JPH0541190A - X-ray image tube - Google Patents
X-ray image tubeInfo
- Publication number
- JPH0541190A JPH0541190A JP19789091A JP19789091A JPH0541190A JP H0541190 A JPH0541190 A JP H0541190A JP 19789091 A JP19789091 A JP 19789091A JP 19789091 A JP19789091 A JP 19789091A JP H0541190 A JPH0541190 A JP H0541190A
- Authority
- JP
- Japan
- Prior art keywords
- input
- ray image
- phosphor layer
- photocathode
- image tube
- 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
Landscapes
- Image-Pickup Tubes, Image-Amplification Tubes, And Storage Tubes (AREA)
Abstract
Description
【0001】[0001]
【産業上の利用分野】この発明はX線イメ−ジ管に係
り、特にその入力面の改良に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an X-ray image tube, and more particularly to improvement of its input surface.
【0002】[0002]
【従来の技術】一般にX線イメ−ジ管は図2に示すよう
に構成され、真空外囲器1内の入力側に入力窓1aに対
向して入力面2が、出力側に陽極3及び出力面4がそれ
ぞれ配設され、更に真空外囲器1の内部の側壁に沿って
集束電極5が設けられている。そして、入力面2は、基
板6に入力蛍光体層7と光電面8が順次積層形成されて
なっている。2. Description of the Related Art Generally, an X-ray image tube is constructed as shown in FIG. 2, in which the input side of the vacuum envelope 1 is opposed to the input window 1a, the input side 2 is on the output side, and the anode 3 is on the output side. Output surfaces 4 are respectively arranged, and focusing electrodes 5 are further provided along side walls inside the vacuum envelope 1. The input surface 2 is formed by sequentially stacking the input phosphor layer 7 and the photoelectric surface 8 on the substrate 6.
【0003】動作時にはX線管9からのX線が被写体1
0を通り、入力窓1aと基板6を通過して入力蛍光体層
7で光に変換される。この光は光電面8に達し、電子に
変換される。この電子は集束電極5と陽極3により集束
・加速され、出力面4において可視光像に変換される。
このようにしてX線像は可視光像に変換されるが、この
可視光像はTVカメラ、シネカメラ、スポットカメラ等
により記録され、医療診断が行なわれる。During operation, the X-ray from the X-ray tube 9 is the subject 1.
0, passes through the input window 1a and the substrate 6, and is converted into light at the input phosphor layer 7. This light reaches the photocathode 8 and is converted into electrons. The electrons are focused and accelerated by the focusing electrode 5 and the anode 3, and converted into a visible light image on the output surface 4.
In this way, the X-ray image is converted into a visible light image, and this visible light image is recorded by a TV camera, cine camera, spot camera, etc., and medical diagnosis is performed.
【0004】[0004]
【発明が解決しようとする課題】一様なX線がX線イメ
−ジ管に入射した場合には、最終的な画像も一様な明る
さ或いは濃度を持つことが期待される。ところが、実際
には画像の中央部と周辺部で、明るさ或いは濃度が異な
ることがある。例えば、X線イメ−ジ管の持つ糸巻き歪
みと呼ばれる電子レンズの歪みにより、周辺部の電子密
度が小さくなって、周辺部の明るさ或いは濃度が中央部
に比べて小さくなることがある。When uniform X-rays are incident on the X-ray image tube, it is expected that the final image will also have uniform brightness or density. However, in reality, the brightness or the density may be different between the central part and the peripheral part of the image. For example, the distortion of the electron lens called the pincushion distortion of the X-ray image tube may reduce the electron density in the peripheral portion, and the brightness or density in the peripheral portion may become smaller than that in the central portion.
【0005】又、違う例としては、光電面のアンチモン
の濃度が、アンチモン蒸発源の幾何学的配置によって中
央部と周辺部で異なってしまうことがある。このような
場合、中央部の濃度が適性であれば、光電面の周辺部は
中央部と比べて電子を発生させる能力が劣る。従って、
最終的な画像では中央部が明るくなる。又、反対に周辺
部の濃度が適性であれば、最終的な画像では周辺部が明
るくなる。このように、明るさ或いは濃度に分布がある
と、X線診断上支障を来たしたり、濃度分布を補正する
ために、画像処理時に処理装置或いはプログラムに負担
がかかることになる。この発明は、X線を電子に変換す
る能率が入力面全面においてほぼ一様であるX線イメ−
ジ管を提供することを目的とする。Another example is that the concentration of antimony on the photocathode differs between the central part and the peripheral part depending on the geometrical arrangement of the antimony evaporation source. In such a case, if the concentration of the central portion is appropriate, the peripheral portion of the photocathode has a lower ability to generate electrons than the central portion. Therefore,
The final image has a bright center. On the contrary, if the density of the peripheral portion is appropriate, the peripheral portion becomes bright in the final image. As described above, if there is a distribution in brightness or density, it may cause a problem in X-ray diagnosis, and a processing device or a program may be burdened during image processing in order to correct the density distribution. The present invention is an X-ray image in which the efficiency of converting X-rays into electrons is substantially uniform over the entire input surface.
The purpose is to provide the tube.
【0006】[0006]
【課題を解決するための手段】この発明は、基板上に形
成された蛍光体の多数の柱状結晶からなる入力蛍光体層
と、この入力蛍光体層上に直接又は間接に形成された光
電面とからなる入力面を備えたX線イメ−ジ管におい
て、柱状結晶の光電面側表面の凸形突起の頂角が入力面
の周辺部から中央部にかけて変化しているX線イメ−ジ
管である。The present invention is directed to an input phosphor layer formed of a large number of columnar crystals of a phosphor formed on a substrate, and a photocathode formed directly or indirectly on the input phosphor layer. In an X-ray image tube having an input surface consisting of and, the apex angle of the convex protrusion on the photocathode-side surface of the columnar crystal changes from the peripheral portion to the central portion of the input surface. Is.
【0007】[0007]
【作用】この発明によれば、X線を電子に変換する能率
が入力面全面においてほぼ一様である。According to the present invention, the efficiency of converting X-rays into electrons is substantially uniform over the entire input surface.
【0008】即ち、入力蛍光体層を構成している柱状結
晶の光電面側表面の凸形突起の頂角が180°に近い場
合、つまり表面が平坦である場合には、光電面は表面全
体に形成される。頂角が小さくなってくると、表面に凹
凸が現われる。凹の部分には光電面の構成要素であるア
ンチモンやアルカリ金属は届き難く、光電面は形成され
ない。That is, when the apex angle of the convex protrusions on the photocathode-side surface of the columnar crystals forming the input phosphor layer is close to 180 °, that is, when the surface is flat, the photocathode is the entire surface. Formed in. As the apex angle becomes smaller, irregularities appear on the surface. It is difficult for antimony and alkali metal, which are the components of the photocathode, to reach the concave portion, and the photocathode is not formed.
【0009】このため、頂角が小さい部分に形成される
光電面の面積は、入力蛍光体層の面積よりも小さくな
る。従って、入力蛍光体層中でX線から変換され入力蛍
光体層の表面に達した光のうち、或る割合のみが電子に
変換される。そして、この割合は頂角が小さくなるにつ
れて小さくなる。このようにして、頂角を変化させるこ
とにより、入力蛍光体層中でX線から変換され入力蛍光
体層の表面に達した光が電子に変換される割合を変化さ
せることが出来る。Therefore, the area of the photocathode formed in the portion having a small apex angle is smaller than the area of the input phosphor layer. Therefore, of the light that has been converted from X-rays and reached the surface of the input phosphor layer in the input phosphor layer, only a certain proportion is converted into electrons. Then, this ratio becomes smaller as the apex angle becomes smaller. In this way, by changing the apex angle, it is possible to change the rate at which light that is converted from X-rays and reaches the surface of the input phosphor layer is converted into electrons in the input phosphor layer.
【0010】[0010]
【実施例】以下、図面を参照して、この発明の一実施例
を詳細に説明するが、この発明は入力面を改善したもの
で、入力面についてのみ説明することにする。DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS An embodiment of the present invention will be described in detail below with reference to the drawings. The present invention is an improvement of the input surface, and only the input surface will be described.
【0011】この発明によるX線イメ−ジ管の入力面
は、図1に示すように構成され、基板11に入力蛍光体
層12と光電面(図示せず)が順次積層形成されてなっ
ている。そして、入力蛍光体層12は蛍光体の多数の柱
状結晶からなっている。The input surface of the X-ray image tube according to the present invention is constructed as shown in FIG. 1, and the input phosphor layer 12 and the photocathode (not shown) are sequentially laminated on the substrate 11. There is. The input phosphor layer 12 is composed of many columnar crystals of phosphor.
【0012】この場合、柱状結晶の光電面側表面の凸形
突起の頂角が入力面の周辺部から中央部にかけて変化し
ている。即ち、入力面の中央部の柱状結晶12aの頂角
α1は、周辺部の柱状結晶12bの頂角α2 よりも大き
くなっている。即ち、α1 >α2 に設定されている。In this case, the apex angle of the convex protrusion on the photocathode-side surface of the columnar crystal changes from the peripheral portion to the central portion of the input surface. That is, the apex angle α 1 of the columnar crystal 12a in the central portion of the input surface is larger than the apex angle α 2 of the columnar crystal 12b in the peripheral portion. That is, α 1 > α 2 is set.
【0013】このため、周辺部の柱状結晶12bの表面
に光電面を形成する場合、柱状結晶12bの隙間13
に、光電面を構成する物質例えばアルカリ金属が付着し
難く、結果的に光電面は柱状結晶12bの頂角付近のみ
に形成されることになる。従って、周辺部でX線から変
換された光は、その一部分が光電面で光に変換されるこ
とになり、中央部よりもX線を光に変換する能率を抑え
ることが出来る。Therefore, when the photocathode is formed on the surface of the peripheral columnar crystal 12b, the gap 13 between the columnar crystals 12b is formed.
In addition, the substance forming the photocathode, for example, an alkali metal hardly adheres, and as a result, the photocathode is formed only near the apex angle of the columnar crystal 12b. Therefore, a part of the light converted from the X-rays in the peripheral portion is converted into the light by the photocathode, and the efficiency of converting the X-rays into light can be suppressed more than that in the central portion.
【0014】又、上記とは逆に、入力面の周辺部の柱状
結晶12bの頂角α2 を、中央部の柱状結晶12aの頂
角α1 よりも大きくすれば(α2 >α1 )、中央部のX
線を光に変換する能率を、周辺部のX線を光に変換する
能率よりも抑えることが出来る。Conversely, if the apex angle α 2 of the columnar crystals 12b in the peripheral portion of the input surface is made larger than the apex angle α 1 of the columnar crystals 12a in the central portion (α 2 > α 1 ) contrary to the above. , X in the center
The efficiency of converting rays into light can be suppressed to be lower than the efficiency of converting X-rays in the peripheral portion into light.
【0015】尚、上記実施例では、入力蛍光体層12上
に直接光電面が形成されていたが、入力蛍光体層12上
に透明導電膜を介して光電面が形成されている場合で
も、この発明は適用出来る。又、この発明は上記の入力
面以外は、図2のX線イメ−ジ管と同様構成であるの
で、詳細な説明を省略する。In the above embodiment, the photocathode is directly formed on the input phosphor layer 12, but even when the photocathode is formed on the input phosphor layer 12 via the transparent conductive film, This invention can be applied. Further, the present invention has the same structure as the X-ray image tube of FIG. 2 except for the above-mentioned input surface, and therefore detailed description thereof will be omitted.
【0016】[0016]
【発明の効果】この発明によれば、X線を電子に変換す
る能率が入力面全面においてほぼ一様である。この結
果、X線診断上支障を来たしたり、濃度分布を補正する
ために画像処理時に処理装置或いはプログラムに負担が
かかるという、従来見られた欠点を解消することが出来
る。According to the present invention, the efficiency of converting X-rays into electrons is substantially uniform over the entire input surface. As a result, it is possible to solve the drawbacks that have been seen in the past, such that the X-ray diagnosis may be hindered and the processing device or the program may be burdened at the time of image processing in order to correct the density distribution.
【図1】この発明の一実施例に係るX線イメ−ジ管の入
力面を拡大して示す断面図。FIG. 1 is an enlarged sectional view showing an input surface of an X-ray image tube according to an embodiment of the present invention.
【図2】一般的なX線イメ−ジ管の全体を示す概略断面
図。FIG. 2 is a schematic sectional view showing the whole of a general X-ray image tube.
11…基板、12…入力蛍光体層、12a,12b…柱
状結晶、α1 ,α2 …頂角。11 ... Substrate, 12 ... Input phosphor layer, 12a, 12b ... Columnar crystal, α 1 , α 2 ... Apex angle.
Claims (1)
結晶からなる入力蛍光体層と、この入力蛍光体層上に直
接又は間接に形成された光電面とからなる入力面を備え
たX線イメ−ジ管において、 上記柱状結晶の上記光電面側表面の凸形突起の頂角が上
記入力面の周辺部から中央部にかけて変化していること
を特徴とするX線イメ−ジ管。1. An input surface comprising an input phosphor layer formed of a large number of columnar crystals of a phosphor formed on a substrate, and a photocathode formed directly or indirectly on the input phosphor layer. In the X-ray image tube, the apex angle of the convex protrusion on the photocathode-side surface of the columnar crystal changes from the peripheral portion to the central portion of the input surface. ..
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP19789091A JPH0541190A (en) | 1991-08-07 | 1991-08-07 | X-ray image tube |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP19789091A JPH0541190A (en) | 1991-08-07 | 1991-08-07 | X-ray image tube |
Publications (1)
Publication Number | Publication Date |
---|---|
JPH0541190A true JPH0541190A (en) | 1993-02-19 |
Family
ID=16381998
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP19789091A Pending JPH0541190A (en) | 1991-08-07 | 1991-08-07 | X-ray image tube |
Country Status (1)
Country | Link |
---|---|
JP (1) | JPH0541190A (en) |
-
1991
- 1991-08-07 JP JP19789091A patent/JPH0541190A/en active Pending
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