JPH02257938A - Mri device - Google Patents
Mri deviceInfo
- Publication number
- JPH02257938A JPH02257938A JP1078280A JP7828089A JPH02257938A JP H02257938 A JPH02257938 A JP H02257938A JP 1078280 A JP1078280 A JP 1078280A JP 7828089 A JP7828089 A JP 7828089A JP H02257938 A JPH02257938 A JP H02257938A
- Authority
- JP
- Japan
- Prior art keywords
- receiving coil
- type
- coil
- receiving
- cpu
- 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.)
- Pending
Links
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 abstract description 2
- 229910052802 copper Inorganic materials 0.000 abstract description 2
- 239000010949 copper Substances 0.000 abstract description 2
- 238000005259 measurement Methods 0.000 description 13
- 239000003990 capacitor Substances 0.000 description 6
- 238000012545 processing Methods 0.000 description 5
- 238000005481 NMR spectroscopy Methods 0.000 description 4
- 230000003068 static effect Effects 0.000 description 3
- 230000005540 biological transmission Effects 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 229940079593 drug Drugs 0.000 description 2
- 239000003814 drug Substances 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 238000006243 chemical reaction Methods 0.000 description 1
- 238000012937 correction Methods 0.000 description 1
- 238000013480 data collection Methods 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 230000005284 excitation Effects 0.000 description 1
- 230000008676 import Effects 0.000 description 1
- 238000000691 measurement method Methods 0.000 description 1
- 230000009466 transformation Effects 0.000 description 1
- 238000004804 winding Methods 0.000 description 1
Abstract
Description
【発明の詳細な説明】
〔産業上の利用分野〕
本発明は、ＭＲＩ装置、特に高周波受信コイルの種別の
自動取込みをはかるＭＲＩ装置に関する。DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to an MRI apparatus, and particularly to an MRI apparatus that automatically acquires the type of high-frequency receiving coil.
ＭＲＩ装置では、被検体からのエコー信号を受信するた
めに高周波受信コイルを使用する。高周波受信コイルは
、被検体の測定部位毎にその性能や形状が異なる。測定
部位には、頭頚部２体幹部。An MRI apparatus uses a high-frequency receiving coil to receive echo signals from a subject. The performance and shape of the high-frequency receiving coil differ depending on the measurement site of the subject. The measurement sites include the head and neck, and two trunks.
関節部等があり、且つ各部位毎に複数の種別のコイルが
ある。形状にも、円筒形、楕円形、フレキシブル形、サ
ーフエース形等がある。There are joints, etc., and there are multiple types of coils for each part. Shapes include cylindrical, oval, flexible, surf ace, etc.
ＭＲＩ装置は、計算機を有するが、この計算機では、高
周波受信コイルの種類に応じて測定パラメータを選択す
る。例えば、スピンエコー法では、９０’パルス−１８
０＠パルスの順に選択励起パルスを発生する。その振幅
は、９ｏ°を「１」とすると１８０”では「２」となる
。この９０’パルスと１８０°パルスとの比はいかなる
種類の受信コイルでも同じであるが、ゲインは異なる。The MRI apparatus has a computer, and this computer selects measurement parameters depending on the type of high-frequency receiving coil. For example, in the spin echo method, 90' pulse -18
Selective excitation pulses are generated in the order of 0@pulse. If the amplitude is ``1'' at 9o°, it is ``2'' at 180''. The ratio of the 90' pulse to the 180° pulse is the same for any type of receiver coil, but the gain is different.
例えば、９０”パルスの振幅が５であれば、１８０゜パ
ルスの振幅が１０であり、９０″′パルスの振幅が１．
０であれば、１８０″′パルスの振幅が２０となる。即
ち、１対２の比率は同じであるがゲインが異なる。For example, if a 90'' pulse has an amplitude of 5, a 180° pulse has an amplitude of 10, and a 90'' pulse has an amplitude of 1.
If it is 0, the amplitude of the 180'' pulse is 20. That is, the 1:2 ratio is the same but the gain is different.
かかるゲインはスピンエコー法では測定パラメータとな
る。他の測定法では異なった測定パラメータがありうる
。Such a gain becomes a measurement parameter in the spin echo method. Other measurement methods may have different measurement parameters.
計算機は、測定毎にその受信コイルの種別を取込む。受
信コイルの種別と測定パラメータとは対応しており、計
算機は、取込んだ受信コイルの種別から対応する８１ｇ
定パラメータを選択する。そして、この選択した測定パ
ラメータを利用してＭＲＩ計測を行わせる。The computer takes in the type of receiving coil for each measurement. The receiving coil type and measurement parameters correspond, and the computer calculates the corresponding 81g from the received receiving coil type.
Select the fixed parameters. Then, MRI measurement is performed using the selected measurement parameters.
さて、受信コイルの種別の計算機への入力は、操作者が
自分でキーボード等から行う。Now, the operator inputs the receiving coil type into the computer by himself using a keyboard or the like.
尚、ＭＲＩ装置については、ｒＮＭＲ医学（基礎と臨床
）」（核磁気共鳴医学研究会編、丸善株式会社、昭和６
２年発行）に詳しい。Regarding MRI equipment, please refer to "rNMR Medicine (Basic and Clinical)" (edited by Nuclear Magnetic Resonance Medicine Study Group, Maruzen Co., Ltd., 1932).
2 years old).
操作者による受信コイル種別の入力は、誤入力がさけら
れない。誤入力であると、測定パラメータも誤って選択
されることとなり、誤った測定をしてしまう、また１画
像が歪んだものとなり、誤判断を招く。When inputting the receiving coil type by the operator, erroneous input is inevitable. If the input is incorrect, the measurement parameters will also be selected incorrectly, leading to incorrect measurements and one image being distorted, leading to erroneous judgments.
本発明の目的は、受信コイルの種別を正しく入力可能と
するＭＲＩ装置を提供するものである。An object of the present invention is to provide an MRI apparatus that allows the type of receiving coil to be input correctly.
【ａ題を解決するための手段〕
本発明は、受信コイルに種別指定手段を一体化して設け
た。[Means for solving problem a] In the present invention, a type designating means is integrated with the receiving coil.
本発明によれば、受信コイルと一体化した種別指定手段
により、受信コイル種別を指定する。この指定した種別
はＭＲＩ装置に取込まれ、測定パラメータの選択に利用
され、測定に供する。According to the present invention, the receiving coil type is specified by the type specifying means integrated with the receiving coil. This specified type is taken into the MRI apparatus, used for selecting measurement parameters, and used for measurement.
第２図は本発明に係るＭＲＩ装置の全体構成を示すブロ
ック図である。このＭＲＩ装置は、核磁気共鳴（ＮＭＲ
）現象を利用して被検体の断層画像を得るもので、静磁
場発生磁石１ｏと、中央処理装置（ＣＰＵ）１１とシー
ケンサ１２と、送信系１３と、磁場勾配発生系１４と、
受信系１５と信号処理系１６とから成る。上記静磁場発
生磁石１０は、被検体１の周りにその体軸方向（水平方
向）または体軸と直交する方向（垂直方向）に強く均一
な静磁場を発生させるもので、上記被検体１の周りのあ
る広がりをもった空間に永久磁石方式または常電導方式
あるいは超電導方式の磁場発生手段が配置されている。FIG. 2 is a block diagram showing the overall configuration of the MRI apparatus according to the present invention. This MRI device uses nuclear magnetic resonance (NMR).
) phenomenon to obtain a tomographic image of a subject, which includes a static magnetic field generating magnet 1o, a central processing unit (CPU) 11, a sequencer 12, a transmitting system 13, a magnetic field gradient generating system 14,
It consists of a receiving system 15 and a signal processing system 16. The static magnetic field generating magnet 10 generates a strong and uniform static magnetic field around the subject 1 in the body axis direction (horizontal direction) or in a direction perpendicular to the body axis (vertical direction). Permanent magnet type, normal conduction type, or superconducting type magnetic field generating means is arranged in a surrounding space with a certain extent.
上記シーケンサ１２は、ＣＰＵ１１の制御で動作し、被
検体１の断層画像のデータ収集に必要な種々の命令を送
信系１３及び磁場勾配発生系１４並びに受信系１５に送
るものである。上記送信系１３は、高周波発振器１７と
変調器１８と高周波増幅器１９７！□送信側の高周波コ
イル２０ａとから成り、上記高周波発振器１７から出力
された高周波パルスをシーケンサ１２の命令に従って変
調器１８で振幅変調し、この振幅変調された高周波パル
スを高周波増幅器１９で増幅した後に被検体１に近接し
て配置された高周波コイル２０ａに供給することにより
電磁波が上記被検体１に照射されるようになっている。The sequencer 12 operates under the control of the CPU 11 and sends various commands necessary for data collection of tomographic images of the subject 1 to the transmission system 13, magnetic field gradient generation system 14, and reception system 15. The transmission system 13 includes a high frequency oscillator 17, a modulator 18, and a high frequency amplifier 197! □It consists of a high-frequency coil 20a on the transmitting side, the high-frequency pulse outputted from the high-frequency oscillator 17 is amplitude-modulated by a modulator 18 according to the commands of the sequencer 12, and after this amplitude-modulated high-frequency pulse is amplified by a high-frequency amplifier 19. The subject 1 is irradiated with electromagnetic waves by supplying the electromagnetic waves to a high-frequency coil 20a placed close to the subject 1.
上記磁場勾配発生系１４は、Ｘ、Ｙ、Ｚの三軸方向に巻
かれた傾斜磁場コイル２１と、それぞれのコイルを駆動
する傾斜磁場電源２２とから成り、上記シーケンサ１２
からの命令に従ってそれぞれのコイルの傾斜磁場電源２
２を駆動することにより、Ｘ、Ｙ、Ｚの三軸方向に傾斜
磁場Ｇｘ 、 Ｇｖ。The magnetic field gradient generation system 14 is composed of gradient magnetic field coils 21 wound in the three axial directions of X, Y, and Z, and a gradient magnetic field power supply 22 that drives each coil.
Gradient magnetic field power source 2 of each coil according to instructions from
2, gradient magnetic fields Gx, Gv are generated in the three axes of X, Y, and Z.
Ｇｚを被検体１に印加するようになっている。この傾斜
磁場の加え方により、被検体１に対するスライス面を設
定することができる。上記受信系１５は、受信側のソレ
ノイド形の高周波コイル２０ｂと増幅器２３とから成り
、上記送信側の高周波コイル２０ａから照射された電磁
波による被検体１の応答の電磁波（ＮＭＲ信号）は被検
体１に近接して配置された高周波コイル（受信コイルｙ
２０ｂで検出され、増幅器２３及び直交位相検波器２４
を介してＡ／Ｄ変換器２５に入力してデジタル量に変換
され、さらにシーケンサ１２からの命令によるタイミン
グで直交位相検波器２４によりサンプリングされた二基
列の収集データとされ。Gz is applied to the subject 1. Depending on how this gradient magnetic field is applied, a slice plane for the subject 1 can be set. The receiving system 15 is composed of a solenoid-type high-frequency coil 20b on the receiving side and an amplifier 23, and the electromagnetic waves (NMR signals) of the response of the subject 1 to the electromagnetic waves irradiated from the high-frequency coil 20a on the transmitting side are transmitted to the subject 1. A high-frequency coil (receiving coil y
20b, an amplifier 23 and a quadrature phase detector 24
The data is input to the A/D converter 25 via the A/D converter 25, where it is converted into a digital quantity, and further sampled by the quadrature phase detector 24 at the timing according to the command from the sequencer 12, resulting in two bases of collected data.
その信号が信号処理系１６に送られるようになっている
。また、高周波コイル２０ｂは、コイル制御器２６．シ
ーケンサ１２．ＣＰＵＩＩにより自動同調及びコイル２
０ｂの種別の識別が行えるようになっている。信号処理
系１６は、ＣＰＵＩＩと、磁気ディスク２７等の記憶装
置と、ＣＲＴ等のデイスプレィ２８とから成り、ＣＰＵ
Ｉ １で制御、フーリエ変換、補正係数計算、像再構成
等の処理を行い、任意断面の画像をデイスプレィ２８に
表示するようになっている。The signal is sent to a signal processing system 16. Further, the high frequency coil 20b is controlled by a coil controller 26. Sequencer 12. Automatic tuning and coil 2 by CPUII
The type of 0b can be identified. The signal processing system 16 consists of a CPU II, a storage device such as a magnetic disk 27, and a display 28 such as a CRT.
I1 performs processing such as control, Fourier transformation, correction coefficient calculation, and image reconstruction, and displays an image of an arbitrary cross section on the display 28.
第１図は、本発明の実施例図である。受信コイル２０ｂ
は、コイル本体部５０と共振コンデンサ５１、マツチン
グ用コンデンサ５２．バリコン５３、パリキャップ５４
．可変抵抗器５５より成る。バリコン５３は、コンデン
サ共振容量の粗調整用に使用し、微調整はパリキャップ
５４で行う。FIG. 1 is a diagram showing an embodiment of the present invention. Receiving coil 20b
The coil body 50, the resonance capacitor 51, and the matching capacitor 52. Varicon 53, Paris cap 54
．． It consists of a variable resistor 55. The variable capacitor 53 is used for coarse adjustment of the capacitor resonance capacitance, and the fine adjustment is performed using the variable cap 54.
コイル制御器２６は、同調制御回路３１を持つ。The coil controller 26 has a tuning control circuit 31.
同調制御回路３１は、大きさを種々変更できる直流電圧
を発生する。この直流電圧によってパリキャップ５４の
コンデンサ容量を変化させ、エコー受信信号の共振点を
見つけ出す。共振点が見つかれば、同調が得られたこと
になり、この時の信号をアンプ２３を介してＣＰＵ（計
算機）１１へ取込む。この同調制御回路３１の直流電圧
の変更指令はＣＰＵＩＩが行う、且つ同調点の発見もＣ
ＰＵ１１が行う。The tuning control circuit 31 generates a DC voltage whose magnitude can be varied. The capacitor capacity of the Paris cap 54 is changed by this DC voltage, and the resonance point of the echo reception signal is found. If a resonance point is found, it means that tuning has been achieved, and the signal at this time is taken into the CPU (computer) 11 via the amplifier 23. The CPU II issues a command to change the DC voltage of the tuning control circuit 31, and also discovers the tuning point.
Performed by PU11.
さて、可変抵抗器５５は、同調制御回路３１の出力端と
アースとの間に接続する。１個の受信コイル２０ｂに１
個の可変抵抗器５５を一体化して組込んでおく、そこで
１組込んだ後に可変抵抗器５５をその受信コイルの種別
を示す抵抗値に設定する。−度設定したならば、変更し
ない。一方、同調制御回路３１は、同調操作の前に種別
読取り用の直流電圧Ｄｏを発生する。このＤｏ発生はＣ
ＰＵＩ １が指示する。可変抵抗器５５は、Ｄ。Now, the variable resistor 55 is connected between the output terminal of the tuning control circuit 31 and ground. 1 for each receiving coil 20b
The variable resistors 55 are integrated and installed, and after one is installed, the variable resistor 55 is set to a resistance value that indicates the type of the receiving coil. - Once set, do not change it. On the other hand, the tuning control circuit 31 generates a DC voltage Do for type reading before the tuning operation. This Do occurrence is C
PUI 1 indicates. The variable resistor 55 is D.
を受けて、設定値対応の分圧出力を発生する。これをＡ
Ｄ変換器３２がＡＤ変換し、ＣＰＵＩＩに受信コイル２
０ｂの種別コードとして取込ませる。In response to this, it generates a partial pressure output corresponding to the set value. This is A
The D converter 32 performs AD conversion and sends the receiving coil 2 to the CPU II.
Import it as a type code of 0b.
他の受信コイル２０ｂ’内でも、受信コイル２０ｂと同
じような構成となっており、受信コイル２０ｂ’の種別
を示す抵抗値が同様に設定されている。従って、受信コ
イル２０ｂに代って、受信コイル２０ｂ’ を取付けた
場合であっても、受信コイル２０ｂ’の種別を示す種別
コードがＣＰＵＩＩに取込めることになる。The other receiving coils 20b' have the same configuration as the receiving coil 20b, and the resistance values indicating the type of the receiving coils 20b' are set similarly. Therefore, even if the receiving coil 20b' is attached instead of the receiving coil 20b, the type code indicating the type of the receiving coil 20b' can be imported into the CPU II.
その他の受信コイルでも同様に可変抵抗器が存在し１種
別を示す抵抗値が設定されている。Similarly, variable resistors exist in other receiving coils, and resistance values indicating one type are set.
さて、受信コイル２０ｂが円筒形状の場合の外観図を第
３図に示す、コイル本体部６１は、銅板を巻回してコイ
ルを構成している。この外表面にチューニングボード６
０を取付けた。チューニングボード６ｏは第１図のコン
デンサ５１，５２゜５３．５４．及び可変抵抗器３０を
内部に取込んだ筐体である。かくして、コイル本体部６
１とチューニングボード６０とは一体化されたことにな
る。 尚、第３図で、受信コイル２０ｂと他回路とのコ
ネクタは、チューニングボード６０に取付けるとよい。FIG. 3 shows an external view of the receiving coil 20b having a cylindrical shape. The coil body 61 is formed by winding a copper plate. Tuning board 6 on this outer surface
I installed 0. The tuning board 6o has capacitors 51, 52, 53, 54. and a casing incorporating a variable resistor 30 therein. Thus, the coil main body 6
1 and the tuning board 60 are now integrated. Incidentally, in FIG. 3, the connector between the receiving coil 20b and other circuits is preferably attached to the tuning board 60.
更に、可変抵抗器の代りに直接にＷ１圧を設定させても
よく、また、同調制御回路の出力直流電圧を利用せずに
他の電圧を利用してもよい。バーコードによる指定でも
よい。Furthermore, the W1 voltage may be set directly instead of using the variable resistor, or another voltage may be used instead of the output DC voltage of the tuning control circuit. It may also be specified by barcode.
本発明によれば、受信コイル毎にその種別を固定して指
定できるため、ＭＲＩ装置は、受信コイルの種別を受信
コイル取付は後自動的に読取ることができる。該入力の
恐れを大幅に少なくできた。According to the present invention, since the type can be fixed and specified for each receiving coil, the MRI apparatus can automatically read the type of the receiving coil after the receiving coil is attached. The fear of such input can be greatly reduced.
第１図は本発明の受信コイルの実施例図、第２図は本発
明のＭＲＩ装置の実施例図、第３図は本発明の受信コイ
ルの外観側図である。
２０ｂ、２０ｂ’・・・受信コイル、５５・・・可変抵
抗器、３１・・・同調制御回路。FIG. 1 is an embodiment of the receiving coil of the present invention, FIG. 2 is an embodiment of the MRI apparatus of the present invention, and FIG. 3 is an external side view of the receiving coil of the present invention. 20b, 20b'... Receiving coil, 55... Variable resistor, 31... Tuning control circuit.
Claims (1)
イルで受信してＭＲＩ画像を得るＭＲＩ装置において、 受信コイル種別対応に該種別を指示する指示手段を設け
、該指示手段を受信コイルに一体化した構成とするＭＲ
Ｉ装置。[Claims] 1. In an MRI apparatus that obtains an MRI image by receiving an echo signal obtained by applying a magnetic field with a high-frequency receiving coil, an instruction means for indicating the type corresponding to the type of the receiving coil is provided, MR in which the means is integrated into the receiving coil
I device.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1078280A JPH02257938A (en) | 1989-03-31 | 1989-03-31 | Mri device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1078280A JPH02257938A (en) | 1989-03-31 | 1989-03-31 | Mri device |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPH02257938A true JPH02257938A (en) | 1990-10-18 |
Family
ID=13657552
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP1078280A Pending JPH02257938A (en) | 1989-03-31 | 1989-03-31 | Mri device |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH02257938A (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2001245868A (en) * | 1999-12-22 | 2001-09-11 | General Electric Co <Ge> | Method and device for controlling peripheral equipment of medical imaging system |
Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS6273146A (en) * | 1985-09-27 | 1987-04-03 | Toshiba Corp | Magnetic resonance imaging apparatus |
| JPS62227341A (en) * | 1986-03-31 | 1987-10-06 | 株式会社東芝 | Magnetic resonance imaging apparatus |
-
1989
- 1989-03-31 JP JP1078280A patent/JPH02257938A/en active Pending
Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS6273146A (en) * | 1985-09-27 | 1987-04-03 | Toshiba Corp | Magnetic resonance imaging apparatus |
| JPS62227341A (en) * | 1986-03-31 | 1987-10-06 | 株式会社東芝 | Magnetic resonance imaging apparatus |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2001245868A (en) * | 1999-12-22 | 2001-09-11 | General Electric Co <Ge> | Method and device for controlling peripheral equipment of medical imaging system |
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