JPH0856918A - Magnetic resonance imaging system - Google Patents
Magnetic resonance imaging systemInfo
- Publication number
- JPH0856918A JPH0856918A JP6196635A JP19663594A JPH0856918A JP H0856918 A JPH0856918 A JP H0856918A JP 6196635 A JP6196635 A JP 6196635A JP 19663594 A JP19663594 A JP 19663594A JP H0856918 A JPH0856918 A JP H0856918A
- Authority
- JP
- Japan
- Prior art keywords
- magnetic field
- gradient magnetic
- photographing
- gradually
- subject
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
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- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
Description
【０００１】[0001]
【産業上の利用分野】本発明は磁気共鳴イメージング装
置、特に被検体である被検者の緊張感を緩和することに
向けられた磁気共鳴イメ−ジング装置に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a magnetic resonance imaging apparatus, and more particularly to a magnetic resonance imaging apparatus aimed at alleviating a feeling of tension of a subject who is a subject.
【０００２】[0002]
【従来の技術】磁気共鳴イメ−ジング装置においては、
被検体に高周波磁場及び傾斜磁場が撮影期間中繰り返し
印加され、それによって生じる核磁気共鳴信号にもとづ
いて被検体の像が生成される。一方、傾斜磁場が繰り返
し印加されることに起因していわゆる打撃音が発生す
る。このため、その減少策が種々試みられているが、十
分な解決策は得られていないのが現状である。2. Description of the Related Art In a magnetic resonance imaging apparatus,
A high frequency magnetic field and a gradient magnetic field are repeatedly applied to the subject during the imaging period, and an image of the subject is generated based on the nuclear magnetic resonance signal generated thereby. On the other hand, so-called hitting sound is generated due to the repeated application of the gradient magnetic field. For this reason, various reduction measures have been tried, but the current situation is that a sufficient solution has not been obtained.
【０００３】[0003]
【発明が解決しようとする課題】この打撃音に関し、本
発明者は、被検体である被検者、特に初めて検査を受け
る被検者は撮影の初めと終わりに特に緊張感を覚えるこ
とに気づき、更にその原因は撮影が開始されると急に打
撃音が生じ、更に撮影が終わると急にその打撃音が止ま
ることにあることがわかった。With regard to this striking sound, the present inventor has noticed that the subject who is the subject, especially the subject who undergoes the examination for the first time, feels particularly nervous at the beginning and end of the photographing. Furthermore, it was found that the cause was that a striking sound suddenly occurred when the shooting was started, and suddenly stopped when the shooting was finished.
【０００４】したがって、本発明の目的は撮影の開始時
及び終了時における被検者の緊張感を和らげるのに適し
た磁気共鳴イメ−ジング装置を提供することにある。SUMMARY OF THE INVENTION Therefore, an object of the present invention is to provide a magnetic resonance imaging apparatus suitable for alleviating the tension of a subject at the start and end of photographing.
【０００５】[0005]
【課題を解決するための手段】本発明の目的は、静磁場
中に置かれた被検体に撮影期間を通じて高周波磁場及び
傾斜磁場を繰り返し印加し、それによって前記被検体か
ら生じる核磁気共鳴信号にもとづいて前記被検体の画像
を得る磁気共鳴イメ−ジング装置であって、前記撮影期
間の前では徐々に増大し、前記撮影期間の後では徐々に
減少する音を発生させるようにしたことを特徴とする磁
気共鳴イメ−ジング装置によって達成される。An object of the present invention is to repeatedly apply a high-frequency magnetic field and a gradient magnetic field to a subject placed in a static magnetic field throughout an imaging period, thereby generating a nuclear magnetic resonance signal from the subject. A magnetic resonance imaging apparatus for obtaining an image of the subject on the basis of the apparatus, wherein a sound that gradually increases before the imaging period and gradually decreases after the imaging period is generated. And a magnetic resonance imaging device.
【０００６】[0006]
【作用】本発明によれば、撮影期間の前では徐々に増大
し、撮影期間の後では徐々に減少する音が発生される。
したがって撮影の前と後では急激な音の変化がなくなる
ため、被検体である被検者の緊張感が和らげられる。According to the present invention, a sound is generated which gradually increases before the photographing period and gradually decreases after the photographing period.
Therefore, since there is no sudden change in sound before and after the imaging, the feeling of tension of the examinee who is the subject is relieved.
【０００７】[0007]
【実施例】図２に磁気共鳴イメ−ジング装置の全体構成
を示す。均一な静磁場を発生する磁石101中に、被検体1
02を置き、被検体中の1Ｈに対して、核磁気共鳴を生じ
させるに必要な高周波を送受信システム106において発
生させ、該高周波を送信コイル104より被検体102に対し
て照射する。一定時間照射後、被検体中の1Ｈが発生す
る核磁気共鳴信号を受信コイル105によって検出し、検
出された共鳴信号は送受信システム106によって可聴周
波数に変換され、更にA/D変換器107によってディジタル
信号となる。この信号は計算機109によって必要な処理
をなされ、得られた画像を表示装置110に表示する。ま
た、イメージングに必要な位置情報を信号に付加するた
めの傾斜磁場は、予め決められた必要な条件を満足する
ように計算機109によって制御された傾斜磁場電源108と
該電源に接続された傾斜磁場コイル103によって印加さ
れる。また、前記送受信システム106も同様に計算機に
よって制御される。FIG. 2 shows the overall structure of a magnetic resonance imaging apparatus. The subject 1 is placed in a magnet 101 that generates a uniform static magnetic field.
At 02, a high frequency required to generate nuclear magnetic resonance is generated in the transmission / reception system 106 for 1 H in the subject, and the high frequency is applied to the subject 102 from the transmission coil 104. After irradiation for a certain period of time, the nuclear magnetic resonance signal generated by 1 H in the subject is detected by the receiving coil 105, the detected resonance signal is converted into an audible frequency by the transmission / reception system 106, and further by the A / D converter 107. It becomes a digital signal. This signal is subjected to necessary processing by the computer 109, and the obtained image is displayed on the display device 110. Further, the gradient magnetic field for adding position information necessary for imaging to a signal is a gradient magnetic field power supply 108 controlled by a computer 109 so as to satisfy a predetermined necessary condition and a gradient magnetic field connected to the power supply. Applied by coil 103. The transmission / reception system 106 is also controlled by a computer.
【０００８】図３に撮影のための基本的なパルスシーケ
ンスを示す。静磁場中に置かれた被検体の磁化は静磁場
の方向を向いている。そこに90°パルス201を照射する
と、被検体の磁化は静磁場と直角方向に向き、静磁場強
度に比例した周波数をもった核磁気共鳴信号が発生す
る。この信号は横緩和の影響に加えて、静磁場の不均一
性により急速に減衰するが、ＴＥ／２時間後に180°パ
ルス202を照射すると、更にＴＥ／２時間後に再び強い
信号208が発生する。この信号をサンプリングする。90
°パルス照射から信号発生までの時間をエコー時間（Ｔ
Ｅ）といい、ＴＥを変えることにより画像に反映される
横緩和の影響が変わる。FIG. 3 shows a basic pulse sequence for photographing. The magnetization of the subject placed in the static magnetic field is oriented in the direction of the static magnetic field. When 90 ° pulse 201 is irradiated there, the magnetization of the subject is oriented in the direction perpendicular to the static magnetic field, and a nuclear magnetic resonance signal having a frequency proportional to the static magnetic field intensity is generated. This signal is rapidly attenuated by the inhomogeneity of the static magnetic field in addition to the effect of lateral relaxation, but when a 180 ° pulse 202 is irradiated after TE / 2 hours, a strong signal 208 is again generated after TE / 2 hours. . This signal is sampled. 90
° Echo time (T
This is called E), and the influence of lateral relaxation reflected on the image changes by changing TE.
【０００９】上記計測を一定時間ＴＲごとに繰り返す。
この信号に位置情報を与えるため互いに直交した３つの
傾斜磁場を使用する。傾斜磁場印加量を少しずつ変化さ
せて計測を繰り返す。The above measurement is repeated every fixed time TR.
Three gradient fields orthogonal to each other are used to provide position information to this signal. The amount of applied gradient magnetic field is gradually changed and the measurement is repeated.
【００１０】まず、平面を切り出すために90°、180°
パルス201、202の印加時に計測ごに同じ出力値のスライ
ス用傾斜磁場203、204を印加する。すると、90°、180
°パルスの周波数に応じた磁場強度の磁化のみが励起さ
れる。これをスライシングという。First, in order to cut out a plane, 90 ° and 180 °
When the pulses 201 and 202 are applied, the slice gradient magnetic fields 203 and 204 having the same output value are applied to each measurement. Then, 90 °, 180
° Only the magnetization of the magnetic field strength corresponding to the pulse frequency is excited. This is called slicing.
【００１１】その平面内の磁化について周波数エンコー
ド用傾斜磁場206、207、位相エンコード用傾斜磁場205
を印加し、平面内の位置情報を与える。周波数エンコー
ドは信号サンプリングの際に計測ごとに同じ出力値の傾
斜磁場を印加して、ＮＭＲ信号の周波数と信号の発生位
置を対応させる手法である。また、位相エンコードと
は、信号サンプリングの前に計測ごとに変化する傾斜磁
場を与えて、計測ごとの位相の変化と位置を対応させる
手法である。Regarding magnetization in the plane, gradient magnetic fields 206 and 207 for frequency encoding and gradient magnetic field 205 for phase encoding
Is applied to give position information in the plane. Frequency encoding is a method of applying a gradient magnetic field having the same output value for each measurement at the time of signal sampling so that the frequency of the NMR signal and the generation position of the signal correspond. In addition, the phase encoding is a method in which a gradient magnetic field that changes for each measurement is applied before the signal sampling so that the phase change and the position for each measurement correspond to each other.
【００１２】このように、位相エンコード用傾斜磁場は
計測ごとに変化するが、スライス用傾斜磁場、周波数エ
ンコード用傾斜磁場は計測ごとに同じ様に印加されるの
で、撮影の開始から終了まで、ほぼ同じ打撃音が続く。As described above, the gradient magnetic field for phase encoding changes with each measurement, but the gradient magnetic field for slicing and the frequency gradient magnetic field for frequency encoding are applied in the same manner for each measurement, so that from the start to the end of imaging, the gradient magnetic field is almost the same. The same batting sound continues.
【００１３】なお、スライシングの方向をＺ軸方向、位
相エンコ−ド方向をＹ軸方向とすれば、周波数エンコ−
ド方向はＸ軸方向となる。図２において、ＧZはスライ
シング用傾斜磁場、ＧYは位相エンコ−ド用傾斜磁場、
ＧXは周波数エンコ−ド用傾斜磁場を表している。If the slicing direction is the Z-axis direction and the phase encoding direction is the Y-axis direction, the frequency encoding is performed.
The direction is the X-axis direction. In FIG. 2, G Z is a gradient magnetic field for slicing, G Y is a gradient magnetic field for phase encoding,
G X represents a gradient magnetic field for frequency encoding.
【００１４】図１は撮影の前後において徐々に増大及び
減少する音（打撃音）を発生させるためのパルスシ−ケ
ンスの一例を示す。（Ａ）は、撮影の開始直前の数秒の
間、傾斜磁場強度が傾斜磁場出力値なしから図３の第１
計測で使用される傾斜磁場出力値へ除々に変化するよ
う、撮影には寄与しない傾斜磁場印加を行うことを示
す。この場合の傾斜磁場の立上り時間は一定であって、
かつ図３における撮影時と同じ立上り時間とする。傾斜
磁場印加の時間間隔は図３における撮影の時間間隔と同
じであることが望ましい。（Ｂ）は図３における撮影シ
−ケンスと同じシ−ケンスを示す。（Ｃ）は、撮影の終
了直後の数秒の間、傾斜磁場強度が図３の最終計測で使
用される傾斜磁場出力値から傾斜磁場出力値なしへ除々
に変化するよう、撮影には寄与しない傾斜磁場印加を行
うことを示す。この場合も傾斜磁場の立上り時間は一定
であって、かつ図３における撮影時と同じ立上り時間と
する。傾斜磁場印加の時間間隔は図３における撮影の時
間間隔と同じであることが望ましい。FIG. 1 shows an example of a pulse sequence for producing sounds (striking sounds) that gradually increase and decrease before and after photographing. (A) shows that the gradient magnetic field strength has no gradient magnetic field output value for a few seconds immediately before the start of imaging, and the first magnetic field in FIG.
It is shown that a gradient magnetic field that does not contribute to imaging is applied so that the gradient magnetic field output value used for measurement gradually changes. The rise time of the gradient magnetic field in this case is constant,
Moreover, the rise time is the same as that at the time of shooting in FIG. The time interval for applying the gradient magnetic field is preferably the same as the time interval for imaging in FIG. (B) shows the same sequence as the photographing sequence in FIG. (C) shows a gradient that does not contribute to imaging so that the gradient magnetic field strength gradually changes from the gradient magnetic field output value used in the final measurement of FIG. 3 to no gradient magnetic field output value for a few seconds immediately after the end of imaging. It shows that a magnetic field is applied. Also in this case, the rise time of the gradient magnetic field is constant, and the rise time is the same as that at the time of imaging in FIG. The time interval for applying the gradient magnetic field is preferably the same as the time interval for imaging in FIG.
【００１５】図１（Ａ）のシ−ケンスによれば、徐々に
高くなる打撃音が発生し、そしてその打撃音は遂には撮
影時に繰り返し印加される傾斜磁場に起因して発生する
打撃音と実質的に同レベルに達する。また、図１（Ｂ）
のシ−ケンスによれば、撮影時に繰り返し印加される傾
斜磁場に起因して発生する打撃音と実質的に同レベルか
ら徐々に減少する打撃音が発生される。したがって、被
検体である被検者の緊張感は和らげられるようになる。According to the sequence shown in FIG. 1 (A), a striking sound that gradually rises is generated, and the striking sound finally becomes a striking sound caused by the gradient magnetic field repeatedly applied during photographing. Reach virtually the same level. In addition, FIG. 1 (B)
According to the above sequence, a striking sound that gradually decreases from a level substantially the same as the striking sound generated due to the gradient magnetic field repeatedly applied at the time of photographing is generated. Therefore, the sense of tension of the subject, which is the subject, can be relieved.
【００１６】図４は撮影の前後において徐々に増大及び
減少する音（打撃音）を発生させるためのパルスシ−ケ
ンスのもう一つの例を示す。（Ａ）は、撮影の開始直前
の数秒の間、図３の第１計測で使用される傾斜磁場出力
値で、立上り時間が長い状態から図３の計測において使
用される短い状態へと除々に変化するよう、撮影には寄
与しない傾斜磁場印加を行うことを示す。傾斜磁場印加
の時間間隔は従来技術の撮影の時間間隔と同じであるこ
とが望ましい。（Ｂ）は図３における撮影シ−ケンスと
同じシ−ケンスを示す。（Ｃ）は、撮影の終了直後の数
秒の間、図３の最終計測で使用する傾斜磁場出力値で、
立上り時間が図３の計測において使用される短い状態か
ら長い状態へと除々に変化するよう、撮影には寄与しな
い傾斜磁場印加を行うことを示す。傾斜磁場印加の時間
間隔は図３における撮影の時間間隔と同じであることが
望ましい。この実施例によっても、撮影の前後において
撮影期間の前では徐々に増大しながらその撮影期間中に
繰り返し印加される傾斜磁場に起因して生じる打撃音と
実質的に同レベルに達する打撃音が発生され、撮影期間
の後ではその撮影期間中に繰り返し印加される傾斜磁場
に起因して生じる打撃音と実質的に同レベルから徐々に
減少する打撃音が発生される。FIG. 4 shows another example of the pulse sequence for generating a sound (striking sound) that gradually increases and decreases before and after photographing. (A) is the gradient magnetic field output value used in the first measurement of FIG. 3 for a few seconds immediately before the start of imaging, and gradually increases from a state in which the rise time is long to a short state in which the measurement in FIG. 3 is used. It is shown that a gradient magnetic field application that does not contribute to imaging is performed so as to change. It is desirable that the time interval of applying the gradient magnetic field is the same as the time interval of the conventional imaging. (B) shows the same sequence as the photographing sequence in FIG. (C) is the gradient magnetic field output value used in the final measurement in FIG. 3 for a few seconds immediately after the end of imaging,
It is shown that the gradient magnetic field application that does not contribute to imaging is performed so that the rise time gradually changes from the short state used in the measurement of FIG. 3 to the long state. The time interval for applying the gradient magnetic field is preferably the same as the time interval for imaging in FIG. Also in this embodiment, a striking sound is generated before and after the photographing, which gradually increases before the photographing period and reaches substantially the same level as the striking sound generated due to the gradient magnetic field repeatedly applied during the photographing period. After the shooting period, a striking sound is generated which is gradually reduced from substantially the same level as the striking sound generated due to the gradient magnetic field repeatedly applied during the shooting period.
【００１７】撮影の前後における打撃音の漸増及び漸減
は、図１ではその撮影の前後に繰り返し印加される傾斜
磁場の強度を、図４ではその撮影の前後に繰り返し印加
される傾斜磁場の立上り時間をそれぞれ変えることによ
って実現されているが、その撮影の前後に繰り返し印加
される傾斜磁場パルスシ−ケンスの繰り返し時間、した
がってその傾斜磁場の印加時間間隔を変えることによっ
ても、撮影の前後において撮影期間の前では徐々に増大
しながらその撮影期間中に繰り返し印加される傾斜磁場
に起因して生じる打撃音と実質的に同レベルに達する打
撃音を発生させ、撮影期間の後ではその撮影期間中に繰
り返し印加される傾斜磁場に起因して生じる打撃音と実
質的に同レベルから徐々に減少する打撃音を発生させる
ことができる。Gradually increasing and gradually decreasing the striking sound before and after the photographing means the strength of the gradient magnetic field repeatedly applied before and after the photographing in FIG. 1, and the rise time of the gradient magnetic field repeatedly applied before and after the photographing in FIG. It is realized by changing each of the above, but also by changing the repetition time of the gradient magnetic field pulse sequence repeatedly applied before and after the imaging, and thus by changing the time interval for applying the gradient magnetic field, The striking sound that reaches the same level as the striking sound caused by the gradient magnetic field repeatedly applied during the shooting period is gradually generated before, and after the shooting period, it is repeated during the shooting period. It is possible to generate an impact sound that gradually decreases from substantially the same level as the impact sound generated due to the applied gradient magnetic field.
【００１８】[0018]
【発明の効果】本発明によれば、撮影の開始時及び終了
時における被検者の緊張感を和らげるのに適した磁気共
鳴イメ−ジング装置が提供される。According to the present invention, there is provided a magnetic resonance imaging apparatus suitable for alleviating the tension of a subject at the start and end of photographing.
【図１】図２の装置と共に用いられる、撮影の前後にお
いて徐々に増大及び減少する打撃音を発生させるための
パルスシ−ケンスの一例を示す図である。1 is a diagram showing an example of a pulse sequence used to generate a striking sound that gradually increases and decreases before and after photographing, which is used with the apparatus of FIG. 2;
【図２】本発明にもとづく一実施例を示す磁気共鳴イメ
−ジング装置の全体構成の概念図である。FIG. 2 is a conceptual diagram of the overall configuration of a magnetic resonance imaging apparatus showing an embodiment based on the present invention.
【図３】図２の装置と共に用いられる撮影用パルスシ−
ケンスの一例を示す図である。FIG. 3 is an imaging pulse train used with the apparatus of FIG.
It is a figure which shows an example of a can.
【図４】図２の装置と共に用いられる、撮影の前後にお
いて徐々に増大及び減少する打撃音を発生させるための
パルスシ−ケンスのもう一つの例を示す図である。FIG. 4 is a diagram showing another example of the pulse sequence used to generate the striking sound that gradually increases and decreases before and after the photographing, which is used with the apparatus of FIG. 2;
101…磁石、102…被検体、103…傾斜磁場コイル、104…
送信コイル、105…受信コイル 106…送受信システム、1
07…A/D変換器、108…傾斜磁場電源、109…計算機、110
…表示装置101 ... Magnet, 102 ... Subject, 103 ... Gradient magnetic field coil, 104 ...
Transmitting coil, 105 ... Receiving coil 106 ... Transmitting / receiving system, 1
07 ... A / D converter, 108 ... Gradient magnetic field power supply, 109 ... Calculator, 110
... Display device
Claims (1)
じて高周波磁場及び傾斜磁場を繰り返し印加し、それに
よって前記被検体から生じる核磁気共鳴信号にもとづい
て前記被検体の画像を得る磁気共鳴イメ−ジング装置で
あって、前記撮影期間の前では徐々に増大し、前記撮影
期間の後では徐々に減少する音を発生させるようにした
ことを特徴とする磁気共鳴イメ−ジング装置。1. A magnetic field which obtains an image of the subject based on a nuclear magnetic resonance signal generated from the subject by repeatedly applying a high frequency magnetic field and a gradient magnetic field to the subject placed in a static magnetic field throughout an imaging period. A resonance imaging device, wherein a magnetic resonance imaging device is configured to generate a sound that gradually increases before the imaging period and gradually decreases after the imaging period.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP6196635A JPH0856918A (en) | 1994-08-22 | 1994-08-22 | Magnetic resonance imaging system |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP6196635A JPH0856918A (en) | 1994-08-22 | 1994-08-22 | Magnetic resonance imaging system |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPH0856918A true JPH0856918A (en) | 1996-03-05 |
Family
ID=16361050
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP6196635A Pending JPH0856918A (en) | 1994-08-22 | 1994-08-22 | Magnetic resonance imaging system |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH0856918A (en) |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| KR20010046445A (en) * | 1999-11-12 | 2001-06-15 | 윤종용 | Reducing method of impact of a patient by gradient-coil noise in magnetic resonance imaging system |
| JP2009291484A (en) * | 2008-06-06 | 2009-12-17 | Hitachi Medical Corp | Magnetic resonance imaging apparatus |
| WO2016162957A1 (en) * | 2015-04-07 | 2016-10-13 | 株式会社日立製作所 | Magnetic resonance imaging apparatus |
-
1994
- 1994-08-22 JP JP6196635A patent/JPH0856918A/en active Pending
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| KR20010046445A (en) * | 1999-11-12 | 2001-06-15 | 윤종용 | Reducing method of impact of a patient by gradient-coil noise in magnetic resonance imaging system |
| JP2009291484A (en) * | 2008-06-06 | 2009-12-17 | Hitachi Medical Corp | Magnetic resonance imaging apparatus |
| WO2016162957A1 (en) * | 2015-04-07 | 2016-10-13 | 株式会社日立製作所 | Magnetic resonance imaging apparatus |
| US10436862B2 (en) | 2015-04-07 | 2019-10-08 | Hitachi, Ltd. | Magnetic resonance imaging apparatus |
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