JPH0333325B2 - - Google Patents
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- Publication number
- JPH0333325B2 JPH0333325B2 JP57234244A JP23424482A JPH0333325B2 JP H0333325 B2 JPH0333325 B2 JP H0333325B2 JP 57234244 A JP57234244 A JP 57234244A JP 23424482 A JP23424482 A JP 23424482A JP H0333325 B2 JPH0333325 B2 JP H0333325B2
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- Prior art keywords
- magnetic field
- pulse
- nuclear magnetic
- gradient magnetic
- living body
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
- G01R33/48—NMR imaging systems
- G01R33/483—NMR imaging systems with selection of signals or spectra from particular regions of the volume, e.g. in vivo spectroscopy
- G01R33/4833—NMR imaging systems with selection of signals or spectra from particular regions of the volume, e.g. in vivo spectroscopy using spatially selective excitation of the volume of interest, e.g. selecting non-orthogonal or inclined slices
- G01R33/4835—NMR imaging systems with selection of signals or spectra from particular regions of the volume, e.g. in vivo spectroscopy using spatially selective excitation of the volume of interest, e.g. selecting non-orthogonal or inclined slices of multiple slices
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- Physics & Mathematics (AREA)
- Optics & Photonics (AREA)
- Spectroscopy & Molecular Physics (AREA)
- High Energy & Nuclear Physics (AREA)
- Condensed Matter Physics & Semiconductors (AREA)
- General Physics & Mathematics (AREA)
- Magnetic Resonance Imaging Apparatus (AREA)
Description
【発明の詳細な説明】
ａ 発明の技術分野
本発明は核磁気共鳴コンピユータ断層撮影（以
下「NMR−CT」という）方法に係り、特に被
検体の複数個所の断層像を短時間で得ることので
きる核磁気共鳴コンピユータ断層撮影装置（以下
「NMR−CT装置」という）に関する。[Detailed Description of the Invention] a Technical Field of the Invention The present invention relates to a nuclear magnetic resonance computer tomography (hereinafter referred to as "NMR-CT") method, and in particular to a method for obtaining tomographic images of multiple locations of a subject in a short time. The present invention relates to a nuclear magnetic resonance computer tomography apparatus (hereinafter referred to as "NMR-CT apparatus") that can be used.
ｂ 従来技術及びその欠点
最近、被検体として例えば生体の特定個所の断
層像を得るためにNMR−CT方法が用いられる。
而して、断層像は複数個の信号により構成され、
例えばIR法（インバージヨンリカバリ法）によ
り前記断層像を得る場合、まず一様な磁束密度の
磁場内に置かれた生体に180゜パルスを与えて核磁
気モーメントを反転させ、所定時間経過後に前記
個所に関連した90゜パルスと例えば三次元空間の
Ｚ軸方向の傾斜磁場とを共に生体に与えることに
より前記個所に核磁気共鳴を起こさせ、さらに生
体に例えば三次元空間のＸ軸方向及びＹ軸方向の
傾斜磁場を与えることにより核磁気共鳴部分から
断層像を得るための各信号を検出していた。b. Prior Art and Its Disadvantages Recently, the NMR-CT method has been used to obtain a tomographic image of a specific part of a living body as a subject.
Therefore, a tomographic image is composed of multiple signals,
For example, when obtaining the tomographic image using the IR method (inversion recovery method), first a 180° pulse is applied to a living body placed in a magnetic field with uniform magnetic flux density to reverse the nuclear magnetic moment, and after a predetermined period of time, the By applying both a 90° pulse related to the location and a gradient magnetic field in the Z-axis direction of three-dimensional space to the living body, nuclear magnetic resonance is caused at the location, and further Each signal used to obtain a tomographic image from the nuclear magnetic resonance region was detected by applying an axial gradient magnetic field.
而して、180゜パルスを与えられたことにより、
生体の磁気モーメントの方向が例えばＺ軸方向に
おいて反転し、この核磁気モーメントは縦緩和時
間に従い、約１秒後に元の方向へ回復する。そし
て、前記各信号を得るためには前記核磁気モーメ
ントが元の方向へ回復してから生体に180゜パルス
を与えなければならない。このため、前記各信号
は略１秒毎にしか得られないので、例えば256個
の前記信号から構成される断層像を得るためには
略256秒、即ち４〜５分程度の時間を必要とした。 Therefore, by applying a 180° pulse,
The direction of the magnetic moment of the living body is reversed, for example, in the Z-axis direction, and this nuclear magnetic moment recovers to its original direction after about 1 second according to the longitudinal relaxation time. In order to obtain each of the signals, a 180° pulse must be applied to the living body after the nuclear magnetic moment has returned to its original direction. For this reason, each of the signals can only be obtained approximately every second, so for example, to obtain a tomographic image composed of 256 signals, approximately 256 seconds, or approximately 4 to 5 minutes, is required. did.
また、従来のNMR−CT方法を用いたNMR−
CT装置では、180゜パルスと同時にＺ軸方向の傾
斜磁場を生体に与えていなかったので、断層像を
得る個所だけでなくその他の個所を含めた生体の
広い範囲にわたっていっせいに核磁気モーメント
を反転させていた。このため、これらの核磁気モ
ーメントが前記したように元の方向に回復するま
では、前述の特定個所以外からも引続いてすぐ信
号を検出することはできなかった。この結果、従
来のNMR−CT方法は、生体の複数個所につい
てそれぞれの断層像を得るために長時間を要する
という欠点があった。 In addition, NMR-CT using conventional NMR-CT method
In the CT device, a gradient magnetic field in the Z-axis direction was not applied to the living body at the same time as the 180° pulse, so the nuclear magnetic moment was reversed all at once over a wide range of the living body, including not only the area where the tomographic image was obtained but also other areas. was. Therefore, until these nuclear magnetic moments were restored to their original directions as described above, it was not possible to immediately detect signals from other than the above-mentioned specific locations. As a result, the conventional NMR-CT method has the disadvantage that it takes a long time to obtain tomographic images of multiple locations in a living body.
ｃ 発明の目的
本発明は、被検体の複数部分における核磁気モ
ーメントを個別且つ時系列的に反転させるように
したことにより、前記個所の断層像を短時間に得
ることのできるNMR−CT装置を提共するにあ
る。c. Purpose of the Invention The present invention provides an NMR-CT apparatus that can obtain tomographic images of multiple parts of a subject in a short time by reversing nuclear magnetic moments in multiple parts individually and in time series. It is to share.
ｄ 実施例の説明
第１図は、本発明に係るNMR−CT装置によ
り被検体の複数個所の断層像を得る様子を示す説
明図、第２図は同じくその動作波形図である。図
において１は被検体としての生体であって、生体
１の長手方向に三次元空間のＺ軸をとる場合、生
体１は、磁束がＺ軸方向を向き且つ磁束密度が一
様な靜磁場H0内におかれる。Ｄ１，Ｄ２，Ｄ３
…DMはXY面に平行な面を表わし、各面Ｄ１〜
DMはＺ軸方向にそれぞれ適宣寸法離れている。
d1，d2，d3…dMは、面Ｄ１，Ｄ２，Ｄ３…DMと
対応した生体１の断層像を得る部分である。d Description of Examples FIG. 1 is an explanatory diagram showing how tomographic images of a plurality of locations of a subject are obtained by the NMR-CT apparatus according to the present invention, and FIG. 2 is an operational waveform diagram thereof. In the figure, 1 is a living body as a subject, and when the Z-axis of a three-dimensional space is taken in the longitudinal direction of the living body 1, the living body 1 is placed in a quiet magnetic field H in which the magnetic flux is directed in the Z-axis direction and the magnetic flux density is uniform. It is placed within 0 . D1, D2, D3
...DM represents a plane parallel to the XY plane, and each plane D1~
The DMs are separated by an appropriate distance in the Z-axis direction.
d 1 , d 2 , d 3 , . . . d M are parts for obtaining tomographic images of the living body 1 corresponding to the planes D 1 , D 2 , D 3 , . . . DM.
而して、Ａ１，Ａ２，Ａ３…AMは、前記部分
d1〜dMの核磁気モーメントをを一周期TB内にお
いてそれぞれ反転させる180゜パルスであって、こ
れらの180゜パルスＡ１〜AMは所定時間TAを隔て
て時系的にＺ軸方向に沿って生体１に与える。周
期TBは生体１の縦緩和時間よりも長い時間に設
定される。そして、180゜パルスＡ１〜AMと同時
に傾斜磁場GZ1を生体１に与える。この傾斜磁場
GZ1は磁束の向きがＺ軸方向であって、且つ磁束
密度はＺ軸方向にリニアに変化している。 Therefore, A1, A2, A3...AM are the above parts
These 180° pulses A1 to AM reverse the nuclear magnetic moments of d 1 to d M within one period T B , and these 180° pulses A1 to AM are time-series in the Z-axis direction at intervals of a predetermined time T A. Give it to living body 1 along the following lines. The period T B is set to be longer than the longitudinal relaxation time of the living body 1. Then, a gradient magnetic field G Z1 is applied to the living body 1 at the same time as the 180° pulses A1 to AM. This gradient magnetic field
In G Z1 , the magnetic flux direction is in the Z-axis direction, and the magnetic flux density changes linearly in the Z-axis direction.
Ｂ１，Ｂ２，Ｂ３…BMは、前記部分d1〜dMに
一周期TB内においてそれぞれ核磁気共鳴を起こ
させる90゜パルスであって、これらの90゜パルスＢ
１〜BMは傾斜磁場GZ1及び180゜パルスＡ１〜AM
に同期させ、且つ所定の時間〓遅れて、Ｚ軸方向
に沿って生体１に与える。この時間〓は180゜パル
スＢ１〜BMとが重ならないように設定される。
そして、90゜パルスＡ１〜AMと90゜パルスＢ１〜
BMとが重ならないように設定される。そして、
90゜パルスＢ１〜BMと同時に傾斜磁場GZ2を生体
１に与える。この傾斜磁場GZ2は磁束の向きがＺ
軸方向であって且つ磁束密度はＺ軸方向にリニア
に変化している。 B1, B2, B3...BM are 90° pulses that cause nuclear magnetic resonance in each of the portions d 1 to d M within one period T B , and these 90° pulses B
1~BM is gradient magnetic field G Z1 and 180° pulse A1~AM
is applied to the living body 1 along the Z-axis direction, and after a predetermined time delay. This time period is set so that the 180° pulses B1 to BM do not overlap.
Then, 90° pulse A1~AM and 90° pulse B1~
It is set so that it does not overlap with BM. and,
A gradient magnetic field G Z2 is applied to the living body 1 at the same time as the 90° pulses B1 to BM. This gradient magnetic field G Z2 has a magnetic flux direction of Z
In the axial direction, the magnetic flux density changes linearly in the Z-axis direction.
ところで、上述の180゜パルスＡ１〜AM及び90゜
パルスＢ１〜BMの周波数帯域等は、次の条件を
満たす必要がある。即ち、180゜パルスＡ１〜AM
及び90゜パルスＢ１〜BMは傾斜磁場GZ1及びGZ2
の強さと各面Ｄ１〜DMの位置に応じて定められ
る周波数を中心とし、各面D1〜DMの厚みに対
応する周波数帯域内に定められる。そして、傾斜
磁場GZ1及びGZ2が実質的に同一である場合には、
180゜パルスＡ１〜AMの周波数帯域は90゜パルスの
それを含み且つこの帯域内で180゜パルスＡ１〜
AMの各周波数成分の強度は第３図イに実線で示
すように略均一であることを要する。180゜パルス
Ａ１〜AMの断続時間は、生体１の縦緩和時間に
比して短いものでよい。そして、180゜パルスＡ１
〜AMは周波数帯域が同図ロに示すように略
SINC波形状に分布した高周波を用いる。一方、
90゜パルスＢ１〜BMの継続時間は生体１の横緩
和時間より十分短いことが必要なため、例えば１
ｍsec程度に選ばれる。そして、90゜パルスＢ１〜
BMは例えば周波数帯域が同図イに破線で示すよ
うにガウス波形状に分布した高周波を用いる。 By the way, the frequency bands of the above-mentioned 180° pulses A1 to AM and 90° pulses B1 to BM need to satisfy the following conditions. That is, 180° pulse A1~AM
and 90° pulses B1 to BM are gradient magnetic fields G Z1 and G Z2
centering on a frequency determined according to the strength of and the position of each surface D1 to DM, and is determined within a frequency band corresponding to the thickness of each surface D1 to DM. And when the gradient magnetic fields G Z1 and G Z2 are substantially the same,
The frequency band of 180° pulse A1~AM includes that of 90° pulse, and within this band, 180° pulse A1~
The intensity of each frequency component of AM is required to be approximately uniform as shown by the solid line in FIG. 3A. The intermittent time of the 180° pulses A1 to AM may be shorter than the longitudinal relaxation time of the living body 1. Then, 180° pulse A1
~AM is an abbreviation for the frequency band as shown in the figure (b).
Uses high frequencies distributed in the shape of a SINC wave. on the other hand,
The duration of 90° pulses B1 to BM needs to be sufficiently shorter than the transverse relaxation time of living body 1, so for example 1
It is selected to be about msec. And 90° pulse B1~
BM uses, for example, a high frequency wave whose frequency band is distributed in the shape of a Gaussian wave, as shown by the broken line in Figure A.
而して、90゜パルスＢ１〜BM及び傾斜磁場GZ2
を生体１に与えた直後、傾斜磁場GX及びGYを生
体１に与える。この傾斜磁場GX及びGYは磁束の
向きがＺ軸方向であって、且つその磁束密度はＸ
軸及びＹ軸方向にそれぞれリニアに変化してい
る。 Therefore, 90° pulse B1~BM and gradient magnetic field G Z2
Immediately after applying G X and G Y to the living body 1, gradient magnetic fields G X and G Y are applied to the living body 1. The magnetic flux direction of these gradient magnetic fields G X and G Y is in the Z-axis direction, and the magnetic flux density is
It changes linearly in both the axial and Y-axis directions.
そして、傾斜磁場GX及びGYを生体１に与えて
いる間に、生体１の近傍に配した適宜の検出コイ
ルにより前記部分d1〜dMの核磁気共鳴信号を検出
する。そして、この検出信号をコンピユータ処理
することにより前記部分d1〜dMについてそれぞれ
断層像を得るようになっている。 Then, while applying the gradient magnetic fields G X and G Y to the living body 1, nuclear magnetic resonance signals in the portions d 1 to d M are detected by appropriate detection coils placed near the living body 1 . Then, by computer processing this detection signal, tomographic images are obtained for each of the portions d1 to dM .
次に、上述の如く構成された本発明に係る
NMR―CT方法を用いたNMR−CT装置の動作
について説明する。 Next, according to the present invention configured as described above,
The operation of an NMR-CT apparatus using the NMR-CT method will be explained.
生体１の前記部分d1〜dMの核磁気モーメントは
180゜パルスＡ１〜AMと傾斜磁場GZ1を与えられ
たことにより、前記時間TAを隔てて時系列的に
Ｚ軸方向において反転する。そして、反転された
前記部分d1〜dMの核磁気モーメントは、90゜パル
スＢ１〜BMと傾斜磁場GZ2を与えられたことに
より核磁気共鳴を起こしてそれぞれXY平面内に
倒れ、核磁気共鳴信号を発する。次いで、生体１
に傾斜磁場GX及びGYを与えている間に、前記検
出コイルにより核磁気共鳴信号を検出する。そし
て、この検出信号を適宜に処理することにより、
前記部分d1〜dMについてそれぞれ断層像を得る。 The nuclear magnetic moment of the parts d 1 to d M of the living body 1 is
By applying the 180° pulses A1 to AM and the gradient magnetic field G Z1 , it is reversed in the Z-axis direction in time series at the time interval T A . Then, the nuclear magnetic moments of the inverted portions d 1 to d M cause nuclear magnetic resonance due to the application of the 90° pulses B 1 to BM and the gradient magnetic field G Z2 , and fall within the XY plane, resulting in nuclear magnetic Emit a resonance signal. Next, living body 1
While applying gradient magnetic fields G X and G Y to the detector coil, a nuclear magnetic resonance signal is detected by the detection coil. By processing this detection signal appropriately,
A tomographic image is obtained for each of the portions d1 to dM .
第４図は、前記NMR―CT装置で被検体のよ
り多くの部分の断層像を得る場合の動作波形図を
示している。この場合、各周期TB内に前記実施
例の場合に比してより多くの180゜パルスＡ１〜
AN（Ｍ＜Ｎ）を傾斜磁場GZ1と生体１に与えてい
る。そして、各周期TB内の最後の180゜パルスAN
を生体１に与えてから、次周期TBの最初の180゜パ
ルスＡ１を生体１に与える迄の時間TA′は例えば
前記所定時間TAと等しくしている。このため、
各周期TBの180゜パルスＡ１〜ANは生体１に所定
時間TAを隔てて連続的に与えられる。そして、
各周期TBの180゜パルスＡ１〜ANに対応した90゜パ
ルスＢ１〜BNも傾斜磁場GZ2と共に生体１に連
続的に与えられる。また、傾斜磁場GX及びGYも
前記時間TAを隔てて連続的に生体１に与えられ
る。なお、この場合前記所定時間TAは180゜パル
スＡ１〜ANと90゜パルスＢ１〜BNとが重ならな
いように定められる。 FIG. 4 shows an operation waveform diagram when obtaining tomographic images of a larger portion of the subject with the NMR-CT apparatus. In this case, within each period T B there are more 180° pulses A1~ than in the above embodiment.
AN (M<N) is applied to the gradient magnetic field G Z1 and the living body 1. and the last 180° pulse AN in each period T B
The time T A ′ from when 180° pulse A1 of the next period T B is applied to the living body 1 to when the first 180° pulse A1 of the next cycle T B is applied to the living body 1 is, for example, equal to the predetermined time TA . For this reason,
The 180° pulses A1 to AN of each cycle T B are continuously applied to the living body 1 at intervals of a predetermined time T A. and,
The 90° pulses B1 to BN corresponding to the 180° pulses A1 to AN of each period T B are also continuously applied to the living body 1 together with the gradient magnetic field G Z2 . Further, the gradient magnetic fields G X and G Y are also continuously applied to the living body 1 at intervals of the time T A . In this case, the predetermined time T A is determined so that the 180° pulses A1 to AN and the 90° pulses B1 to BN do not overlap.
ｅ 効 果
前記実施例において、所定時間TAは50〜100ｍ
secの範囲で適宜に設定され得るので、略１秒程
度を必要とする周期TB内に被検体の10〜20個所
の核磁気共鳴信号を得ることができる。このた
め、本発明に係るNMR―CT装置による場合、
従来のNMR―CT方法で被検体の特定の一個所
の断層像を得ていた時間、即ち４〜５分内に、被
検体の10〜20個所の断層像を得ることができる。
この結果、被検体の複数個所の断層像を得るため
の時間を大幅に短縮し得る。e Effect In the above embodiment, the predetermined time T A is 50 to 100 m.
Since it can be appropriately set within the range of seconds, it is possible to obtain nuclear magnetic resonance signals from 10 to 20 locations on the subject within a period T B that requires about 1 second. Therefore, when using the NMR-CT apparatus according to the present invention,
It is possible to obtain tomographic images of 10 to 20 locations on a subject within 4 to 5 minutes, which is the time required to obtain tomographic images of one specific location on the subject using conventional NMR-CT methods.
As a result, the time required to obtain tomographic images of multiple locations of the subject can be significantly shortened.
第１図は本発明に係るNMR―CT装置により
被検体の複数個所の断層像を得る様子を示す説明
図、第２図は同じくその動作波形図、第３図イは
前記NMR―CT装置に用いる180゜パルス及び90゜
パルスの周波数分布を示す波形図、同図ロはその
180゜パルスの時間波形の一例を示す波形図、第４
図は前記NMR―CT装置で被検体のより多くの
部分の断層像を得る場合の動作波形図である。
１……生体、Ａ１〜AM，Ａ１〜AN……180゜
パルス、Ｂ１〜BM，Ｂ１〜BN……90゜パルス、
GZ1，GZ2，GX，GY……傾斜磁場。
Fig. 1 is an explanatory diagram showing how tomographic images of multiple locations of a subject are obtained by the NMR-CT device according to the present invention, Fig. 2 is a diagram of its operation waveforms, and Fig. 3 A is an explanatory diagram showing how the NMR-CT device according to the present invention obtains tomographic images at multiple locations. A waveform diagram showing the frequency distribution of the 180° pulse and 90° pulse used;
Waveform diagram showing an example of the time waveform of a 180° pulse, No. 4
The figure is an operation waveform diagram when obtaining tomographic images of a larger portion of a subject with the NMR-CT apparatus. 1...Biological body, A1-AM, A1-AN...180° pulse, B1-BM, B1-BN...90° pulse,
G Z1 , G Z2 , G X , G Y ... Gradient magnetic field.
Claims (1)
断層像をインバージヨンリカバリ法により得る核
磁気共鳴コンピユータ断層撮影装置において、被
検体にＺ軸方向に沿って傾斜磁場を所定時間ごと
に与えるとともに、 所望位置の断層像を得るために前記傾斜磁場の
強さに応じて定められる周波数を中心とする周波
数帯域内で強さが一定の180゜パルスを前記傾斜磁
場と同時に与えることにより被検体の所望断面部
分の核磁気モーメントを順次反転させ、 前記核磁気モーメントを反転した断面に応じて
磁界強さ及び周波数分布が定められた傾斜磁場と
90゜パルスとを、前記傾斜磁場及び180゜パルスに
同期させ、かつ、所定の時間遅れを持たせてＺ軸
方向に沿って与えることによって、前記断面に核
磁気共鳴を順次起こさせ、このときの各断面の核
磁気共鳴信号をＸ方向、及びＹ方向の傾斜磁場を
与えて取り出すことに基づき所望位置の断層像を
得るようにしたことを特徴とする核磁気共鳴コン
ピユータ断層撮影装置。[Claims] 1. In a nuclear magnetic resonance computerized tomography system that obtains tomographic images of a subject placed in a magnetic field with uniform magnetic flux density by an inversion recovery method, the subject is tilted along the Z-axis direction. A magnetic field is applied at predetermined intervals, and in order to obtain a tomographic image at a desired position, a 180° pulse with a constant strength within a frequency band centered on a frequency determined according to the strength of the gradient magnetic field is applied to the gradient magnetic field. At the same time, the nuclear magnetic moment of a desired cross section of the object is sequentially reversed by applying a gradient magnetic field whose magnetic field strength and frequency distribution are determined according to the cross section where the nuclear magnetic moment is reversed.
A 90° pulse is synchronized with the gradient magnetic field and the 180° pulse, and is applied along the Z-axis direction with a predetermined time delay, thereby sequentially causing nuclear magnetic resonance in the cross section, and at this time, A nuclear magnetic resonance computer tomography apparatus characterized in that a tomographic image at a desired position is obtained by extracting nuclear magnetic resonance signals of each cross-section by applying gradient magnetic fields in the X direction and the Y direction.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57234244A JPS59125047A (en) | 1982-12-31 | 1982-12-31 | Computer-aided tomography method with nuclear magnetic resonance |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57234244A JPS59125047A (en) | 1982-12-31 | 1982-12-31 | Computer-aided tomography method with nuclear magnetic resonance |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS59125047A JPS59125047A (en) | 1984-07-19 |
| JPH0333325B2 true JPH0333325B2 (en) | 1991-05-16 |
Family
ID=16967933
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP57234244A Granted JPS59125047A (en) | 1982-12-31 | 1982-12-31 | Computer-aided tomography method with nuclear magnetic resonance |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS59125047A (en) |
Families Citing this family (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS62295651A (en) * | 1986-01-28 | 1987-12-23 | 横河メディカルシステム株式会社 | Nuclear magnetic resonance tomographic imaging apparatus |
Family Cites Families (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| GB1601970A (en) * | 1978-05-31 | 1981-11-04 | Nat Res Dev | Methods of deriving image information from objects |
| US4458203A (en) * | 1980-12-11 | 1984-07-03 | Picker International Limited | Nuclear magnetic resonance imaging |
-
1982
- 1982-12-31 JP JP57234244A patent/JPS59125047A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPS59125047A (en) | 1984-07-19 |
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