JPS5892973A - Radiation detector for emission ct apparatus - Google Patents
Radiation detector for emission ct apparatusInfo
- Publication number
- JPS5892973A JPS5892973A JP19249781A JP19249781A JPS5892973A JP S5892973 A JPS5892973 A JP S5892973A JP 19249781 A JP19249781 A JP 19249781A JP 19249781 A JP19249781 A JP 19249781A JP S5892973 A JPS5892973 A JP S5892973A
- Authority
- JP
- Japan
- Prior art keywords
- output
- circuit
- input terminal
- discriminator
- scintillator
- 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
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
- G01T1/2914—Measurement of spatial distribution of radiation
- G01T1/2985—In depth localisation, e.g. using positron emitters; Tomographic imaging (longitudinal and transverse section imaging; apparatus for radiation diagnosis sequentially in different planes, steroscopic radiation diagnosis)
Landscapes
- Physics & Mathematics (AREA)
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- General Physics & Mathematics (AREA)
- High Energy & Nuclear Physics (AREA)
- Molecular Biology (AREA)
- Spectroscopy & Molecular Physics (AREA)
- Measurement Of Radiation (AREA)
- Nuclear Medicine (AREA)
Abstract
Description
【発明の詳細な説明】
本発明は、エミツションＣＴ装置用放射線検出装置に関
する。DETAILED DESCRIPTION OF THE INVENTION The present invention relates to a radiation detection device for an emission CT device.
従来のリング型エミツションＣＴ装置にハ、１つのシン
チレータに対し、１つの光電子増倍管を使用しているが
、全身器官用又は高分解能のエミツションＣＴ装置では
、多数のシンチレータｔ［用するので、光電子増倍管の
数も増大し、自ずと装置が大型となり、価格も高くなる
。Conventional ring-type emission CT devices use one photomultiplier tube for one scintillator, but in a whole-body organ or high-resolution emission CT device, a large number of scintillators are used. As the number of photomultiplier tubes increases, the device naturally becomes larger and more expensive.
本発明の目的は、２つのシンチレータは各光電子増倍管
の細心に配列され、もう１つのシンチレータは該２つの
光電子増倍管にまたがって配列された、２つの光電子増
倍管部に対して少くとも３つ、多くて５つのシンチレー
タが接続可能で、さらに工・ネルギー弁別も一時に行な
われる、メエミッションＣＴ装置用放射線検出装置を提
供するにある０
本発明の好適な実施例を図面について説明する図面は、
本発明の一実施例を示す構成ブロック図である０これに
より、シンチレータ１ ａ ％ １ ｂ ｓ Ｌ ｃの
どれにγ線が入射したかは、検出ゲー）７ａ、７ｂ。It is an object of the present invention to provide two scintillators arranged meticulously in each photomultiplier tube, and another scintillator arranged across the two photomultiplier tubes for the two photomultiplier sections. It is an object of the present invention to provide a radiation detection device for a emission CT device, which can connect at least three scintillators and at most five scintillators, and also performs energy and energy discrimination at the same time. The drawings to explain are
1 is a configuration block diagram showing an embodiment of the present invention. Accordingly, it is possible to determine which of the scintillators 1a%1bsLc the gamma rays have entered in the detection game) 7a, 7b.
７ｃのどれより出力が検知されるかにより識別さ、れる
。7c from which the output is detected.
９示の実施例によれば、軸心のシンチレータ１＆又ｉ
１ｂについては、光電子増倍管２Ａ又は２Ｂ。According to the embodiment shown in FIG. 9, the scintillator 1 & also i
For 1b, photomultiplier tube 2A or 2B.
増幅器３、ディスクリミネータへ介してその出力を一方
一の入力端とした検出ゲート回路７８又は７Ｃ金具有し
、他の入力端は光電子増倍管２Ａ又は２Ｂ、増幅器３、
波高弁別器９ａ又は９ ｃｓ Ｎ Ａ Ｎ Ｄ演算の非
同時計数回路６ａ又は６Ｃを介してその出力に接続され
、また交叉シンチレータについては、両電子増倍管２Ａ
及び２Ｂ、ディスクリミネータ４を介してその各出力の
ＡＮＤ演算を行う同時引数回路５ｂに接続され、その出
力を一方の入力−とした積出ゲート回路７ｂｉ具有し、
他方の入力端は、両 □光電子増倍管２Ａ及び２Ｂ
、増幅器３、各出力の加算回路ｓｂ４．正！用増幅器１
０ ｂ 、波高弁別器９ａ、を介してその出力に接続さ
れており、さらに同時計数回路５ｂの出力が２つの非同
時計数回路にも接続されるＯ
図・水側構成において、シンチレータ１ａにγ線が入射
した場合には、光電子増倍管２Ａからのみ出力信号゛が
存在し、同時計数回路５ｂからは出力がないので、他方
波高弁別器９ａの出力のみが、ＮＡＮＤＡＮＤ演算時計
数回路６ａｔ−介して、検出ゲート回路７ａに゛入９、
エネルギー弁別された信号−が検出端に認められる。シ
ンチレータ１ｂにγ線が入射すると、光電増倍管２Ａ及
び２Ｂ両方から信号が出る。次いで、両川力信号のＡＮ
Ｄ演算を行う同時計数回路５ｂは、検出ゲート回路７ｂ
の一方入力端へ出力信号を送り、□他方加算器８ｂで足
された波高信号が、波高弁別器９ｂで波高弁別されて他
方の入力端へ送られ、検出ゲート回路７ｂからエネルギ
ー弁別された信号が出力する。シンチレータ１＆Ｃγ線
が入射した場合には、軸心シンチレータａの時の同様に
信号Ｃが出力する。The amplifier 3 has a detection gate circuit 78 or 7C metal fitting whose output is connected to one input terminal through a discriminator, and the other input terminal is a photomultiplier tube 2A or 2B, the amplifier 3,
It is connected to the output of the pulse height discriminator 9a or 9cs via the non-coincidence counting circuit 6a or 6C for NAND calculation, and for the crossover scintillator, both electron multiplier tubes 2A
and 2B, which is connected via a discriminator 4 to a simultaneous argument circuit 5b that performs an AND operation on each of its outputs, and has an output gate circuit 7bi with its output as one input.
The other input end is connected to both □photomultiplier tubes 2A and 2B.
, amplifier 3, and an adder circuit sb4 for each output. Correct! amplifier 1
0b is connected to its output via the wave height discriminator 9a, and the output of the coincidence circuit 5b is also connected to two non-coincidence circuits. When a beam is incident, there is an output signal only from the photomultiplier tube 2A, and there is no output from the coincidence circuit 5b, so only the output of the wave height discriminator 9a is output from the NAND AND operation clock circuit 6at-. into the detection gate circuit 7a through 9,
An energy-discriminated signal is recognized at the detection end. When γ-rays are incident on the scintillator 1b, signals are output from both photomultiplier tubes 2A and 2B. Next, the AN of Ryokawa Riki signal
The coincidence circuit 5b that performs the D calculation is a detection gate circuit 7b.
An output signal is sent to one input terminal of □, and the pulse height signal added by the adder 8b is subjected to pulse height discrimination by the pulse height discriminator 9b and sent to the other input terminal, and the energy-discriminated signal is output from the detection gate circuit 7b. outputs. When the scintillator 1 & C gamma rays are incident, a signal C is output in the same way as in the case of the axial scintillator a.
また、他の実施態様によれば、図示構成例のうち、加算
器８ｂ、波高弁別器９ａ、９ｂ、・９ｃｉ省略し、他方
ディスクリミネータ４を波高弁別器に代え、また非同時
計数回路６ａ、６ｃをインバータに代え、さらに検出ゲ
ート回路７ｂヲ省略して同時計数回路６ａの出力を交叉
シンチレータの検出端として構成することも可能である
。According to another embodiment, the adder 8b and the pulse height discriminators 9a, 9b, and 9ci are omitted from the illustrated configuration example, the discriminator 4 is replaced with a pulse height discriminator, and the noncoincident counting circuit 6a is replaced with a pulse height discriminator. , 6c may be replaced with inverters, and the detection gate circuit 7b may be omitted, and the output of the coincidence circuit 6a may be configured as the detection terminal of a cross scintillator.
なお、シンチレータの配列態′様について、マルゲスラ
イスのリング型エミツションＣＴ装置の一合は、フライ
ス方向のシンチレータ配列にも適用できる。Regarding the arrangement of the scintillators, the arrangement of the ring-type emission CT device for the Maruge slice can also be applied to the scintillator arrangement in the milling direction.
シンチレータをリング状に配列すれば、光電、子増倍管
の数をシンチレータの数の４にでき、また、÷ルチスラ
イス、例えば３リングのエミツションＣＴ装置に適用す
れば、光電子増倍管の数は、レンチレータの数のし と
なり、その作用効果は顕著であ仝。If the scintillators are arranged in a ring shape, the number of photomultiplier tubes can be reduced to 4, which is the number of scintillators.If applied to a multi-slice, for example, a 3-ring emission CT device, the number of photomultiplier tubes can be reduced to 4. , the number of lentilators is greater, and its effects are remarkable.
本発明は、さらに、ポジトロン・エミツションＣＴ装置
、シングルフォトンエミツションＣＴ装置の両方に適用
できる。The present invention is further applicable to both positron emission CT devices and single photon emission CT devices.
図面は、本発明の一実施例を示した構成ブロック図であ
る。
１はシンチレータ、２は光電子増倍管、３は増幅器、４
はディスクリミネータ、５は同時計数回路、６は非同時
計数回路、７はゲート回路、８は加算回路、−９は波高
弁別器、１０は補正用増幅器である。The drawing is a configuration block diagram showing one embodiment of the present invention. 1 is a scintillator, 2 is a photomultiplier tube, 3 is an amplifier, 4
5 is a coincidence circuit, 6 is a non-coincidence counting circuit, 7 is a gate circuit, 8 is an addition circuit, -9 is a pulse height discriminator, and 10 is a correction amplifier.
Claims (1)
され、もう１つのシンチレータは該２つの光電子増倍管
にまたがって配列（交叉）された、２つの光電子増倍管
組に対しで少くとも３つのシンチレータが接続された型
式において、軸心シンチレータ（ｌａ又Ｉｄｌｅ）につ
いては、光電子増倍管（２Ａ又Ｈ２Ｂ）、ディスクリミ
ネータ（４）ｋＶしてその出力を一方の入力端とした検
出ゲート回路（７ａ又は７ｃ）ｔ”具有し、他方の入力
端は光電子増倍管（２Ａ又Ｈ２Ｂ）、波高弁別器（９ａ
又は９ｃ）と非同時計数回路（６ａ又Ｕ６ｃ）とを介し
てそのネータ（４）とを介してその各出力の同時計数回
路（５ｂ）に接続され、その出力を一方の入力端とした
検出ゲート回路（７ｂ）′Ｉ！−具有し、他方の入力端
は両光電子増倍管出力の加算回路（８ｂ）と補正波高弁
別器（９ｂ）とを介してその出力に接続され、さらに同
時計数回路（５ｂ）の出力が非同時計数回路（６ａ、２
、特許請求の範囲第１項において、加算器（８ｂ）、波
高弁別器（９ａ、９ｂ、９ｃ）ｅ省略し、またディスク
リミネータ（４）全波高弁別器に代え、非同時計数回路
（６ａ及び６ｃ）をインバータに代え、さらに検出ゲー
ト回路（７ｂ）を省略して同時計数回路（６ａ）の出力
を交叉シンチレータの検出端としたことを特徴とする、
エミツションＣＴ装置用放射線検出装置。1) Two scintillators are arranged at the axis of each photomultiplier tube, and another scintillator is arranged across the two photomultiplier tubes (crossing), for two sets of photomultiplier tubes. In the type in which at least three scintillators are connected, for the axial scintillator (LA or Idle), the output of the photomultiplier tube (2A or H2B) and discriminator (4) kV is connected to one input terminal. The other input terminal has a photomultiplier tube (2A or H2B) and a pulse height discriminator (9a or H2B).
or 9c) and a noncoincident counting circuit (6a or U6c), and the output is connected to the coincidence counting circuit (5b) of each output via its inator (4), and the output is used as one input terminal for detection. Gate circuit (7b)'I! - the other input terminal is connected to the output of both photomultiplier tube outputs via an adder circuit (8b) and a correction pulse height discriminator (9b), and the output of the coincidence circuit (5b) is Coincidence circuit (6a, 2
, in claim 1, the adder (8b), the wave height discriminator (9a, 9b, 9c)e are omitted, and the discriminator (4) is replaced with the full wave height discriminator, and a noncoincident counting circuit (6a) is omitted. and 6c) are replaced with inverters, the detection gate circuit (7b) is omitted, and the output of the coincidence circuit (6a) is used as the detection terminal of the crossing scintillator,
Radiation detection device for emission CT equipment.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP19249781A JPS5892973A (en) | 1981-11-30 | 1981-11-30 | Radiation detector for emission ct apparatus |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP19249781A JPS5892973A (en) | 1981-11-30 | 1981-11-30 | Radiation detector for emission ct apparatus |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS5892973A true JPS5892973A (en) | 1983-06-02 |
| JPH0416756B2 JPH0416756B2 (en) | 1992-03-25 |
Family
ID=16292284
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP19249781A Granted JPS5892973A (en) | 1981-11-30 | 1981-11-30 | Radiation detector for emission ct apparatus |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS5892973A (en) |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS60250280A (en) * | 1984-05-24 | 1985-12-10 | クレイトン フアウンデイシヨン フオ− リサ−チ | Positron radiation tomographic radiation camera |
| JPS6132984U (en) * | 1984-07-31 | 1986-02-27 | 株式会社島津製作所 | Radiation detector for ECT |
| JPH0624807U (en) * | 1992-07-17 | 1994-04-05 | 株式会社新来島どっく | Hand drill with level |
| JP2007183149A (en) * | 2006-01-06 | 2007-07-19 | Institute Of Physical & Chemical Research | Neutron detector |
-
1981
- 1981-11-30 JP JP19249781A patent/JPS5892973A/en active Granted
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS60250280A (en) * | 1984-05-24 | 1985-12-10 | クレイトン フアウンデイシヨン フオ− リサ−チ | Positron radiation tomographic radiation camera |
| JPS6132984U (en) * | 1984-07-31 | 1986-02-27 | 株式会社島津製作所 | Radiation detector for ECT |
| JPH0624807U (en) * | 1992-07-17 | 1994-04-05 | 株式会社新来島どっく | Hand drill with level |
| JP2007183149A (en) * | 2006-01-06 | 2007-07-19 | Institute Of Physical & Chemical Research | Neutron detector |
Also Published As
| Publication number | Publication date |
|---|---|
| JPH0416756B2 (en) | 1992-03-25 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| JPS5892973A (en) | Radiation detector for emission ct apparatus | |
| Kulberg et al. | Improved resolution of the Anger scintillation camera through the use of threshold preamplifiers | |
| US2584138A (en) | Radioactivity detector and discriminator | |
| US3717763A (en) | Scintillation camera device | |
| JPH0623670B2 (en) | Photomultiplier tube | |
| Derenzo et al. | Dynamic positron emission tomography in man using small bismuth germanate crystals | |
| JPS6183985A (en) | Scintillation detector | |
| JPH07104072A (en) | Ect device | |
| JPS62203078A (en) | Radiation position detector | |
| GB1070657A (en) | Low background radiation detection | |
| JPS62135787A (en) | Detector of positron ct device | |
| CN215914647U (en) | Gamma probe and gamma detection system comprising same | |
| JPS5850500A (en) | Wide range monitoring device | |
| JP2653047B2 (en) | Radiation detector | |
| JP3065625B2 (en) | Radiation detector | |
| JPH0572554B2 (en) | ||
| JPH0247712B2 (en) | ||
| JPS5814071A (en) | Simultaneous counter in a positron ct device | |
| KR20130052328A (en) | Radiation diagnosis apparatus | |
| JPS62167493A (en) | Gamma camera | |
| JPS61226676A (en) | Method for correcting scattered radiation of radioactive ray position detector | |
| JPH0340354B2 (en) | ||
| JPH02262088A (en) | Gamma camera | |
| JPH0264496A (en) | Triple coincidence count circuit | |
| US6297490B1 (en) | Method and apparatus for determining the centre photodetector in a digital scintillation camera |