JPH0310188A - Radiation detector - Google Patents
Radiation detectorInfo
- Publication number
- JPH0310188A JPH0310188A JP1146505A JP14650589A JPH0310188A JP H0310188 A JPH0310188 A JP H0310188A JP 1146505 A JP1146505 A JP 1146505A JP 14650589 A JP14650589 A JP 14650589A JP H0310188 A JPH0310188 A JP H0310188A
- Authority
- JP
- Japan
- Prior art keywords
- elements
- scintillator
- light
- rays
- spacer
- 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
- 230000005855 radiation Effects 0.000 title claims description 13
- 125000006850 spacer group Chemical group 0.000 abstract description 18
- 239000000853 adhesive Substances 0.000 abstract description 7
- 230000001070 adhesive effect Effects 0.000 abstract description 7
- 230000002265 prevention Effects 0.000 abstract 1
- 239000003795 chemical substances by application Substances 0.000 description 10
- 238000010586 diagram Methods 0.000 description 4
- 230000000694 effects Effects 0.000 description 4
- 230000006866 deterioration Effects 0.000 description 3
- 238000004519 manufacturing process Methods 0.000 description 2
- 239000002184 metal Substances 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- OAICVXFJPJFONN-UHFFFAOYSA-N Phosphorus Chemical compound [P] OAICVXFJPJFONN-UHFFFAOYSA-N 0.000 description 1
- 230000002411 adverse Effects 0.000 description 1
- 230000000903 blocking effect Effects 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 238000003745 diagnosis Methods 0.000 description 1
- 239000011521 glass Substances 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 239000003973 paint Substances 0.000 description 1
- 239000000758 substrate Substances 0.000 description 1
Landscapes
- Apparatus For Radiation Diagnosis (AREA)
- Measurement Of Radiation (AREA)
Abstract
Description
【発明の詳細な説明】
［発明の目的］
（産業上の利用分野）
本発明は、放射線診断装置の放射線検出器用蛍光体をカ
ッテングブレードまたはワイヤソーにより所定のピッチ
で切断することにより複数のシンチレータ素子を併設し
入射Ｘ線を光電変換する放射線検出器に関する。Detailed Description of the Invention [Objective of the Invention] (Industrial Field of Application) The present invention provides a method for cutting a phosphor for a radiation detector of a radiological diagnostic apparatus at a predetermined pitch with a cutting blade or a wire saw to produce a plurality of scintillator elements. The present invention relates to a radiation detector that is equipped with a radiation detector and photoelectrically converts incident X-rays.
（従来の技術）
放射線診断装置例えばＸｔｌＣＴ装置は、Ｘ線を被検体
に***しながら被検体に対して回動するＸ！９１管、こ
のＸ線管に対向して設けられこのＸ線管から被検体を透
過したＸ線を検出する検出器を具備して構成されている
。前記Ｘ線管が被検体を回動しながら所定角度でＸ線を
***し、検出器から検出される角度ごとのデータを再構
成処理し、表示装置に良好な断層像を得ている。このよ
うに良好な断層像を得るためには例えば前記検出器の性
能が要求される。また前記検出器は、Ｘ線管から***さ
れ被検体を透過したＸ線を光に変換するシンチレータと
、このシンチレータがらの光を受光するフォトダイオー
ドと備えている。従来この種のｘｌ検出器は次のように
構成されている。(Prior Art) A radiological diagnostic device, such as an XtlCT device, rotates with respect to the subject while emitting X-rays to the subject. 91 tube, and a detector provided opposite to the X-ray tube to detect X-rays transmitted through the subject from the X-ray tube. The X-ray tube emits X-rays at a predetermined angle while rotating the subject, reconstructs data detected by the detector for each angle, and obtains a good tomographic image on a display device. In order to obtain such a good tomographic image, for example, the performance of the detector is required. Further, the detector includes a scintillator that converts the X-rays emitted from the X-ray tube and transmitted through the subject into light, and a photodiode that receives the light from the scintillator. Conventionally, this type of xl detector is configured as follows.
第４図は従来の多チヤンネル型Ｘ線検出器を示す概略斜
視図、第５図は前記第４図に示すＸ線検出器のフォトダ
イオードの詳細を示す図、第６図は従来のシンチレータ
素子群の製造方法を示す概略図である。FIG. 4 is a schematic perspective view showing a conventional multi-channel X-ray detector, FIG. 5 is a diagram showing details of the photodiode of the X-ray detector shown in FIG. 4, and FIG. 6 is a conventional scintillator element. FIG. 2 is a schematic diagram showing a method of manufacturing the group.
第４図に示すようにＸ線検出器は、プリント配線基板７
と、この基板７の上に積層され複数の光電変換素子を有
するフォトダイオード５と、このフォトダイオード５の
上に複数に併設して設けられるシンチレータ素子１と、
この各シンチレータ素子１と交互に併設される第１の光
反射部材としての光反射剤２とを備えて構成される。ま
た第５図に示すように前記フォトダイオード５の表面に
は複数のフォトダイオード素子４が前記シンチレータ素
子１に対応して併設され、この各フォトダイオード素子
４の端縁には信号を取出すための端子６が設けられてい
る。これらの端子６はプリント配線基板７の端子に図示
しないワイヤボンディング等で接続されている。As shown in FIG. 4, the X-ray detector includes a printed wiring board 7
A photodiode 5 stacked on this substrate 7 and having a plurality of photoelectric conversion elements, a plurality of scintillator elements 1 provided side by side on this photodiode 5,
It is configured to include each scintillator element 1 and a light reflecting agent 2 as a first light reflecting member which is arranged alternately. Further, as shown in FIG. 5, a plurality of photodiode elements 4 are provided on the surface of the photodiode 5 in correspondence with the scintillator element 1, and at the edge of each photodiode element 4 there is a A terminal 6 is provided. These terminals 6 are connected to terminals of a printed wiring board 7 by wire bonding or the like (not shown).
このように構成されたＸ線検出器は、従来次のようにし
て製造されていた。すなわち第６図に示すように図示し
ないアッセンブリ用治具の上に前記シンチレータ素子１
と前記光反射剤２とを交互に併設しシンチレータ素子群
３（例えば１６チヤンネル）を形成する。そのあと、シ
ンチレータ素子群３を透明接着剤を用いてフォトダイオ
ード素子４に対応させ、各々のチャンネルに一致させる
ように接着接合させる。The X-ray detector configured in this manner has conventionally been manufactured in the following manner. That is, as shown in FIG. 6, the scintillator element 1 is placed on an assembly jig (not shown).
and the light reflecting agent 2 are arranged alternately to form a scintillator element group 3 (for example, 16 channels). Thereafter, the scintillator element group 3 is made to correspond to the photodiode element 4 using a transparent adhesive, and adhesively bonded so as to correspond to each channel.
かくしてフォトダイオード５の上にシンチレータ素子群
３をマウントした場合、入射されてきたＸ線はシンチレ
ータ素子１で電子変換され、この電子の運動エネルギー
が失われる過程で可視光子を発生する。そしてこの可視
光子がそれぞれのシンチレータ素子１に対応するフォト
ダイオード５で光電変換され電気信号となる。また前記
入射されてきたＸ線と同時に特性Ｘ線を発生し、この特
性Ｘ線もシンチレータ素子１や光反射剤２に吸収される
。When the scintillator element group 3 is thus mounted on the photodiode 5, the incident X-rays are converted into electrons in the scintillator element 1, and visible photons are generated in the process of losing the kinetic energy of the electrons. These visible photons are then photoelectrically converted by the photodiodes 5 corresponding to the respective scintillator elements 1 to become electrical signals. Moreover, characteristic X-rays are generated simultaneously with the incident X-rays, and these characteristic X-rays are also absorbed by the scintillator element 1 and the light reflecting agent 2.
（発明が解決しようとする課題）
然し乍ら、従来のＸ線検出器にあっては、次のような問
題がある。すなわちシンチレータ素子群３を１つ１つピ
ンセット等でつまみ、図示しないアッセンブリ用治県の
上に並ベシンチレータ素子１間に遮光するための光反射
剤２を押入し、この光反射剤２とシンチレータ素子１と
を交互に接着剤で接着していた。このためアッセイされ
たシンチレータ素子群３はシンチレータ素子１と光反射
剤２とが凹凸にバラバラに接着されていた。このためシ
ンチレータ素子１はシンチレータ併設方向（チャンネル
方向）に対して不揃いであるため、チャンネル毎にシン
チレータ１による発光量が異なってしまう。すなわち前
記入射Ｘ線および特性Ｘ線の大部分はシンチレータ素子
１や光反射剤２に吸収されるが、一部は隣接する他のシ
ンチレータ素子１に透過し電気信号になる。このためシ
ンチレータ素子間でクロストークが発生してしまい、画
像診断に悪影響を与えるという問題があった。(Problems to be Solved by the Invention) However, conventional X-ray detectors have the following problems. That is, the scintillator element group 3 is picked up one by one with tweezers or the like, and the light reflecting agent 2 for blocking light is pushed between the parallel scintillator elements 1 on top of the assembly area (not shown), and the light reflecting agent 2 and the scintillator are Elements 1 and 1 were alternately bonded with adhesive. For this reason, in the scintillator element group 3 that was assayed, the scintillator elements 1 and the light reflecting agent 2 were adhered to each other unevenly. For this reason, since the scintillator elements 1 are not aligned with respect to the direction in which the scintillators are provided (channel direction), the amount of light emitted by the scintillator 1 differs for each channel. That is, most of the incident X-rays and characteristic X-rays are absorbed by the scintillator element 1 and the light reflecting agent 2, but some of them are transmitted to other adjacent scintillator elements 1 and become electrical signals. For this reason, crosstalk occurs between scintillator elements, which poses a problem of adversely affecting image diagnosis.
そこで本発明の目的は、シンチレータ素子と光反射剤と
の面の凹凸をなくして隣接するチャンネルの受光素子へ
の光漏れによるクロストークを防止して鮮明な断層像を
得る放射線検出器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 radiation detector that eliminates unevenness on the surfaces of a scintillator element and a light reflecting agent to prevent crosstalk due to light leakage to the light receiving element of an adjacent channel, thereby obtaining a clear tomographic image. There is a particular thing.
［発明の構成］
（課題を解決する為の手段）
本発明は上記の課題を解決し目的を達成する為に次のよ
うな手段を講じた。すなわち本発明は、Ｘ線入射量に応
じて光を発生する複数のシンチレータ素子、この各シン
チレー゛夕素子と交互に併設されこの併設方向に対し各
シンチレータ素子からの光を反射させる第１の光反射部
材を備えたシンチレータ素子群と、このシンチレータ素
子群の前記併設方向に直交する方向の少なくとも一端に
前記併設方向に沿って設けられ前記直交する方向に対し
各シンチレータ素子からの光を反射させる第２の光反射
部材とを備えたものである。[Structure of the Invention] (Means for Solving the Problems) In order to solve the above problems and achieve the objects, the present invention takes the following measures. That is, the present invention provides a plurality of scintillator elements that generate light according to the amount of incident X-rays, and a first light beam that is arranged alternately alongside each scintillator element and reflects the light from each scintillator element in the direction in which the scintillator elements are arranged. a scintillator element group including a reflecting member; and a scintillator element group provided at at least one end of the scintillator element group in a direction perpendicular to the direction in which the scintillator elements are arranged, and reflecting light from each scintillator element in the direction perpendicular to the direction in which the scintillator elements are arranged. 2 light reflecting members.
また前記第２の光反射部材は、白色からなるものである
。Further, the second light reflecting member is made of white.
（作用）
このような手段を講じたことにより、次のような作用を
呈する。シンチレータ素子の併設方向に直交する方向の
少なくとも一端に前記併設方向に沿って第２の反射部材
を設けたので、シンチレータ素子の端面が均一になり、
しかもこの端面からの特性Ｘ線の隣接するチャンネルへ
の漏れを防止できる。これにより特性Ｘ線に起因するク
ロストークによるエネルギー特性のバラツキを軽減でき
るので、画像の劣化を防止した鮮明な断層像が得られる
。(Effects) By taking such measures, the following effects are achieved. Since the second reflecting member is provided at at least one end in the direction perpendicular to the direction in which the scintillator elements are arranged, the end surface of the scintillator element becomes uniform;
Furthermore, leakage of characteristic X-rays from this end face into adjacent channels can be prevented. As a result, variations in energy characteristics due to crosstalk caused by characteristic X-rays can be reduced, so a clear tomographic image can be obtained without image deterioration.
（実施例）
第１図は本発明に係る放射線検出器の一実施例を示す概
略斜視図、第２図はフォトダイオード素子５上にマウン
トされた多チヤンネル型Ｘ線検出器を示す概略斜視図、
第３図は前記Ｘ線検出器を示す断面図である。なお前記
第４図乃至第６図に示す部分と同一部分については同一
符号を付しその詳細な説明は省略する。第１図に示すよ
うにＸ線検出器は、シンチレータ素子群３と、第２の光
反射部材としてのスペーサ９を備えている。前記シンチ
レータ素子群３は、前記Ｘ線入射量に応じて光を発生す
る複数のシンチレータ素子１．この各シンチレータ素子
１と交互に併設されこの併設方向（以下チャンネル方向
という。）に対し各シンチレータ素子からの光を反射さ
せる第１の光反射部材としてのスペーサ２を備えている
。またスペーサ９は、シンチレータ素子群３のチャンネ
ル方向に直交する方向（以下スライス方向という。）の
両端に、前記チャンネル方向に沿って満２０に介挿され
るように設けられ前記スライス方向に対し各シンチレー
タ素子１からの光を反射させるものである。前記スペー
サ２．９は同一材質からなり、両面に白色塗料を塗布し
た光反射剤９ａ、９ｂが形成され内部に金属薄板９ｃを
有している。また第３図において、スペーサ９は左右に
設けられた散乱線遮蔽用スリット１０のＸ線入射面の延
長線より外側（点線ａ、ｂの外側）に設けられている。(Example) FIG. 1 is a schematic perspective view showing an example of a radiation detector according to the present invention, and FIG. 2 is a schematic perspective view showing a multichannel X-ray detector mounted on a photodiode element 5. ,
FIG. 3 is a sectional view showing the X-ray detector. Note that the same parts as those shown in FIGS. 4 to 6 are designated by the same reference numerals, and detailed explanation thereof will be omitted. As shown in FIG. 1, the X-ray detector includes a scintillator element group 3 and a spacer 9 as a second light reflecting member. The scintillator element group 3 includes a plurality of scintillator elements 1. Spacers 2 are provided as first light reflecting members which are alternately arranged alongside each scintillator element 1 and reflect light from each scintillator element in the direction in which they are arranged (hereinafter referred to as the channel direction). Further, the spacers 9 are provided at both ends of the scintillator element group 3 in a direction perpendicular to the channel direction (hereinafter referred to as the slice direction), so that the spacers 9 are inserted in a total of 20 spaces along the channel direction. It reflects the light from the element 1. The spacer 2.9 is made of the same material, has light reflecting agents 9a and 9b coated with white paint on both sides, and has a thin metal plate 9c inside. Further, in FIG. 3, the spacer 9 is provided outside the extension line of the X-ray incident surface of the scattered radiation shielding slits 10 provided on the left and right sides (outside the dotted lines a and b).
また前記Ｘ線入射面の延長線より内側では、シンチレー
タ素子１の可視光射面と光学的に結合されたフォトダイ
オード５を分割している。Further, on the inner side of the extension line of the X-ray incident surface, a photodiode 5 optically coupled to the visible light incident surface of the scintillator element 1 is divided.
以下実施例について図面を参照して説明する。Examples will be described below with reference to the drawings.
まず第１図に示すようにスペーサ２とシンチレータ素子
１とを交互に併設し、スライス方向の両端に設けられた
溝２０にスペーサ９を適宜の接着剤を用いて挿入しこれ
らを接合する。そして挿入接合されたシンチレータ素子
群３を第２図に示すように多チャンネルル型フォトダイ
オード５がマウントされたプリント配線基板７に透明接
着剤（例えばガラス用接着剤など）を用いて各チャンネ
ルとシンチレータ素子１とが一致するように接着しこれ
らを接合する。First, as shown in FIG. 1, spacers 2 and scintillator elements 1 are arranged alternately, and spacers 9 are inserted into grooves 20 provided at both ends in the slicing direction using an appropriate adhesive to bond them together. Then, as shown in FIG. 2, the inserted and bonded scintillator element group 3 is attached to each channel on a printed wiring board 7 on which a multi-channel photodiode 5 is mounted using a transparent adhesive (for example, glass adhesive). The scintillator element 1 is bonded so as to be aligned with the scintillator element 1 to join them.
そして第３図に示すように入射Ｘ線は、散乱線遮蔽用ス
リット１０の端面ａから端面すの範囲でコリメータ１１
を介してシンチレータ素子１に入力する。ここでスペー
サ９は散乱線遮蔽用スリット１０のＸ線入射面の延長線
より外側、すなわち点線ａ、ｂの外側に設けられている
ので、シンチレータ素子１で発光した光のうち、スライ
ス方向への光は前記スペーサっで吸収される。これによ
りシンチレータ素子間での光の漏れは防止できるので、
クロストークを防止でき、アーチファクトとして画像に
影響を及ぼすことがなくなる。As shown in FIG. 3, the incident X-rays enter the collimator 11 in the range from end face a to end face
The signal is inputted to the scintillator element 1 via. Here, since the spacer 9 is provided outside the extension line of the X-ray incident surface of the scattered radiation shielding slit 10, that is, outside the dotted lines a and b, out of the light emitted by the scintillator element 1, it is transmitted in the slice direction. Light is absorbed by the spacer. This prevents light from leaking between scintillator elements.
Crosstalk can be prevented and images will not be affected by artifacts.
このように本実施例によれば、シンチレータ素子１のチ
ャンネル方向に直交するスライス方向の両端に、前記チ
ャンネル方向に沿ってスペーサ９を設けたので、シンチ
レータ素子１の端面が均一になり、しかもこの端面から
の特性Ｘ線の隣接するチャンネルへの漏れを防止できる
。これにより特性Ｘ線に起因するクロストークによるエ
ネルギー特性のバラツキを軽減できるので、画像の劣化
を防止した鮮明な断層像が得られる。As described above, according to this embodiment, since the spacers 9 are provided along the channel direction at both ends of the scintillator element 1 in the slice direction perpendicular to the channel direction, the end surfaces of the scintillator element 1 are made uniform, and this It is possible to prevent characteristic X-rays from leaking from the end face into adjacent channels. As a result, variations in energy characteristics due to crosstalk caused by characteristic X-rays can be reduced, so a clear tomographic image can be obtained without image deterioration.
なお本発明は上述した実施例に限定されるものではない
。上述した実施例ではシンチレータ素子１のスライス方
向の両端にスペーサ９を設けるようにしたが、例えばス
ペーサ９はＸ線検出器の使用に応じて、シンチレータ素
子１のスライス方向の少なくとも一端に設けるようにし
ても上述した実施例と同様な効果が奏せられる。このほ
か本発明の要旨を逸脱しない範囲で種々変形実施可能で
あるのは勿論である。Note that the present invention is not limited to the embodiments described above. In the embodiment described above, the spacer 9 is provided at both ends of the scintillator element 1 in the slice direction, but for example, the spacer 9 may be provided at at least one end of the scintillator element 1 in the slice direction depending on the use of an X-ray detector. Even in this case, the same effects as in the above-mentioned embodiment can be achieved. It goes without saying that various other modifications can be made without departing from the gist of the present invention.
［発明の効果］
本発明によれば、シンチレータ素子の併設方向に直交す
る方向の少なくとも一端に前記併設方向に沿って第２の
反射部材を設けたので、シンチレータ素子の端面が均一
になり、しかもこの端面からの特性Ｘｌｉの隣接するチ
ャンネルへの漏れを防止できる。これにより特性Ｘ線に
起因するクロストークによるエネルギー特性のバラツキ
を軽減できるので、画像の劣化を防止した鮮明な断層像
が得られる放射線検出器を提供できる。[Effects of the Invention] According to the present invention, since the second reflecting member is provided along the direction in which the scintillator elements are arranged at least at one end in the direction perpendicular to the direction in which the scintillator elements are arranged, the end face of the scintillator element becomes uniform. It is possible to prevent characteristic Xli from leaking from this end face into an adjacent channel. As a result, variations in energy characteristics due to crosstalk caused by characteristic X-rays can be reduced, so it is possible to provide a radiation detector that can obtain clear tomographic images that prevent image deterioration.
第１図は本発明に係る放射線検出器の一実施例を示す概
略斜視図、第２図はフォトダイオード素子上にマウント
された多チヤンネル型Ｘ線検出器を示す概略斜視図、第
３図は前記Ｘ線検出器の詳細を示す図、第４図は従来の
多チヤンネル型Ｘ線検出器を示す概略斜視図、第５図は
前記第４図に示すＸ線検出器のフォトダイオードの詳細
を示す断面図、第６図は従来のシンチレータ素子群の。
製造方法を示す概略図である。
１・・・シンチレータ素子、３・・・シンチレータ素子
群、２，９・・・スペーサ、４・・・フォトダイオード
素子、５・・・フォトダイオード、６・・・フォトダイ
オード端子、７・・・プリント配線基板、９ｃ・・・金
属薄板、９ａ、９ｂ・・・反射剤、１０・・・散乱線遮
蔽用スリット、１１・・・コリメータ、２０・・・溝。FIG. 1 is a schematic perspective view showing an embodiment of a radiation detector according to the present invention, FIG. 2 is a schematic perspective view showing a multichannel X-ray detector mounted on a photodiode element, and FIG. A diagram showing details of the X-ray detector, FIG. 4 is a schematic perspective view showing a conventional multi-channel X-ray detector, and FIG. 5 shows details of the photodiode of the X-ray detector shown in FIG. 4. The sectional view shown in FIG. 6 is of a conventional scintillator element group. It is a schematic diagram showing a manufacturing method. DESCRIPTION OF SYMBOLS 1...Scintillator element, 3...Scintillator element group, 2, 9...Spacer, 4...Photodiode element, 5...Photodiode, 6...Photodiode terminal, 7... Printed wiring board, 9c... Metal thin plate, 9a, 9b... Reflective agent, 10... Slit for scattering radiation shielding, 11... Collimator, 20... Groove.
Claims (2)
ータ素子、この各シンチレータ素子と交互に併設されこ
の併設方向に対し各シンチレータ素子からの光を反射さ
せる第１の光反射部材を備えたシンチレータ素子群と、
このシンチレータ素子群の前記併設方向に直交する方向
の少なくとも一端に前記併設方向に沿って設けられ前記
直交する方向に対し各シンチレータ素子からの光を反射
させる第２の光反射部材とを具備したことを特徴とする
放射線検出器。(1) A plurality of scintillator elements that generate light according to the amount of incident X-rays, and a first light reflecting member that is arranged alternately with each scintillator element and reflects the light from each scintillator element in the direction in which the scintillator elements are arranged. a group of scintillator elements,
A second light reflecting member is provided at at least one end of the scintillator element group in a direction orthogonal to the direction in which the scintillator elements are arranged, and a second light reflecting member is provided along the direction in which the scintillator elements are arranged and reflects light from each scintillator element in the direction orthogonal to the direction. A radiation detector featuring:
とを特徴とする請求項１項記載の放射線検出器。(2) The radiation detector according to claim 1, wherein the second light reflecting member is made of white.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1146505A JP2941306B2 (en) | 1989-06-08 | 1989-06-08 | Radiation detector |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1146505A JP2941306B2 (en) | 1989-06-08 | 1989-06-08 | Radiation detector |
Related Child Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP7157099A Division JPH11326525A (en) | 1999-03-17 | 1999-03-17 | Radiation detector |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH0310188A true JPH0310188A (en) | 1991-01-17 |
| JP2941306B2 JP2941306B2 (en) | 1999-08-25 |
Family
ID=15409150
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP1146505A Expired - Lifetime JP2941306B2 (en) | 1989-06-08 | 1989-06-08 | Radiation detector |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP2941306B2 (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| NL9400855A (en) * | 1993-05-27 | 1994-12-16 | Hitachi Medical Corp | Radiation detection device and method for the manufacture thereof. |
| US5386122A (en) * | 1992-06-30 | 1995-01-31 | Hitachi Medical Corporation | Radiation detector and method for making the same |
-
1989
- 1989-06-08 JP JP1146505A patent/JP2941306B2/en not_active Expired - Lifetime
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5386122A (en) * | 1992-06-30 | 1995-01-31 | Hitachi Medical Corporation | Radiation detector and method for making the same |
| NL9400855A (en) * | 1993-05-27 | 1994-12-16 | Hitachi Medical Corp | Radiation detection device and method for the manufacture thereof. |
| US5506409A (en) * | 1993-05-27 | 1996-04-09 | Hitachi Medical Corporation | Radiation detecting device and the manufacture thereof |
Also Published As
| Publication number | Publication date |
|---|---|
| JP2941306B2 (en) | 1999-08-25 |
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