したものを示す。2 and 3 show a further application of this method to the gantry section.
【００２４】静磁場マグネット１の内側には傾斜磁場コ
イルボビン９に巻き回された傾斜磁場コイル２が配置さ
れ、さらにこの内側に被検者１１に高周波パルスを与
え、被検者の励起スピンの情報を得るために鞍形状のＲ
Ｆコイル１０が配置され、被検者１１がこの中に送り込
まれる。A gradient magnetic field coil 2 wound around a gradient magnetic field coil bobbin 9 is arranged inside the static magnetic field magnet 1, and a high frequency pulse is given to the subject 11 inside the gradient magnetic field coil 2 to obtain information on excited spins of the subject. Saddle-shaped R to obtain
The F coil 10 is arranged and the subject 11 is fed into this.
【００２５】冷却空気等を吹き付ける送風路Ｆ〜Ｌを図
のように、静磁場マグネット１と傾斜磁場コイル２との
間、傾斜磁場コイルボビン９と傾斜磁場コイル２との間
隙、傾斜磁場コイルボビン９とＲＦコイル１０との間、
被検者１１の周囲にそれぞれ設け、図示はしていないが
この送風路Ｆ〜Ｌには各々温度検出部Ｆ〜Ｌが設けられ
ている。As shown in the drawing, the air ducts F to L for blowing cooling air are provided between the static magnetic field magnet 1 and the gradient magnetic field coil 2, the gap between the gradient magnetic field coil bobbin 9 and the gradient magnetic field coil 2, and the gradient magnetic field coil bobbin 9. Between the RF coil 10,
Although not shown, the air passages F to L are respectively provided around the subject 11 and temperature detectors F to L are provided respectively.
【００２６】そして、磁気シールド外に設けられた冷却
装置Ｆ〜Ｌからの冷風がダクト等を介して各送風路Ｆ〜
Ｌに流れ込むようになっている。Then, the cool air from the cooling devices F to L provided outside the magnetic shield is blown through the ducts or the like into the air ducts F to L.
It is designed to flow into L.
【００２７】磁気シールド外の冷却装置制御部６には各
冷却装置Ｆ〜Ｌを駆動させるための信号を出力させるた
めに、サーモスイッチが備えられており、この各サーモ
スイッチが働く温度として、それぞれＴ1 〜Ｔ7 までの
値が設定されている。The cooling device control section 6 outside the magnetic shield is provided with thermoswitches for outputting signals for driving the cooling devices F to L. Values from T1 to T7 are set.
【００２８】したがって、図３に示すように各送風路に
設置した温度検出部Ｆ〜Ｌからの各温度信号が冷却装置
制御部６に伝達されると各信号が対応する設定温度Ｔ1
〜Ｔ7 と比較され、例えば、温度検出部Ｇからの信号が
Ｔ2 を越えている場合には冷却装置制御部６からオン信
号が出力され、冷却装置Ｇが駆動し送風路Ｇへ冷風が送
られ、Ｔ2 以下になるとオフ信号が出力され送風が遮断
される。Therefore, as shown in FIG. 3, when the temperature signals from the temperature detectors F to L installed in the respective air ducts are transmitted to the cooling device controller 6, the respective signals correspond to the set temperature T1.
~ T7, for example, when the signal from the temperature detection unit G exceeds T2, an ON signal is output from the cooling device control unit 6, the cooling device G is driven, and cool air is sent to the air passage G. , T2 or less, an off signal is output and the ventilation is shut off.
【００２９】他の冷却装置についても同様な働きをす
る。The other cooling devices have similar functions.
【００３０】以上のように、各発熱部に対して段階的に
冷却を行うことができ、冷却効率が向上し、消費電力を
抑えることができる。As described above, each heat generating portion can be cooled stepwise, the cooling efficiency is improved, and the power consumption can be suppressed.
【００３１】また、送風に伴う騒音問題に対応するた
め、患者近くの送風路に対しては、撮像のためのスキャ
ン開始時に冷却装置へオン信号を送るような構造にして
おくことによって、スキャン中のみ送風し、通常は送風
音が聞こえないようにしても良い。Further, in order to deal with the noise problem associated with the air flow, the air flow path near the patient is structured so that an ON signal is sent to the cooling device at the start of the scan for imaging, so that the air flow during the scan can be reduced. Only the air may be blown, and the sound of the air blow may not normally be heard.
【００３２】さらに、磁気シールド内において、画像に
対するノイズの影響が強く温度センサを設置しにくい部
分は、スキャンパラメータ等により温度上昇を予測する
ことによって、冷却装置を制御するようにしても良い。Further, in the magnetic shield, the cooling device may be controlled by predicting the temperature rise by the scan parameter or the like in the portion where the influence of noise on the image is strong and the temperature sensor is difficult to install.
【００３３】[0033]
【発明の効果】以上説明したように、本発明のＭＲＩ装
置によれば、装置内の各発熱源に設けられた温度測定部
からの温度測定信号に基づいて冷却装置の制御部が冷却
能力、冷却方式の異なる複数の冷却装置の最適な組み合
わせを判断してオン・オフ等を行うので、冷却効率や消
費電力の効率は高めることができる。As described above, according to the MRI apparatus of the present invention, the control unit of the cooling device has the cooling capability based on the temperature measurement signal from the temperature measurement unit provided in each heat source in the device. Since the optimum combination of the plurality of cooling devices having different cooling systems is determined to perform the on / off operation, the cooling efficiency and the power consumption efficiency can be improved.
【００３４】また、被検者に対する騒音を軽減すること
ができる。Further, it is possible to reduce noise on the subject.
【図１】本発明の一実施例のＭＲＩ装置の構成を示す模
式図である。FIG. 1 is a schematic diagram showing a configuration of an MRI apparatus according to an embodiment of the present invention.
【図２】本発明のＭＲＩ装置のガントリ部の構成を示す
図である。FIG. 2 is a diagram showing a configuration of a gantry unit of the MRI apparatus of the present invention.
【図３】図２における冷却のフローチャートを示す。FIG. 3 shows a flowchart of cooling in FIG.
【図４】ＭＲＩ装置の概観を示す図である。FIG. 4 is a diagram showing an overview of an MRI apparatus.
【図５】従来のＭＲＩ装置の構成を示す図である。FIG. 5 is a diagram showing a configuration of a conventional MRI apparatus.
Claims (1)
れた傾斜コイルと、これら全体を覆う磁気シールドと、
磁気シールド外に配置された制御機器部とコンソール部
と冷却能力、冷却方式の異なる複数の冷却装置と、これ
ら冷却装置の制御部を備えた装置において、 装置内の各発熱源に別個に温度測定部を設け、前記各温
度測定部からの測定信号に基づいて冷却装置の制御部が
前記複数の冷却装置を組み合わせて使用することを特徴
とするＭＲＩ装置。1. A static magnetic field magnet, a gradient coil arranged inside the static magnetic field magnet, and a magnetic shield covering the whole of them.
In a device equipped with a control device, a console, and multiple cooling devices with different cooling capacities and cooling methods that are located outside the magnetic shield, and a device that has a control unit for these cooling devices, measure the temperature separately for each heat source inside the device. An MRI apparatus characterized in that a control unit of the cooling device uses a plurality of cooling devices in combination based on a measurement signal from each of the temperature measuring units.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP7134168A JPH08322815A (en) | 1995-05-31 | 1995-05-31 | Mri equipment |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP7134168A JPH08322815A (en) | 1995-05-31 | 1995-05-31 | Mri equipment |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPH08322815A true JPH08322815A (en) | 1996-12-10 |
Family
ID=15122045
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP7134168A Pending JPH08322815A (en) | 1995-05-31 | 1995-05-31 | Mri equipment |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH08322815A (en) |
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1995
- 1995-05-31 JP JP7134168A patent/JPH08322815A/en active Pending
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| JP2008012296A (en) * | 2006-06-30 | 2008-01-24 | General Electric Co <Ge> | Apparatus and method for providing forced airflow to surface of gradient coil |
| JP2008149144A (en) * | 2006-12-18 | 2008-07-03 | General Electric Co <Ge> | System, method, and apparatus for controlling temperature of mri magnet warm bore |
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| US9417301B2 (en) | 2010-08-25 | 2016-08-16 | Koninklijke Philips N.V. | RF shield for MRI comprising conductive coating as shielding material |
| JP2012108110A (en) * | 2010-11-15 | 2012-06-07 | Toshiba Corp | Medical imaging system |
| WO2012127450A1 (en) | 2011-03-24 | 2012-09-27 | Koninklijke Philips Electronics N.V. | Reduction of peak electrical power consumption in magnetic resonance imaging systems |
| CN103443642A (en) * | 2011-03-24 | 2013-12-11 | 皇家飞利浦有限公司 | Reduction of peak electrical power consumption in magnetic resonance imaging systems |
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