JPH0252278A - Scintillation camera - Google Patents
Scintillation cameraInfo
- Publication number
- JPH0252278A JPH0252278A JP20320388A JP20320388A JPH0252278A JP H0252278 A JPH0252278 A JP H0252278A JP 20320388 A JP20320388 A JP 20320388A JP 20320388 A JP20320388 A JP 20320388A JP H0252278 A JPH0252278 A JP H0252278A
- Authority
- JP
- Japan
- Prior art keywords
- inputted
- signals
- detectors
- position calculation
- circuit
- 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.)
- Granted
Links
- 239000011159 matrix material Substances 0.000 claims abstract description 13
- 230000005251 gamma ray Effects 0.000 abstract description 7
- 239000000463 material Substances 0.000 abstract 1
- 230000035945 sensitivity Effects 0.000 description 5
- 230000000694 effects Effects 0.000 description 4
- 238000009206 nuclear medicine Methods 0.000 description 3
- 238000010521 absorption reaction Methods 0.000 description 2
- 238000003745 diagnosis Methods 0.000 description 2
- 230000017531 blood circulation Effects 0.000 description 1
- 238000001514 detection method Methods 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 238000003384 imaging method Methods 0.000 description 1
- 238000004020 luminiscence type Methods 0.000 description 1
- 230000004060 metabolic process Effects 0.000 description 1
- 210000000056 organ Anatomy 0.000 description 1
- 229940121896 radiopharmaceutical Drugs 0.000 description 1
- 239000012217 radiopharmaceutical Substances 0.000 description 1
- 230000002799 radiopharmaceutical effect Effects 0.000 description 1
Landscapes
- Nuclear Medicine (AREA)
Abstract
Description
【発明の詳細な説明】
〔産業上の利用分野〕
本発明は、核医学画像診断に使用されるシンチレーショ
ンカメラに係シ、特に複数の検出器で構成する高感度を
指向したシンチレーションカメラに関する。DETAILED DESCRIPTION OF THE INVENTION [Industrial Application Field] The present invention relates to a scintillation camera used for nuclear medicine image diagnosis, and more particularly to a scintillation camera configured with a plurality of detectors and aimed at high sensitivity.
核医学画像診断装置として知られているシンチレーショ
ンカメラは人体の代謝、血流等に代表される臓器の機能
診断に適するが、人体に投与された放射性医薬品から放
射されるガンマ線情報の検出感度が低いことは一般に知
られている事実である。シンチレーションカメラに関連
する従来技術としては、例えば米国特許第3,011,
057号公報に示されている。Scintillation cameras, known as nuclear medicine imaging diagnostic devices, are suitable for functional diagnosis of organs such as metabolism and blood flow in the human body, but have low sensitivity for detecting gamma ray information emitted from radiopharmaceuticals administered to the human body. This is a generally known fact. As prior art related to scintillation cameras, for example, US Pat. No. 3,011,
This is shown in Publication No. 057.
核医学画像診断装置として知られているシンチレーショ
ンカメラにおいて、その感度を向上させる目的で検出器
を複数個にし人体よシ放射されるガンマ線情報をよシ有
効に利用する2検出器形シンチV−ジョンカメラまたは
多検出器形シンチレーションカメラがある。しかし、シ
ンチレーショ/カメラの検出器を複数にして装置の検出
感度を向上させる場合、それに付随するコストの上昇に
ついて十分な配慮がなされていなかった。In order to improve the sensitivity of scintillation cameras, which are known as nuclear medicine image diagnostic devices, a two-detector type scintillation V-joon is used that uses multiple detectors to more effectively utilize gamma ray information emitted from the human body. There are cameras or multi-detector scintillation cameras. However, when increasing the detection sensitivity of the device by using a plurality of scintillation/camera detectors, sufficient consideration has not been given to the accompanying cost increase.
従来技術では、これら複数の検出器をもつシンチレーシ
ョンカメラの位置計算回路は検出器の数と同数で構成し
ているが、保有すべきガンマ線情報の量からみて位置計
算回路の処理能力に余裕があり、経済性の観点からまだ
改善すべき点が残されている。In conventional technology, a scintillation camera with multiple detectors has the same number of position calculation circuits as the number of detectors, but considering the amount of gamma ray information that must be stored, the position calculation circuit has sufficient processing capacity. However, there are still points that need to be improved from an economic standpoint.
本発明の目的は、装置の感度向上を狙って複数の検出器
で構成するシンチレーションカメラにおいて、検出器の
信号からガンマ線像をつくる最適な位置計算回路を構成
することにより、さらに経済性の優れた装を全提供する
ことにある。The purpose of the present invention is to improve the sensitivity of the device by configuring an optimal position calculation circuit for creating a gamma ray image from the detector signals in a scintillation camera configured with multiple detectors. The goal is to provide all equipment.
上記目的は、板状のシンチレータに光電子増倍管を光学
的に結合した検出器とシンチレータの発光位置を求める
位置計算手段とを有し%核検出器が複数個からなるシン
チレーションカメラにおいて、該位置計算手段が該複数
検出器の出力信号のうちの発光位置情報を一括する行列
加算器、該行列加算器の出力により発光位置を計算する
位置計算回路、該複数検出器の出力信号から前記発光位
置計算結果に対応する検出器を識別する弁別器を具備す
ることを特徴とするシンチレーションカメラ、及び上記
位置計算回路の個数を上記検出器の数より少くすること
により、達成される。The above object is to provide a scintillation camera consisting of a plurality of nuclear detectors, which includes a detector in which a photomultiplier tube is optically coupled to a plate-shaped scintillator, and a position calculation means for determining the light emitting position of the scintillator. The calculation means includes a matrix adder that collectively collects light emission position information among the output signals of the plurality of detectors, a position calculation circuit that calculates the light emission position based on the output of the matrix adder, and a position calculation circuit that calculates the light emission position from the output signals of the plurality of detectors. This is achieved by a scintillation camera characterized by being equipped with a discriminator for identifying a detector corresponding to a calculation result, and by making the number of the position calculation circuits smaller than the number of detectors.
以下、本発明の一実施例を第1図により説明する。 An embodiment of the present invention will be described below with reference to FIG.
第1図は検出器数が4個で1位置計算回路が1個で構成
する実施例である。被検体1よシ時間的に離散した全方
向に放射するガンマ線は検出器Di、D2.D3.D4
に装着したコリメータ2のそれぞれに対して直角な方向
のガンマ線だけが通過してシンチレータ3に到達して発
光する。つぎに、この発光はシンチレータ3に2次元に
配列された光電子増倍管4で検出、増幅され、さらにプ
リアンプ5によりミ圧信号に変換され、信号81〜S4
として行列加算器6に入力される。行列加算器6に入力
された信号S1〜S4は発光位置を計算するだめのデー
タとして使用される。ここで、各検出器Di、D2.D
3.D4に対する個々の行列信号を同じ行列について重
ねて加算することで、4個の検出器D1〜D4に対する
共通の総合行列信号Σxl、Σyr’t、得る。つぎに
、この総合行列信号ΣXl、ΣYjは通常の位置計算回
路8に入力されて、検出器DI、D2.D3゜U4で検
出したカンマ線を検出器DI、D2゜U3.U4の区別
なく一括して位置計算した後、その計算値X、 Yを弁
別器9に入力する。FIG. 1 shows an embodiment in which the number of detectors is four and one position calculation circuit is provided. Gamma rays emitted from the subject 1 in all temporally discrete directions are detected by detectors Di, D2. D3. D4
Only gamma rays in a direction perpendicular to each of the collimators 2 attached to the scintillator 3 pass through, reach the scintillator 3, and emit light. Next, this light emission is detected and amplified by the photomultiplier tubes 4 arranged two-dimensionally in the scintillator 3, and further converted into a pressure signal by the preamplifier 5, and the signals 81 to S4
It is input to the matrix adder 6 as . The signals S1 to S4 input to the matrix adder 6 are used as data for calculating the light emission position. Here, each detector Di, D2. D
3. By superimposing and adding the individual matrix signals for D4 for the same matrix, a common total matrix signal Σxl, Σyr't for the four detectors D1 to D4 is obtained. Next, the total matrix signals ΣXl, ΣYj are input to a normal position calculation circuit 8, and the detectors DI, D2 . The comma ray detected by D3°U4 is sent to detector DI, D2°U3. After calculating the position of U4 all at once without distinction, the calculated values X and Y are input to the discriminator 9.
他方、検出器DI、D2.D3.D4についてそれぞれ
に付随する光電子増倍管4の信号Sl。On the other hand, the detectors DI, D2. D3. The signal Sl of the photomultiplier tube 4 associated with each for D4.
S2.S3.S4を2信号加算器7に入力して、ノンチ
レータ発光の時間データとして使用される。S2. S3. S4 is input to the two-signal adder 7 and used as time data for non-tilator light emission.
2信号加算器7に入力した信号Sl、S2.S3゜S4
は検出器D1.D2.D3.D4が検出したガンマ線に
よる全発光量(光電吸収ピーク)信号SZI、SZ2.
SZ3,5Z4(r得て、これを検出器DI、D2.D
3.D4に対応する波高分析器12にそれぞれ入力する
。波高分析器12の出力Ul、U2.U3.U4は全発
光量信号SZ 1゜SZ2.SZ3.SZ4の波高値が
ガンマ線の全吸収に相当する場合のみ出力すると同時に
、ガンマ線が入射した検出器Di、D2.D3.D4を
識別できる。ここで、信号Ul、U2.U3゜U4ff
i上記の弁別器9に入力することにより、位置計算回路
8の計算結果X、 YとUl、 U2゜U3.U4とを
対応させる。その上で、X、Y。The signals Sl, S2 . S3゜S4
is detector D1. D2. D3. Total luminescence amount (photoelectric absorption peak) signals SZI, SZ2.D4 due to gamma rays detected by D4.
SZ3,5Z4 (obtain r and use it as detector DI, D2.D
3. Each signal is input to the pulse height analyzer 12 corresponding to D4. Outputs Ul, U2 . of the wave height analyzer 12 . U3. U4 is the total light emission amount signal SZ1°SZ2. SZ3. It outputs only when the peak value of SZ4 corresponds to the total absorption of gamma rays, and at the same time the detectors Di, D2 . D3. D4 can be identified. Here, signals Ul, U2 . U3゜U4ff
By inputting i to the above discriminator 9, the calculation results of the position calculation circuit 8 are X, Y and Ul, U2゜U3. Make it correspond to U4. On top of that, X, Y.
Ul 、X、Y、U2 、X、Y、U3 、X、y。Ul ,X,Y,U2 ,X,Y,U3 ,X,y.
U4のデータを検出器DI、D2.D3.D4と対をな
す補正回路10に入力し、各検出器D1゜U2.U3.
U4が持つ固有の空間歪などを補正すべき補正定数C1
,C2,C3,C4で補正をして、位置座標を記憶する
メモリ11に取シ込まれる。以上述べたような手順で1
個の位置計算回路8を用いて4個の検出器Di、 U2
. U3゜U4による発光位置の計算が実施される。こ
の場合、最終の出力信号X、 Yは上述の如くメモリ1
1から検出器DI、D2.D3.D4に対する輝度変調
信号Ul、U2.U3.U4と一対をなして出力される
。The data of U4 is sent to detectors DI, D2. D3. D4 is input to the correction circuit 10 paired with each detector D1゜U2 . U3.
Correction constant C1 to correct the inherent spatial distortion etc. of U4
, C2, C3, and C4, and the data is imported into the memory 11 that stores the position coordinates. 1 by following the steps described above.
four detectors Di, U2 using four position calculation circuits 8;
.. The light emitting position is calculated using U3°U4. In this case, the final output signals X and Y are stored in the memory 1 as described above.
1 to detectors DI, D2. D3. Luminance modulation signals Ul, U2 . U3. It is output as a pair with U4.
上記の実施例としては、検出器数が4個の場合について
述べたが、検出器数は4個に限定されることなく他の複
数の検出器の場合にも適用できる。In the above embodiment, the case where the number of detectors is four has been described, but the number of detectors is not limited to four and can also be applied to cases where a plurality of other detectors are used.
また、位置計算回路の数も上記実施例の1個に限定され
ることなく検出器数より少なければ効果が得られるので
、それらの場合にも適用可能である。Further, the number of position calculation circuits is not limited to one as in the above embodiment, and the effect can be obtained as long as it is smaller than the number of detectors, so the present invention is applicable to those cases as well.
本発明によれば、複数の検出器で構成するシンチレーシ
ョンカメラにおいて、その位置計算回路は少なくとも1
つで構成できるので、簡略化による効果、例えば4検出
器で構成する装置の場合、その位置計算回路は従来の1
/4にすることができ、単に経済的な効果ばかシでなく
軽量、小形化にも大きな効果が得られる。According to the present invention, in a scintillation camera configured with a plurality of detectors, at least one position calculation circuit is provided.
For example, in the case of a device consisting of four detectors, the position calculation circuit can be configured with one conventional one.
/4, which not only provides an economical effect, but also provides a significant effect in reducing weight and size.
第1図は本発明の一実施例のブロック構成図を示す。
1・・・被検体、2・・・コリメータ、3・・・シンチ
レータ、4・・・光電子増倍管、5・・・プリアンプ、
6・・・行列加算器、7・・・2信号加算器、8・・・
位置計算回路、9・・・弁別器、10・・・補正回路、
11・・・メモリ、12・・・波高分析器。FIG. 1 shows a block diagram of an embodiment of the present invention. 1... Subject, 2... Collimator, 3... Scintillator, 4... Photomultiplier tube, 5... Preamplifier,
6... Matrix adder, 7... 2-signal adder, 8...
Position calculation circuit, 9... Discriminator, 10... Correction circuit,
11... Memory, 12... Wave height analyzer.
Claims (1)
した検出器とシンチレータの発光位置を求める位置計算
手段とを有し、該検出器が複数個からなるシンチレーシ
ョンカメラにおいて、該位置計算手段が該複数検出器の
出力信号のうちの発光位置情報を一括する行列加算器、
該行列加算器の出力により発光位置を計算する位置計算
回路、該複数検出器の出力信号から前記発光位置計算結
果に対応する検出器を識別する弁別器を具備することを
特徴とするシンチレーションカメラ。 2、上記位置計算回路の個数が上記検出器の数より少い
ことを特徴とする請求項1記載のシンチレーションカメ
ラ。[Claims] 1. A scintillation camera comprising a plurality of detectors, including a detector in which a photomultiplier tube is optically coupled to a plate-shaped scintillator, and a position calculation means for determining the light emitting position of the scintillator. wherein the position calculation means is a matrix adder that collectively collects light emission position information among the output signals of the plurality of detectors;
A scintillation camera comprising: a position calculation circuit that calculates a light emission position based on the output of the matrix adder; and a discriminator that identifies a detector corresponding to the light emission position calculation result from the output signals of the plurality of detectors. 2. The scintillation camera according to claim 1, wherein the number of said position calculation circuits is smaller than the number of said detectors.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP20320388A JP2691573B2 (en) | 1988-08-17 | 1988-08-17 | Scintillation camera |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP20320388A JP2691573B2 (en) | 1988-08-17 | 1988-08-17 | Scintillation camera |
Publications (2)
Publication Number | Publication Date |
---|---|
JPH0252278A true JPH0252278A (en) | 1990-02-21 |
JP2691573B2 JP2691573B2 (en) | 1997-12-17 |
Family
ID=16470176
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP20320388A Expired - Lifetime JP2691573B2 (en) | 1988-08-17 | 1988-08-17 | Scintillation camera |
Country Status (1)
Country | Link |
---|---|
JP (1) | JP2691573B2 (en) |
Cited By (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPH0934486A (en) * | 1995-07-19 | 1997-02-07 | Sony Corp | Method and device for voice acknowledgement, information forming method, and recording medium |
KR20000051947A (en) * | 1999-01-28 | 2000-08-16 | 윤종용 | Gamma camera system |
US6503093B1 (en) | 1996-07-31 | 2003-01-07 | Hirose Electric Co., Ltd. | Circuit board electrical connector |
WO2020040154A1 (en) | 2018-08-22 | 2020-02-27 | 東レ株式会社 | Production method for prepreg, prepreg tape, and fiber reinforced composite material, and prepreg production device |
-
1988
- 1988-08-17 JP JP20320388A patent/JP2691573B2/en not_active Expired - Lifetime
Cited By (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPH0934486A (en) * | 1995-07-19 | 1997-02-07 | Sony Corp | Method and device for voice acknowledgement, information forming method, and recording medium |
US6503093B1 (en) | 1996-07-31 | 2003-01-07 | Hirose Electric Co., Ltd. | Circuit board electrical connector |
KR20000051947A (en) * | 1999-01-28 | 2000-08-16 | 윤종용 | Gamma camera system |
WO2020040154A1 (en) | 2018-08-22 | 2020-02-27 | 東レ株式会社 | Production method for prepreg, prepreg tape, and fiber reinforced composite material, and prepreg production device |
Also Published As
Publication number | Publication date |
---|---|
JP2691573B2 (en) | 1997-12-17 |
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